Noninvasive imaging evaluation of LF
Noninvasive imaging approaches allow detection, staging and monitoring of LF. Morphologic alterations of the liver and signs of portal hypertension are the most significant imaging manifestations of end-stage LF (Table 1) with high specificity. However, these signs demonstrate limited sensitivity and are visible only in advanced cases, thus not being accurate for staging LF over its entire spectrum of severity.8,9 In patients with less advanced LF, the liver parenchyma is usually normal in appearance or exhibits only subtle, nonspecific heterogeneity. In addition, extrahepatic findings, which may include ascites, splenomegaly and portosystemic varices, may be present in other conditions, hence not being specific for LF.10 Luckily, novel emerging imaging techniques are being validated to measure LF, as discussed below. Advantages and limitations of each imaging modality are documented in Table 2.
Table 1.Imaging signs of liver fibrosis
| Liver morphology | Nodular liver surface (surface nodularity) |
| Heterogeneous parenchyma |
Expanded gallbladder fossa
Altered liver size |
| Hypertrophy of caudate lobe and left lobe |
| Atrophy of the segment IV and medial segment of left hepatic lobe |
| Hepatic artery | Increased diameter and tortuosity |
| Hepatic veins | Decreased diameter and altered straightness |
| Portal venous system | Dilation of portal, splenic and superior mesenteric veins |
| Spleen | Splenomegaly |
| Portosystemic collateral circulation | Formation of gastroesophogeal, paraesophogeal, left gastric, short gastric, umbilical and abdominal wall varices with engorged and tortuous appearance
Splenorenal/gastrorenal shunts and retroperitoneal shunts |
| Ascites | |
Table 2.Major advantages and limitations of available non-invasive imaging methods used for liver fibrosis evaluation
| Test | Advantages | Limitations |
| Ultrasound | Conventional ultrasound | Widely available and inexpensive
real-time | Considerable interobserver variability
Relatively low specificity |
Reproducible and without ionizing radiation
Highly sensitive in detecting portal and hepatic vein thrombosis | Interference by intestinal gas, obesity, patient respiration, fasting status, collateral pathways, hepatic steatosis and inflammation |
| Able to measure intrahepatic and systemic hemodynamic changes | |
| Contrast-enhanced ultrasound | Able to measure intrahepatic and systemic hemodynamic changes with better contrast than Doppler US | Require injection of intravenous contrast agents and operator expertise |
| More expensive than conventional ultrasound |
| Ultrasound elastography | Transient elastography | Widely available and well validated in most etiologies of chronic liver diseases
Highly portable
Shear wave frequency well controlled | No anatomic images captured or the exact measurement location recorded during examination
Restricted to patients with no obesity, narrow intercostal space or ascites |
| Lack standardized cut-offs for each liver fibrosis stage |
| Point shear wave elastography | Manually selected ROI allows quantitative analysis of liver stiffness and enables more reliable monitoring with less sampling variability | More expensive and expertise required, whereas less validated than transient elastography |
Generates more robust shear waves than transient elastography
Can be applied in patients with obesity or ascites | Shear wave frequency is hard to control and therefore may introduce measurement variability |
| 2D-shear wave elastography | Ultrafast imaging allows generation of real-time quantitative elastograms | Same limitations as point shear wave elastography |
| Several ROIs can be placed on the elastograms |
| Reduced sampling variability |
| Computed tomography | Conventional computed tomography | Widely available and well validated | Ionizing radiation exposure |
| Allows a full cross-sectional visualization | Require injection of intravenous contrast agents |
| Signs of morphologic liver alterations, cirrhosis and portal hypertension are specific | Not sensitive enough to detect and stage less advanced fibrosis |
| Computed tomography perfusion imaging | Allows quantitative measurement regional and systemic hemodynamic changes | Less available or validated than conventional computed tomography |
| More expensive and more expertise required than conventional computed tomography |
| Magnetic resonance imaging | Conventional magnetic resonance imaging | No ionizing radiation
Liver fibrosis manifests a specific enhancement pattern
Aids in differentiation of focal fibrosis from cirrhosis-related vascular lesions | More expensive and time-consuming than conventional computed tomography
Elevated risk of nephrogenic systemic sclerosis due to gadolinium contrast agent injection |
| Magnetic resonance elastography | High diagnostic accuracy for advanced fibrosis and cirrhosis
Robust
Can be applied in patients with obesity and/or ascites
Able to assess a larger proportion of the liver than ultrasound elastography, which may reduce sampling variability for patient monitoring | High cost and time-consuming
Limited availability
Limited application in patients with iron overload, steatosis, vascular congestion or cholestasis
Acquired with inconsistent breath holds
