Published online Jan 7, 2016. doi: 10.3748/wjg.v22.i1.205
Peer-review started: June 1, 2015
First decision: July 14, 2015
Revised: August 4, 2015
Accepted: December 1, 2015
Article in press: December 1, 2015
Published online: January 7, 2016
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Hepatocellular carcinoma (HCC) is the most common primary liver cancer. Imaging is important for establishing a diagnosis of HCC and early diagnosis is imperative as several potentially curative treatments are available when HCC is small. Hepatocarcinogenesis occurs in a stepwise manner on a background of chronic liver disease or cirrhosis wherein multiple genes are altered resulting in a range of cirrhosis-associated nodules. This progression is related to increased cellularity, neovascularity and size of the nodule. An understanding of the stepwise progression may aid in early diagnosis. Dynamic and multiphase contrast-enhanced computed tomography and magnetic resonance imaging still form the cornerstone in the diagnosis of HCC. An overview of the current diagnostic standards of HCC in accordance to the more common practicing guidelines and their differences will be reviewed. Ancillary features contribute to diagnostic confidence and has been incorporated into the more recent Liver Imaging Reporting and Data System. The use of hepatocyte-specific contrast agents is increasing and gradually changing the standard of diagnosis of HCC; the most significant benefit being the lack of uptake in the hepatocyte phase in the earlier stages of HCC progression. An outline of supplementary techniques in the imaging of HCC will also be reviewed.
Core tip: Imaging is important for establishing a diagnosis of hepatocellular carcinoma (HCC) and an understanding of the stepwise progression of hepatocarcinogenesis may aid in early diagnosis. Dynamic and multiphase contrast-enhanced computed tomography and magnetic resonance imaging still form the cornerstone in the diagnosis of HCC. An overview of the current diagnostic standards of HCC in accordance to the more common practicing guidelines and their differences will be reviewed. Various ancillary features, use of hepatocyte-specific contrast agents and supplementary imaging techniques also help to increase diagnostic confidence and will be reviewed.
- Citation: Hennedige T, Venkatesh SK. Advances in computed tomography and magnetic resonance imaging of hepatocellular carcinoma. World J Gastroenterol 2016; 22(1): 205-220
- URL: https://www.wjgnet.com/1007-9327/full/v22/i1/205.htm
- DOI: https://dx.doi.org/10.3748/wjg.v22.i1.205
Hepatocellular carcinoma (HCC) is the most common primary liver cancer. It ranks sixth in cancer incidence and third in cancer mortality worldwide[1]. It is the most prevalent liver cancer with up to three-quarter of cases in the world occurring in Asia due to the high prevalence of chronic viral hepatitis B[2]. Patients diagnosed with HCC generally have a poor prognosis due to the aggressive nature of the disease[3]. Early diagnosis of HCC is imperative as several potentially curative treatments are available, especially when the lesion is small.
Regular surveillance of patients is instituted for early detection of HCC in patients with chronic liver disease and particularly in those with advanced liver fibrosis. Screening involves clinical examination, serum analysis of liver function and tumour antigens such as alpha-fetoprotein (AFP) and imaging. Although AFP is not specific for HCC and may give false positive results in the setting of hepatitis and fibrosis, it is still useful in monitoring of the disease process in combination with imaging[4]. Non-invasive diagnosis with imaging is currently the preferred method and several guidelines are available to aid in diagnosis and they all endorse arterial enhancement followed by washout in the diagnosis of HCC (Figure 1). Dynamic and multiphase contrast-enhanced computed tomography (CT) and magnetic resonance imaging (MRI) form the cornerstone of diagnosis in HCC. This review presents an overview of the current diagnostic standards of HCC in accordance to the more common practicing guidelines as well as the use of ancillary features and hepatocyte-specific contrast agents in the diagnosis of HCC. An outline of supplementary techniques in the imaging of HCC will also be reviewed.
