Many pathophysiological processes can lead to diffuse parenchymal liver diseases and the end-result of all chronic liver diseases (CLD) is healing by fibrosis and regeneration.1 Hepatic fibrosis, left untreated, progresses to cirrhosis and its associated complications, a major cause of death worldwide. For an effective cure, hepatic fibrosis should be diagnosed early and monitored during treatment. Liver biopsy is the gold standard but limited due to its invasiveness, sampling error, and intra- and interobserver variability. Non-invasive tests are preferred in the management of CLD.2,3,4 Several serum tests for liver function and markers of liver fibrosis are available and have moderate sensitivity and specificity; however, they are confounded by a wide range of extrahepatic diseases.5 Imaging plays an important role in evaluation of CLD and its complications.
Conventional ultrasound (US), computed tomography (CT) and magnetic resonance imaging (MRI) are routinely used to evaluate CLD. These methods assess morphological changes in the liver that are typically seen in the advanced stages (cirrhosis) and are not sensitive for detection of early hepatic fibrosis. However, US, CT, and MRI are excellent methods for evaluating complications, including portal hypertension, ascites and hepatocellular carcinoma. For early detection, quantitative techniques are most useful. MRI is the most promising technique for quantification of hepatic steatosis, iron overload, and hepatic fibrosis.6,7
Non-alcoholic fatty liver disease (NAFLD) is now the most common cause of CLD and the leading cause of liver transplantation. NAFLD is a major health burden worldwide, with great implications for medical resources, and is the most common CLD encountered by radiologists.8,9 In this review, we will briefly review the quantitative assessment of hepatic steatosis and iron overload and focus on current and emerging techniques for evaluation of liver fibrosis.
In the normal liver 5% or fewer hepatocytes have fatty change. Hepatic steatosis or fatty liver results from excessive accumulation of triglycerides within hepatocytes, and a condition that affects nearly 25-35% of the US population.10 Hepatic steatosis can result from many causes including alcohol, drugs, storage disorders, infection and pregnancy. The most common cause of hepatic steatosis is NAFLD, which is associated with obesity and metabolic syndrome.10 NAFLD is a spectrum of disease, with 70-80% of patients having the benign, non-progressive non-alcoholic fatty liver (NAFL). About 20-30% of have progressive non-alcoholic steatohepatitis (NASH), characterized by inflammation and ballooning of hepatocytes, and about 5% of NASH patients progress to cirrhosis.11,12 NAFLD patients are also susceptible to liver failure, as well as cardiovascular and renal comorbidities.13 As hepatic steatosis is a biomarker of NAFLD, detection and quantification of fat is important.
Ultrasound is useful for detecting fatty change in the liver; however, the increased echogenicity of the liver parenchyma is nonspecific. In addition, the quantification of fatty changes with grayscale ultrasound is inaccurate. A new technique, controlled attenuation parameter (CAP), is now available with elastography to quantify the liver fat. CAP can easily detect steatosis >10%.14 The utility of CAP for hepatic steatosis is still being evaluated.
The attenuation of a normal healthy liver on non-contrast enhanced CT ranges from 50-65 Hounsfield Units (HU) and is denser than the spleen parenchyma and the hepatic vasculature.15,16 Non-contrast CT is more accurate in qualitatively diagnosing moderate to severe hepatic steatosis than it is in mild to moderate steatosis. Hepatic steatosis can be diagnosed when liver attenuation < spleen attenuation or when liver attenuation < 48 HU.15 Increased density of the liver vessels compared to the liver parenchyma (Figure 1) is associated with 30% steatosis. Moderate-to-severe hepatic steatosis can be diagnosed with 100% specificity when liver attenuation is <40-42 HU, hepatic-splenic attenuation ratio is < 0.8, or a hepatic-splenic attenuation difference is ≤-10 HU with 73-82% sensitivity for moderate-to-severe hepatic steatosis.17,18 Due to the risks associated with ionizing radiation exposure, CT is not recommended for evaluating hepatic steatosis.
MRI is the most useful technique for evaluating hepatic steatosis. The various techniques for detecting and quantifying hepatic steatosis include fat suppression, chemical shift imaging (CSI), frequency selective imaging, and MR spectroscopy (MRS). Qualitative in-phase and opposed-phase imaging (IP/OP) is widely available and can easily detect fat in the liver (Figure 1). However, the range of hepatic steatosis that can be quantified is only 0-50% and the sequence is easily affected by the presence of iron and other paramagnetic substances. MRS is the most accurate imaging technique capable of detection of small quantities of liver fat and for followup.18,19 However, MRS analysis is limited to a single anatomical location, requires technical expertise and additional post-processing time. Hence, MRS remains a major research tool widely used in clinical trials and not in routine clinical practice.