Insufficient evidence regarding its diagnostic performances |
| Diffusion weighted magnetic resonance imaging | Widely available and relatively easy to perform
Reproducible
Robust
Apparent diffusion coefficient well correlated with liver fibrosis stage
Intravoxel incoherent motion model can add additional diagnostic benefits | Results may be influenced by perfusion effects, hepatic steatosis, edema, iron accumulation and liver inflammation
Sensitive to susceptibility and motion-related artifacts
Acquisition relies significantly on several imaging parameters including field strength and b values |
| Gadoxetic acid disodium | Provides both hemodynamic information and lesion function information in a single examination | Less validated than nonspecific gadolinium chelates
Hepatobiliary phase hypointensity is not specific for hepatocellular carcinoma |
| High diagnostic accuracy for focal liver lesions |
| Early detection of hepatocellular carcinoma |
| Can measure preoperative liver function |
| Magnetic resonance perfusion imaging | Allows quantitative measurement of regional and systemic hemodynamic changes | Time-consuming |
| Less available or validated than conventional magnetic resonance imaging |
| Can be affected by the cardiac status, fasting state, hepatic congestion, inflammation, liver masses, and hepatic portal venous flow |
| Image quality not sufficient for assessing small nodules |
| May require a second contrast material injection |
US
Conventional US: Gray-scale and Doppler US are the conventional US techniques used as first-line imaging examinations for patients with suspected LF. These methods are easy to perform, real-time, noninvasive, reproducible, inexpensive, well validated and widely available, with no ionizing radiation. Besides, they are highly sensitive in detecting portal and hepatic vein thrombosis.11 Parameters comprising liver surface nodularity, altered liver size and/or splenomegaly, bluntness of liver edge, altered liver parenchymal echogenicity with coarsened echotexture, and altered portal vein blood flow velocity and effective portal liver perfusion, have been suggested to be useful in evaluating LF.11,12
However, the diagnostic capacity of conventional US in LF can be limited due to considerable interobserver variability, low specificity, and interference by intestinal gas and obesity.13 Besides, the Doppler US can be affected by patient respiration, fasting status, collateral pathways, hepatic steatosis and inflammation.14,15
Contrast-enhanced US (CEUS): CEUS is an emerging US modality based on intravenous administration of specific contrast agents. The contrast media are gas-filled microbubbles which significantly enhance the intravascular blood flow against other tissues.8,16 It allows for the evaluation of hemodynamic changes during LF evolution. The hepatic vein arrival time (HVAT), defined as the time taken for the contrast media to reach the hepatic vein (HV) after injection, was reported to have negative correlations with the severity of LF or portal hypertension.17,18 As LF evolves, increased formation of sinusoid capillaries and arterio-/portovenous shunts can result in decreased HVAT.16 Kim et al.19 reported that, HVAT was negatively correlated with HV pressure gradient (r2 = 0.545, p < 0.001), and that with 14 seconds as a cut-off value, HVAT achieved sensitivity, specificity and the area under the receiver operating characteristic curve (AUROC) of 0.927, 0.867 and 0.973, respectively, for evaluating clinically significant portal hypertension. In addition, a shorter HVAT was significantly associated with esophageal varices and worse Child-Pugh score.
CEUS is a simple and noninvasive approach for characterizing hemodynamic changes of LF and portal hypertension. However, CEUS is more expensive than conventional US and requires injection of corresponding intravenous contrast agents and considerable operator expertise. These disadvantages may limit its application in routine clinical practice.
US elastography: Imaging-based elastography is an emerging technology that measures tissue stiffness and other mechanical properties noninvasively.20,21 Evaluated with elastography, share wave has particle motion perpendicular to the direction in which the wave propagates. The traveling velocity of shear waves has been validated to correlate with tissue stiffness: shear waves travel faster in stiff tissues (inflamed or fibrotic liver) and slower in soft tissues (normal or fatty liver).22,23 US elastography is able to assess liver stiffness, which increases due to fibrosis in CLDs, by tracking and measuring the speed of shear waves via liver parenchyma. Currently, shear wave imaging (SWI) is the most widely used US elastography technique for evaluating LF. SWI permits quantitative assessment of tissue stiffness and stiffness-related parameters by tracking shear waves propagating through the liver.20
Three major SWI-based techniques, including transient elastography (TE), point shear wave elastography (pSWE) and two-dimensional shear wave elastography (2D-SWE), are commercially available today.24 Among these approaches, TE is not an imaging technique, while pSWE and 2D-SWE are both imaging techniques incorporated in US scanners.