HCC is associated with chronic liver disease and cirrhosis irrespective of its etiology. It has been shown that only about 10% of HCCs develop in non-cirrhotic livers[5]. The incidence of HCC has been increasing, with chronic hepatitis B and C infections being major contributory factors worldwide[6]. Apart from chronic viral infection, several lifestyle factors contribute to the development of HCC. These include excessive alcohol consumption, obesity, diabetes and intake of aflatoxin-contaminated foods[7]. Greater than 90% of HCC cases develop in chronically inflamed liver as a result of viral hepatitis and alcohol abuse[8]. Obesity and diabetes are associated with development of non-alcoholic fatty liver disease (NAFLD)[9]. Insulin resistance and the resulting inflammatory cascade together with the development of non-alcoholic steatohepatitis (NASH) appear to encourage hepatocarcinogenesis[10]. Cigarette smoking is regarded as a co-factor in the development of HCC[11]. Hepatocarcinogenesis also increases in the setting of HIV infection[12]. Lastly, genetic conditions such as haemochromatosis, glycogen storage disease type 1, alpha 1-antitrypsin deficiency are all associated with increased risk of HCC, most frequently on a background of cirrhosis[13].
In patients with chronic liver disease, HCC typically develops in a stepwise manner wherein multiple genes are altered. Chronic inflammation and regeneration of hepatocytes are underlying causes; it results in damage to the DNA of regenerating hepatocytes hence increasing the chance of gene alterations associated with carcinogenesis[14]. The currently accepted nomenclature for stepwise carcinogenesis of HCC is: regenerative nodule (RN); low-grade dysplastic nodule (DNI); high-grade dysplastic nodule (DNII); early and progressed HCC[15-17].
These are typically well-defined rounded regions of the cirrhotic parenchyma surrounded by scar tissue[18]. RNs are essentially phenotypically normal and are usually considered benign lesions[19]. Relative to background parenchyma, they are typically isoattenuating on unenhanced CT, T1, T2 and diffusion weighted (DWI) MR imaging[20,21] (Figure 2). On occasion, they may be T1 hyperintense and T2 hypointense, similar to dysplastic nodules[22]. With intravenous extracellular contrast injection, most RN enhance to the same degree as adjacent liver parenchyma or show slightly less enhancement, hence, they may appear as mildly hypoattenuating nodules relative to enhancing fibrosis in the portal venous phase[23] (Figure 3).
These are nodular lesions that differ macroscopically and microscopically from background parenchyma[24]. They are classified as low or high grade depending on the presence of cytologic and architectural aberrations[25]. DNI resemble RN histologically except that they contain unpaired arteries and clone-like populations[24,25]. On the other hand, DNII show features similar to that of a well-differentiated HCC. They demonstrate cellular atypia with clone-like features, expansile subnodules and architectural alterations[25,26]. Some DNII may contain subnodules of HCC resulting in the nodule-in-nodule appearance[27]. On CT, most DN are hypo- or isodense in the arterial, portal venous and delayed phases[28]. They are typically T1 hyperintense and iso- to hypointense on T2 imaging[23] (Figure 4). Some, especially DNII may contain intracellular fat resulting in signal loss on out-of-phase images[29]. Unlike HCC, DN are almost never T2 hyperintense or show restricted diffusion[30,31] (Figure 4).
Early HCC is likened to carcinoma-in-situ of other organs[32]. They rarely exceed 2 cm and unlike progressed HCC which displaces and destroys surrounding liver parenchyma, early HCCs expand by gradually replacing the parenchyma[17]. The main distinguishing characteristic between a DNII and early HCC is the presence of stromal invasion in the latter which is defined as infiltration of tumour cells into fibrous tissue surrounding portal tracts[25].
Theses nodules are overtly malignant with propensity to invade vessels and metastasize. Lesions smaller than 2 cm are typically distinctly nodular with well-defined margins; they grow by expanding into and compressing surrounding parenchyma resulting in formation of a pseudocapsule[17]. Lesions larger than 2 cm demonstrate a more aggressive behaviour. A mosaic pattern is characteristic which is defined by the presence of several internal subnodules separated by fibrous septa as well as areas of necrosis, haemorrhage and occasionally fatty metamorphosis[33].