TE is the first US-based type. TE is widely available and well validated in hepatitis C virus (HCV) and chronic alcoholic liver disease-related LF, and to a lesser extent in hepatitis B virus (HBV) and nonalcoholic fatty liver disease (NAFLD) patients.25–27 In TE, liver stiffness is evaluated by tracking the speed of shear waves propagating through the liver. The shear waves are generated by an ultrasound transducer, which is usually placed through an intercostal space above the right liver lobe. Propagation of the shear wave is tracked with its speed measured and the tissue stiffness reported in the form of kilopascals (kPa). A shear-wave propagation graph is displayed after each acquisition.
It has been suggested that TE is useful in discriminating no and mild fibrosis (F0-F1) from advanced fibrosis and cirrhosis (F3-F4); however, the accuracy is poor among the early stages of LF. Sporea et al.28 included 199 consecutive patients and reported that, compared with liver biopsy, an optimal cut-off value of 6.8 kPa could achieve 59.6% sensitivity and 93.3% specificity for significant fibrosis (≥ F2), with an AUROC of 0.773. Their study indicated that 6.8 kPa was the best cut-off value to distinguish significant fibrosis from no or mild fibrosis, with acceptable diagnostic accuracy.
In order to further explore the diagnostic accuracy and determine optimal cut-off values of TE for LF assessment, several meta-analyses have been conducted. Friedrich-Rust et al.29 investigated 50 studies and reported that for the detection of significant fibrosis (≥F2), TE demonstrated an AUROC of 0.84 with an optimal cut-off value of 7.6 kPa, while for cirrhosis (F4), the best cut-off value was 13 kPa with an AUROC of 0.94. However, with 40 studies analyzed, Tsochatzis et al.30 reported that, although pooled sensitivity and specificity was 0.79 and 0.78 for F2 and 0.83 and 0.89 for F4, no optimal cut-off for individual fibrosis stage was achieved because cut-offs ranged widely and presented significant overlaps within and between LF stages. Their studies implied that, for each LF stage, the best cut-off values are difficult to determine because these values are highly dependent on the etiology of CLD.
Recently, TE has been recommended by the American Gastroenterological Association, European Association for the Study of Liver and European Federation of Societies for Ultrasound in Medicine and Biology guidelines to be useful in assessing CLDs and chronic viral hepatitis-related LF.31 The American Gastroenterological Association guidelines recommended 12.5 (±1) kPa as the optimal cut-off value for diagnosis of cirrhosis (F4) in patients with chronic HCV infection and alcoholic liver disease, whereas 11.0 (±1) kPa is recommended for chronic HBV patients.32 Moreover, the European Federation of Societies for Ultrasound in Medicine and Biology guidelines issued values above 6.8–7.6 kPa as being highly correlated with the presence of significant fibrosis (≥F2) and that those ranging between 11.0–13.6 kPa may indicate cirrhosis (F4).33 Several algorithms combining TE and serum biomarkers have been proposed to increase diagnostic accuracy and reduce the number of biopsies, mainly in viral hepatitis.34–36 Recently, the European Association for the Study of Liver-ALEH have suggested algorithms for noninvasive tests in first-line fibrosis staging in patients with hepatitis B and C infections37(Fig. 2).
TE is relatively inexpensive, highly portable, widely available, reproducible and easy to perform. However, the technique lacks standardized cut-offs for each fibrosis stage and may be limited in patients with ascites, obesity or narrow intercostal space. Most importantly, the exact measurement locations are not recorded because no anatomic image is captured with TE, which may introduce sampling variability for monitoring LF progress over time.
pSWE is a novel US elastography technique incorporated into conventional US scanners. In pSWE, a region of interest (ROI) of the liver is excited by a high-frequency acoustic radiation force impulse mechanically. This impulse causes tissue expansion and generates shear waves propagating perpendicular to the ultrasound beam axis.38,39 The speed of the shear wave is measured and reported in m/s, with a range between 0.5–5 m/s in different abdominal conditions.40
pSWE has been applied to assess LF of various etiologies in clinical practice. Recently, a meta-analysis of 1163 patients compared the diagnostic performances of TE and pSWE for LF. It reported that for diagnosing significant fibrosis (≥F2), the pooled sensitivity was 0.74 and specificity 0.83 for pSWE; while for TE, the summarized sensitivity and specificity was 0.78 and 0.84, respectively. In cases with cirrhosis (F4), the pooled sensitivity and specificity were 0.87 and 0.87 for pSWE, respectively, and 0.89 and 0.87 for TE. Their study demonstrated no statistically significant difference between the diagnostic accuracies of pSWE and TE for significant fibrosis (≥F2) or cirrhosis (F4).41
pSWE possesses several advantages. First, this technique permits quantitative evaluation of liver stiffness in a manually selected ROI, which enables more reliable patient monitoring and follow-up. Second, because the shear waves are generated locally within the liver, pSWE is more robust than TE and thus can be applied in patients with obesity and/or ascites. However, pSWE is more expensive, requires more expertise to perform, and is less available and validated by current studies compared with TE. Besides, the shear wave frequency is difficult to control precisely in the setting of pSWE, which is likely to introduce measurement variability.
2D-SWE technique, as the currently newest SWI-based method, applies acoustic radiation force focused at successively greater depths on an axial line to stimulate microscopic tissue movements and generate shear waves.42 The entire imaging plane is scanned with high temporal resolution in one acquisition by an ultrafast imaging technique. This allows the real-time generation of quantitative elastograms.43,44 Shear wave speed (m/s) or Young’s modulus (kilopascal) are reported to depict tissue stiffness in 2D-SWE.
Much effort has been devoted to comparing the diagnostic performances of 2D-SWE and other SWI-based methods for staging LF.44–48 Leung et al.46 investigated 226 patients and 171 healthy patients with liver biopsy as a reference standard. They reported the superiority of 2D-SWE over TE in diagnostic accuracy of all fibrosis stages. The AUROCs for 2D-SWE and TE, respectively, were 0.86 and 0.80 for LF ≥F1, 0.88, and 0.78 for ≥F2, 0.93 and 0.83 for ≥F3, and 0.98 and 0.92 for F4. However, another study comparing the diagnostic potential of TE, pSWE and 2D-SWE for LF found no statistically significant diagnostic difference between TE, pSWE or 2D-SWE for LF ≥F2 and F4 with 332 patients.45
2D-SWE can be applied in patients with ascites and is able to analyze multiple ROIs according to the elastograms, which reduces some of the possible sampling variability with TE and pSWE. Nevertheless, the applications of 2D-SWE in LF may have been limited due to its restricted availability and insufficient evidence concerning its diagnostic performance. Moreover, it is more expensive and requires more operator expertise. Therefore, further studies and intensive validations are encouraged to demonstrate its concrete role in LF staging and monitoring of its potential clinical superiority.
CT
CT and MR imaging are useful cross-sectional imaging modalities for LF. The diagnosis, staging and surveillance of HCC, a major consequence of CLDs and LF, are primarily established by multiphasic CT or contrast-enhanced MR imaging findings.49,50 Liver morphology changes, signs of cirrhosis and portal hypertension can be directly evaluated by CT in patients with end-stage LF, as mentioned above (Table 1) (Fig. 3). However, CT is not sensitive enough to detect and discriminate less advanced fibrosis.
CT perfusion imaging is a functional CT-based imaging technique which permits quantitative measurements of the hepatic and systemic hemodynamic changes in patients with LF.51–53 One study with 21 cirrhosis patients demonstrated that two parameters—splenic arterial flow and splenic clearance—were inversely correlated with hepatic venous pressure gradient, and that a splenic clearance cut-off value of 125 ml/min/100 mL yielded 94% sensitivity and 100% specificity for severe portal hypertension.51 This study suggested that CT perfusion can be applied to quantitatively evaluate portal hypertension in patients with LF.
MR imaging
MR imaging has been widely applied and well validated to assess LF and its complications. Nevertheless, early detection and accurate grading of LF with the use of MR imaging remains one of the major challenging areas in liver imaging. Recently, several novel MR techniques have been introduced for this purpose.