In oncology, the diagnosis of malignancy usually necessitates tissue sampling prior to determination of treatment approach. Characterisation of HCC however, is an exception as a non-invasive diagnosis can be attained with imaging in high-risk patient populations[2,34,35]. The more widely used guidelines are the European Association for the Study of the Liver (EASL)[34], American Association for the Study of Liver Disease (AASLD)[35] and the Asian Pacific Society for the Study of the Liver (APASL)[2]. The hallmark diagnostic characteristics of HCC are arterial enhancement followed by portal venous and/or delayed phase washout[36-38] (Figures 1 and 5), this is common to all three guidelines. Comparative studies for CT and MR imaging using extracellular contrast agents found higher sensitivities with MR imaging[39,40]. The sensitivity of MRI for nodular HCC of all sizes is 77%-100% while that of CT is 68%-91%[34,35,41,42]. The size of the lesion is an important determinant in diagnosis; for lesions larger than 2 cm, the sensitivity is close to 100% for both modalities but drops to 45%-80% with MRI and 40%-75% with CT for lesions measuring 1-2 cm[40,43].
Both EASL and AASLD stratify lesions according to size; < 1 cm, 1-2 cm and > 2 cm for EASL and < 1 cm and > 1 cm for AASLD. Both guidelines deem less than 1 cm lesions as too small for characterisation and recommend follow-up. The diagnosis of HCC in lesions larger than 2 cm requires only a single imaging modality when the hallmark enhancement characteristics are present. Another imaging technique should be performed when enhancement characteristics are atypical. These guidelines differ with respect to lesions between 1-2 cm; the AASLD recommends the same approaches as for lesions larger than 2cm whereas EASL recommends the presence of typical enhancement characteristics on two imaging modalities. Both EASL and AASLD recommend biopsy in patients with lesions that do not fit in the above imaging criteria. Unlike EASL and AASLD, APASL does not stratify lesions according to size. Also, the APASL acknowledges the use of contrast-enhanced ultrasound (CEUS) to depict hypervascularity in lesions hypovascular on CT or MRI. When a defect is observed in the Kupffer phase on CEUS, it is diagnosed as HCC. The Kupffer phase also known as the post-vascular phase which occurs 20 min after injection and implies the presence of Kupffer cells which are present in non-neoplastic liver parenchyma and reduced in HCC[44]. If this defect is not observed, close follow-up is recommended.
The Liver Imaging Reporting and Data System (Li-RADS)[45] was introduced relatively recently by the American College of Radiology. The aim of this system was to standardize terminology and criteria in reporting of liver lesions in chronic liver disease. Each lesion is assigned a category ranging from L1 to L5, with each category denoting a higher probability of HCC. Unlike the above mentioned guidelines, Li-RADS takes into account ancillary features. The diagnosis of HCC is established by a combination of major signs including: arterial phase enhancement, lesion size, washout, capsule formation and threshold growth (Table 1). Ancillary features are then applied to upgrade or downgrade the initial classification.
| Arterial phase hypo- or iso-enhancement | Arterial phasehyper-enhancement | |||||
| Diameter (mm) | < 20 | ≥ 20 | < 10 | 10-19 | ≥ 20 | |
| Washout | None | L3 | L3 | L3 | L3 | L4 |
| Capsule formation | One | L3 | L4 | L4 | L4/L5 | L5 |
| Threshold growth | ≥ Two | L4 | L4 | L4 | L5 | L5 |
A substantial proportion of HCCs do not demonstrate the typical arterial enhancement with subsequent washout pattern. It has been shown that up to 40% of HCC lack arterial phase enhancement[34], these are largely early or poorly-differentiated infiltrative HCCs[46,47]. Also, 40%-60% of small HCCs do not demonstrate subsequent washout[48,49]. Hence, several ancillary signs have been described, most of which are better depicted with MRI. It is important to emphasise that these features individually are not specific for HCC, but their presence increases diagnostic probability.
DWI assesses molecular water motion within tissues and this information is acquired by applying balanced gradients to T2-weighted sequences. The degree of diffusion weighting can be altered by changing the b value, an acquisition parameter. With DWI, signal intensity from stationary water molecules is preserved whilst those that are in motion lose signal intensity depending on the degree of motion from their original position at the time of signal acquisition. Diffusion restriction is more prominent in malignant than in benign tumours[50]; the combination of high cellularity and intact cell membranes restrict the motion of water molecules resulting in hyperintensity on diffusion weighted imaging (DWI) and reduction in apparent diffusion coefficient (ADC) maps. DWI is particularly useful in the initial screening of the liver as nearly 70%-95% of HCCs can appear hyperintense[51-53], particularly using low b values[54]. The presence of restricted diffusion is found to be especially useful in the characterisation of small lesions[55,56] (Figure 5). Intermediate or poorly-differentiated HCCs are more often hyperintense on DWI than well-differentiated HCC[16]. In addition, restricted diffusion may be useful in the diagnosis of bland versus tumour thrombus[16].
The presence of fat in a focal liver lesion is better appreciated on MRI than on CT. The presence of fat is depicted as signal drop-out in the opposed-phase images (Figure 6). In chronic liver disease, a fat-contained tumour is highly suggestive of HCC[42], however, benign fat-containing regenerative nodules may also be seen[16]. Intralesional fat is more commonly seen in early as opposed to progressed HCC, with better prognosis associated with fat-contained HCC[55].
On MRI, the presence of mild to moderate T2 signal intensity is more often seen in HCCs (Figure 7). Markedly T2 hyperintense lesions are more likely to represent benign lesions such as cysts and haemangiomas, whereas T2 hypointense lesions may represent iron deposition in the nodules. Like the presence of intralesional fat, the degree of T2 signal intensity may have prognostic implications; many well-differentiated HCCs are found to be hypo- or isointense[56].
The variable tissue components of HCC account for this mosaic pattern; enhancing areas indicate viable tumour cells and low attenuation foci represent necrosis, fibrosis or hemorrhage[33]. Most large HCCs present with this pattern and it is regarded as fairly specific (Figure 8). Since it is found primarily in large lesions, the utility of this ancillary sign is probably of less utility in the characterisation of small HCCs.
This refers to a rim of peripheral enhancement in the portal venous or delayed phases (Figure 9). This sign may be well depicted in both CT and MRI and has been shown to be a significant predictor in the diagnosis of HCC[42,49]. A pseudocapsule has been found in 10%-47% of cases depending on the series studied[57-59].
Portal vein tumour thrombus (PVTT) is a well-known complication of HCCs; such invasion helps distinguish HCC from secondary hepatic cancers which rarely invade intrahepatic vessels[60]. It is important to note that the presence of a tumour thrombus can modify typical imaging features of HCC. When HCC infiltrates a portal vein, it continues to receive arterial blood supply and the tumor may drain directly into the portal vein. This direct draining results in arterioportal shunting and changes in portal vein haemodynamics[61]. Large HCCs complicated by PVTT less often demonstrate typical arterial enhancement with subsequent washout. Instead, the PVTT itself can show arterial phase enhancement with subsequent washout with distension of the vein (Figure 10)[61]. This arterioportal shunting may also result in poor enhancement of the surrounding liver parenchyma.
Presence of iron is better appreciated on MRI as opposed to CT and is shown as marked hypointensity on T2W sequences. Iron is normally present in the Kupffer cells that reside in sinusoids and are abundant in normal liver parenchyma. The presence of iron is highly suggestive of a non-malignant lesion in a cirrhotic liver[48]. On the contrary, the presence of an iron-free lesion in an otherwise iron-laden liver may suggest HCC (Figure 11).