Conventional MR imaging: Like CT, widely applied conventional MR imaging is able to identify liver morphology changes, signs of cirrhosis and portal hypertension in patients with advanced cirrhosis of various etiologies (Table 1). Administration of intravenous gadolinium-based contrast agents can further improve the visibility of LF and its related complications. On T1-weighted images, LF is often hyperintense.54 Moreover, LF usually displays a distinctive progressive enhancement pattern, of which the peak enhancement is usually observed during the late venous and equilibrium phases.54 However, cirrhosis-related vascular lesions, such as HCC and arterioportal shunts, can result in diagnostic confusion over focal fibrosis. Some imaging features may aid in the differential diagnosis. Presence of the specific enhancement pattern, reticular appearance and wedge-shaped configuration usually favor a diagnosis of LF.54
MR elastography: MR elastography is an emerging MR-based imaging modality which quantifies tissue stiffness noninvasively by assessing the propagation of mechanical waves through media55 (Fig. 4). As the shear waves propagate through the liver parenchyma, MR images are acquired with the use of a gradient-echo sequence. Similar to US elastography, the speed and wavelength of the shear wave through liver tissue in MR elastography is positively correlated with tissue stiffness.56 Therefore, liver stiffness can be evaluated by placing and measuring ROIs on the elastograms manually.
MR elastography has been validated for the assessment of LF since its introduction.57–59 A prospective study58 demonstrated that the diagnostic performance of MR elastography for LF was significantly better than that of ultrasound elasticity, pSWE, or the combination of ultrasound elasticity and pSWE. Other prospective studies59,60 reported that the frequency-independent cut-off values of MR elastography were 2.84 kPa for LF ≥F1, 3.18 kPa for ≥F2, 3.32 kPa for ≥F3 and 4.21 kPa for F4. The AUROCs were 0.9128, 0.9244, 0.9744 and 0.9931 for LF ≥F1, ≥F2, ≥F3 and F4, respectively. In a retrospective study, Venkatesh et al.61 demonstrated that MR elastography performed significantly better than conventional MR imaging for staging significant fibrosis (≥F2) (AUROC: 0.98.9 vs. 0.71–0.82, p < 0.001) and cirrhosis (F4) (AUROC: 0.93.5 vs. 0.61–0.80.5, p < 0.01).
The pooled diagnostic performances of MR elastography for LF staging, as reported by several meta-analyses, were good to excellent. Singh et al.62 conducted a meta-analysis of 12 retrospective studies and reported that, with liver biopsy as the gold standard, MR elastography demonstrated mean AUROCs of 0.84, 0.88, 0.93 and 0.92 for LF stage ≥F1, ≥F2, ≥F3 and F4, respectively. Their results suggested that MR elastography yielded excellent diagnostic accuracy for staging advanced fibrosis (≥F3) to cirrhosis (F4) and good performance regarding significant (≥F2) and mild fibrosis (≥F1) independent of sex, obesity, and etiology of CLD.
Using NAFLD cohorts, two cross-sectional prospective studies established head-to-head comparisons between MR elastography and TE for LF diagnosis in sequential patients. Park et al.63 consecutively enrolled 104 patients who underwent MR elastography, TE and liver biopsy in the United States. They demonstrated superior performance of MR elastography over TE in detecting any fibrosis (≥F1 vs. F0) (AUROC: 0.82 vs. 0.67, p = 0.0116), with cut-off values of 2.65 kPa for MR elastography and 6.10 kPa for TE, respectively. However, MR elastography did not increase accuracy for diagnosing other LF stages. This finding was not consistent with those of the other study, conducted by Imajo et al.64 in a Japanese cohort. Imajo et al.64 revealed that MR elastography was significantly more accurate than TE in diagnosing significant fibrosis (≥F2 vs. F0–1), advanced fibrosis (≥F3 vs. F0–2) and cirrhosis (F4 vs. F0–3), but not in any fibrosis (≥F1 vs. F0). This variation may have been attributed to the geographic heterogeneity of the included subjects and different cut-off values applied for each LF stage. Hence, further large scale prospective studies are encouraged to determine the optimal cut-off values of each LF stage for Western and Asian NAFLD populations.
Another prospective cross-sectional study was performed to compare the diagnostic accuracies between MR elastography and pSWE for LF in NAFLD patients. Cui et al.65 reported significantly higher accuracy of MR elastography than pSWE in detecting any fibrosis (≥F1 vs. F0) (AUROC: 0.799 vs. 0.644, p = 0.012), especially in patients with class II obesity (p = 0.007), but the differences were not significant for other LF stages.