This refers to the presence of a nodule within a larger nodule and is usually the result of the development of HCC within a pre-existing cirrhosis-related nodule. The nodule within the larger lesion may demonstrate increased arterial enhancement or T2 signal intensity relative to the surrounding larger nodule (Figure 12).
Hepatobiliary MRI contrast agents are increasingly being used and gradually changing the standard of diagnosis of HCC. These agents are gadolinium chelate-based with an initial vascular phase that is similar to the extracellular agents. However, they are actively taken up by hepatocytes via a group of proteins expressed in hepatocytes along the sinusoidal membrane known as organic anionic transporting polypeptides (OATP)[16]. In humans, OATP 8 appears to be responsible for cellular uptake[62]. The contrast agents are then partially excreted into the biliary system. Two hepatobiliary MRI contrast agents are currently in use: gadobenate dimeglumine (Gd-BOPTA, Multihance, Bracco, Milan, Italy) and gadoxetate dimeglumine (Gd-EOB-DTPA, Primovist in Europe and Eovist in the United States, Bayer Healthcare). Both contrast agents can be injected as an intravenous bolus dose. The hepatobiliary phase is attained 1-3 h after injection of Gd-BOPTA and about 20 min after injection of Gd-EOB-DTPA. With Gd-BOPTA, only 5% of the drug is transported through hepatocytes and excreted into bile whereas with Gd-EOB-DTPA, approximately 50% of the drug undergoes biliary excretion.
A small dose of Gd-EOB-DTPA (0.025 mmol/kg) is required compared to 0.1 mmol/kg for Gd-BOPTA. The former therefore has significant advantages in terms of safety, timing of examination and potentially better contrast. However, due to the low volume injected with Gd-EOB-DTPA compared to Gd-BOPTA, the vascular phase images are less ideal with a narrower imaging window for late hepatic arterial phase acquisition[63] which is when peak arterial enhancement of a nodule typically occurs. This can be overcome by performing multiple acquisitions during the arterial phase. Gd-EOB-DTPA does not provide a conventional delayed phase as hepatocellular uptake occurs during its first pass through the hepatic sinusoids[64]. Hence, by the end of the portal venous phase, considerable hepatocellular uptake has occurred with both intracellular and extracellular pools of Gd-EOB-DTPA contributing substantially to parenchymal enhancement[64]. As this phase represents a transition from extracellular-dominant to intracellular-dominant enhancement, it may be termed the transitional phase[65].
In addition to increased cellularity and neovascularity in the multistep carcinogenesis of HCC, OATP expression gradually decreases in the development of HCC. This results in a lack of uptake in the hepatobiliary phase; most HCCs are hypointense in the hepatobiliary phase (Figure 7) whereas most non-HCC cirrhosis-associated nodules are iso- or hyperintense secondary to preservation of OATP 8 expression[66]. It is however important to note that 5%-10% of HCCs are iso- or hyperintense to liver in the hepatobiliary phase[67,68]. The addition of hepatobiliary phase sequences improves sensitivity of diagnosis of HCC by 5%-15% with Gd-EOB-DTPA (Figure 13)[69,70] and around 10% with Gd-BOPTA[71]. Interestingly, a study showed that 96% of HCC lacking arterial enhancement with subsequent washout (seen primarily in early HCCs) were hypointense during the hepatobiliary phase[72]. This is likely the most significant benefit of the use of hepatobiliary contrast agents in determination of HCC. It is important to note however that all non-hepatocellular lesions appear hypointense on the hepatobiliary phase. Hence, it is imperative to interpret this phase in conjunction with that of the other sequences.
Addition of a non-contrast enhanced phase (NC-CT) to a multi-phase CT study has been found to useful in providing a baseline for assessment of arterial phase enhancement and improving diagnosis of HCC[73]. The current practice of characterizing enhancement and washout with dynamic CT is performed qualitatively by visual assessment of the lesion relative to the surrounding liver parenchyma. This assessment is thus dependent upon variables that can influence liver attenuation such as steatosis and iron deposition. With the addition of NC-CT, even if a lesion was found to be isodense on the arterial phase, the observation of hypodensity on NC-CT would imply hypervascularity of the lesion.
The improved temporal resolution of newer and faster multidetector CT systems allows perfusion studies of the liver[74]. CT perfusion is a method to analyze hemodynamic changes in tissue; it allows for quantitative assessment of various parameters such as tumour blood flow, blood volume, mean transit time and permeability-surface area product[75]. The liver has dual blood supply and neoarterialization occurs with the development of HCC resulting in alteration of perfusion parameters. Blood flow, blood volume, arterial perfusion and hepatic perfusion index were found to be significantly higher in HCC relative to hepatic parenchyma[76,77]. Sahani et al[75] also found that mean blood flow, blood volume and permeability-surface area product were higher in well-differentiated HCC than in moderately or poorly differentiated tumours. Additionally, it has been suggested that perfusion parameters can be utilized as biomakers to monitor treatment response in tumours[78].
Conventional MDCT uses a polychromatic X-ray spectrum provided by a single X-ray tube whereas dual-energy CT (DECT) uses two different energy spectra produced by two different kVp settings. This is achieved by using two X-ray tubes at different tube currents with two corresponding detectors or with a single source X-ray tube with fast peak kVp switching. It is based on the premise that tissues demonstrate different attenuation at different energy levels. This allows for enhanced tissue differentiation and characterization, reduction of artifacts, iodine conspicuity and improvement of contrast-to-noise ratio (CNR) and signal-to-noise ratio (SNR)[79]. The attenuation of a material increases as its photon energy decreases. Materials with higher atomic numbers, such as iodine, portray a much greater attenuation increase as the photon energy decreases. This provides the basis for greater attenuation separation between tumour and liver parenchyma[80]. Gao et al[81] found that monochromatic images obtained using single source DECT can enhance the CT attenuation of iodine contrast media at lower energy levels in the enhanced arterial phase which aids in the identification of more and smaller HCC lesions (Figure 14). DECT may also improve detection of fat within hepatic lesions which may be indicative of HCC[82].
MR elastography (MRE) is a technique which is used for quantitative assessment of tissue stiffness and its most common clinical application is for evaluation of liver stiffness in the diagnosis of hepatic fibrosis[83]. In this technique, hepatic stiffness is measured using low-frequency mechanical shear waves generated by a source that is propagated through the liver. Liver stiffness increases systematically with stage of fibrosis; using a shear stiffness cut-off value of 2.93 kPa, the predicted sensitivity and specificity for detecting all grades of liver fibrosis is 98% and 99% respectively[84]. Malignant tumours have greater stiffness values than benign tumours and normal liver parenchyma[85-87]. Hence, MRE has shown to be a promising non-invasive tool for the imaging and characterization of solid hepatic tumours (Figure 15). A threshold value of approximately 5.0 kPa may be useful for differentiating benign focal lesions from malignant tumours[85]. The utility of MRE for differentiation of malignant tumors of liver is not well established and still under research.
MR spectroscopy (MRS) allows for the non-invasive interrogation of the presence and concentration of various metabolites in tissue and hence aid in the provision of information with regards to tumour pathophysiology and metabolism[88]. It utilizes the magnetic properties of certain atomic nuclei; the more common ones employed are proton (1H), phosphorus-31 (31P) and carbon-13 (13C). 1H is the most commonly studied as it has the highest sensitivity. In liver tumour studies, the lactate resonance is related to energy metabolism of the tumour. Proton resonances of mobile lipids and the peak of total choline have been investigated as biomarkers to identify malignant tumours[88]. An increase in phosphomonoesters is associated with liver tumour progression and successful treatment is associated with a reduction of these levels[89-91]. Hence, 31P MRS can potentially be used for treatment monitoring. MRS with 13C has barely been utilized to examine human liver metabolism due to its technical complexity and relatively low sensitivity[88]. However, new techniques such as hyperpolarization of 13C-labeled glutamine has shown potential in the detection of small HCC in a cirrhotic liver[92].