MR elastography is highly accurate for diagnosing advanced fibrosis (≥F3) and cirrhosis (F4). This technique is robust, and therefore is feasible in obese patients and those with ascites. MR elastography is more sensitive for staging LF compared with other MR techniques. When compared with the US-based elastography techniques, MR elastography allows evaluation of a larger proportion of the liver, which is likely to reduce the sampling variability for patient monitoring over time.
However, MR elastography is limited on account of its high cost, long examination time, restricted product availability and its reliance on patient cooperation for breath-holds. Moreover, liver stiffness measurement with MR elastography may be affected in cases with hepatic iron overload, steatosis, vascular congestion or cholestasis. Therefore, further efforts are required to address the above limitations of MR elastography in liver imaging.
Diffusion-weighted MR imaging (DWI): DWI is a MR technique quantitatively assessing the random thermal diffusion ability of protons within the tissue, which is characterized by the parameter apparent diffusion coefficient (ADC).66 Fibrotic liver tissue usually manifests restricted diffusion; hence, the ADC value of the fibrotic tissue is significantly lower than that of the normal liver parenchyma. Therefore, ADC values are found to be negatively correlated with LF stages in most cases67,68 (Fig. 5).
A recent meta-analysis68 demonstrated DWI to have good diagnostic accuracy for staging LF, and the AUROC was 0.8554 for LF ≥F1, 0.8770 for ≥F2, 0.8836 for ≥F3 and 0.8596 for F4, respectively. Additional diagnostic benefits could be achieved when incorporating the novel DWI-derived intravoxel incoherent motion model into the conventional DWI for patients with LF.68,69
DWI is robust, reproducible, widely available and relatively easy to perform compared with other emerging MR techniques in LF evaluation. However, several challenges stand in the way of using diffusion parameters as surrogate markers for LF assessment. First, perfusion, iron overload, hepatic steatosis, liver inflammation and edema can confound the interpretation of diffusion parameters.54 Second, DWI is sensitive to motion-related artifacts and susceptibility, thus it may be challenging to obtain images with enough quality to conduct reliable quantitative analyses.54 Most importantly, the acquisition standardization of the ADC is of great value but challenging to achieve because DWI relies significantly on several imaging parameters such as field strength and b values. Therefore, intensive large-scale prospective studies are encouraged to focus on standardization of DWI and search for the best cut-offs of ADC value for each LF stage.68
Gadoxetic acid disodium (Gd-EOB-DTPA): Gd-EOB-DTPA is an emerging hepatocyte-specific hepatobiliary MR contrast material capable of, in a single examination, providing both the hemodynamic information during dynamic phases and good lesion characterization concerning hepatocyte function in the hepatobiliary phase (HBP) of the lesion.70
Gd-EOB-DTPA-enhanced MR imaging can optimize detection and differentiation of focal liver lesions, especially HCCs, in cirrhotic patients. During hepatocarcinogenesis, the uptake of Gd-EOB-DTPA by hepatocytes decreases progressively as a result of hepatic dysfunction. Therefore, most HCCs appear as hypointense foci in HBP.70 This enhancement pattern helps to differentiate HCCs, especially early HCCs with diagnostic confusions, from the hyper- or isointense dysplastic and regenerative nodules in HBP.71–74 However, HBP hypointensity is not specific for HCC because it can be found in some iron-rich dysplastic nodules75 and nonhepatocyte containing lesions, such as hemangioma, cholangiocarcinoma and metastases.76
MR imaging with Gd-EOB-DTPA can be applied to measure preoperative liver function in patients with cirrhosis. Quantitative analysis of Gd-EOB-DTPA uptake can help evaluate liver function, determine the optimal timing for liver resection, transplantation or invasive procedures, such as transjugular intrahepatic portosystemic shunt insertion, and predict postoperative liver failure risk.77–79
MR perfusion imaging: During the process of fibrosis, as liver parenchymal blood flow velocity and portal venous flow decrease progressively, hepatic arterial flow and formation of intrahepatic shunts usually increase over time.54 These hemodynamic alterations can be tracked with MR perfusion imaging. Several previous studies in patients with CLDs have demonstrated its feasibility in LF staging.80,81
Nevertheless, liver perfusion can be affected by systemic factors, such as the cardiac status and fasting state, or regional factors, including hepatic congestion, inflammation and space-occupying lesions. Therefore, liver perfusion may not correlate exclusively with LF stage. Moreover, image analysis of MR perfusion imaging is a time-consuming procedure and the image quality of small hepatic nodules is often poor, leading to the need of a second contrast agent injection.