DWI is a technique used for imaging molecular movement or diffusion. ADC in conventional DWI is influenced by two types of molecular movement: molecular diffusion and microcirculation in vessels (perfusion-related diffusion)[93]. With high b-values, the effect of perfusion-related diffusivity is largely eliminated and the ADC value can estimate true molecular diffusion. The effect of perfusion-related diffusion, however, cannot be completely removed. Hence, DWI performed using a range of low and high b-values or intravoxel incoherent motion imaging (IVIM) imaging has been employed to measure diffusion and perfusion-related diffusion separately[94,95]. Post processing of IVIM sequences can generate several parameters including: the D value (true diffusion that reflects intra- and intercellular molecular movement) and the pseudo-diffusion coefficient D* which reflects the microcirculation in the vessels or perfusion-related diffusion; perfusion fraction (Pf) and ADC. D and D* aspects can be separated using biexponential fitting of the DWI data[95]. It is well-established that ADC values of malignant hepatic lesions are lower than that of benign lesions[96,97]. However, measured ADC values show substantial variability secondary to differences in choice of b-values[98]. Diffusivity values acquired using the IVIM model, however, are less influenced by the choice of b-values and may provide consistent and reproducible results[99]. Ichikawa et al[99] found that both the D and D* value of malignant hepatic lesions was suppressed compared with that of benign lesions and that the D value was a more reliable parameter between the two. IVIM-derived D values have been found to show significantly higher accuracy compared with ADC in differentiating high- from low-grade HCC[100]. Additionally, since D* reflects microcirculation, it may be possible to assess the effect of antiangiogenic drugs in HCC[101]. The early results show promise of IVIM in differentiating HCCs from benign nodules, however evidence for clinical utility is still lacking.
Positron emission tomography (PET) with the glucose analogue 2-(18F)fluoro-2-deoxy-D-glucose (FDG) is extensively used in oncologic imaging. FDG-PET may be able to demonstrate increased uptake with HCC (Figure 10), however, it may miss 30%-50% of HCC lesions as the uptake is similar to the uptake in surrounding liver parenchyma[102-104]. Fluro-2-deoxy-D-Galagctose (FDGal) is touted as a hepatocyte-specific PET tracer for HCC; it is a tracer for galactose metabolism and avidly accumulates in the liver compared to other tissues[105]. It has potential not only as a PET tracer for detection of extra- but also intra-hepatic HCC. Sørensen et al[106] presented the first clinical study on the potential use of FDGal PET/CT for the detection of HCC and found high specificity in a retrospective study. Detection of HCC were comparable to that of multiphase contrast-enhanced CT. Additionally, FDGal PET/CT detected more nodules than other imaging modalities at the time of investigation and follow-up revealed rapid progression in those lesions. This may indicate the ability of FDGal to detect more lesions at earlier time points than conventional morphology based imaging modalities.
Imaging plays an imperative role in the diagnosis of HCC. The hallmark feature of arterial enhancement followed by washout is highly specific in at-risk patients and forms the foundation of current diagnostic guidelines. Difficulties in accurate diagnosis are largely secondary to lesions of small size. Ancillary features can aid in diagnosis and its use has been incorporated into Li-RADS. The use of hepatobiliary contrast agents has shown great promise in several studies with the ability to identify high grade dysplastic nodules and early HCC prior to neo-arterialization and progression to overt HCC, it may well be endorsed in future guidelines. Several other imaging techniques have also been investigated, many of which show potential that may shift the paradigm of HCC imaging assessment in the future.
P- Reviewer: Lam V, Sicklick JK, Yang T S- Editor: Yu J L- Editor: A E- Editor: Wang CH
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