The accuracy of proton density fat fraction (PDFF) measurement using chemical shift encoded methods is similar to that of MRS and is easily implemented in MRI scanners. These are typically performed with single-breath-hold sequences that allow coverage of the entire liver. Unlike the previously mentioned MRI techniques, PDFF pulse sequences have been optimized such that they are minimally affected by magnetic field inhomogeneity and T2* effects. A recent study conducted by Serai et al20 showed that PDFF estimation using multipoint Dixon techniques was highly reproducible across readers, magnetic field strengths and across vendor imaging platforms. The advantage of these multi-echo-based sequences is that, in addition to PDFF, they also generate R2* (or T2*) maps, IP and OP images, and water and fat images (Figure 2). The ease of quantification by drawing regions of interest (ROI) over liver parenchyma makes it practical for clinical use. The advantages and disadvantages of various MRI techniques for the quantification of fat is summarized in Table 1.21,22
Liver iron overload results from abnormal accumulation of iron in the hepatocytes, Kupffer cells, or both.23 The condition is associated mostly with hereditary hemochromatosis, transfusion-related iron overload, and chronic liver pathologies.24 Ultrasound is not a suitable modality for evaluating liver iron overload, as it cannot detect iron deposits. On non-contrast CT, iron overload results in increased liver density (≥ HU); however, co-existent hepatic steatosis, which commonly presents as reduced attenuation on CT, can reduce detection sensitivity. Similarly, other pathologies that can increase the liver density on CT, such as Wilson disease, colloidal gold treatment and amiodarone administration, can decrease the specificity of CT. Consequently, CT is not considered a reliable modality for the diagnosis and quantification of liver iron overload.
MRI is a well-established modality for assessing liver iron concentration (LIC) and is a good alternative to biopsy. IP/OP images, which are part of standard liver MRI protocols, can also detect iron. A signal drop is noted on IP images in the case of iron (Figure 3), while fat causes a signal drop on OP images. Iron causes shortening of T1, T2, and T2*, and this shortening is more pronounced with T2* images. Therefore, T2*-weighted images have higher sensitivity and are more routinely used for detecting iron.25,26 The two major methods used in quantifying liver iron overload are signal intensity ratio (SIR) and relaxometry. SIR method calculates the signal intensity (SI) of the liver and another tissue with no iron accumulation (eg, muscle) and determines the ratio to quantify the LIC.27,28 Limitations of SIR include its inability to quantify LIC >350μmol Fe/g and tendency to overestimate LIC. Relaxometry methods, on the other hand, calculate the SI of the liver across several echo times and measure the T2 or T2* values depending on the obtained sequence. T2 or T2* values are inversely related to iron concentration. But, R2 or R2* values (1000/T2 or T2*) are directly related to the iron concentration and increase linearly with LIC determined by liver biopsy. R2* and T2* calculation plays a crucial role in identifying the extent of LIC for treatment with iron-chelating agents. The major advantage of relaxometry is its ability to also calculate myocardial iron overload, while its limitations include the requirement of specialized software which is not readily available.29 A T2* value <18ms is considered to be liver iron overload.30 A recent study conducted by Galimberti et al31 showed that an R2* cut-off value of 147.1 Hz (T2* value of 6.8ms) discriminates moderate and severe hepatic iron overload from absent and mild hepatic iron overload. MR field strength is an important factor in measuring LIC. Although high field strengths have an advantage in identifying tissues with low iron content, the susceptibility to artifacts reduces the sensitivity for detection and quantification of severe iron overload.32,33 Chemical shift-encoded sequences that automatically generate PDFF and R2 * maps for fat and iron quantification, respectively, are useful for clinical practice without the need for additional post-processing. Liver iron quantification with MRI should be tailored to the clinical need and benchmarked against the institutional laboratory values of serum and blood iron levels, as the test results are variable with different laboratory equipment.
CLDs are characterized by ongoing inflammation and fibrosis. Chronic inflammation leads to potentially reversible early hepatic fibrosis and when untreated progresses to cirrhosis with the cross-linking of collagen fibres and the formation of regenerative nodules.34 Regression of hepatic fibrosis can occur, with significant reduction in fibrosis burden, especially when treatment is started early. Hepatitis C can be cured with new antiviral drugs and lifestyle changes can significantly reduce hepatic steatosis. Non-invasive detection and staging of hepatic fibrosis is important in the management of chronic liver diseases.
Liver fibrosis causes coarse echogenicity of liver parenchyma on US, a nonspecific feature that can be seen with fatty change and inflammation. Although grayscale US can identify a cirrhotic liver in CLD, it is unreliable for identifying mild changes, 35, 36 and is often unable to differentiate between mild and severe fibrosis.37 US however can detect morphological changes in advanced fibrosis with moderate accuracy.38
Ultrasound-based Elastography methods include vibration controlled transient elastography (VCTE), point shear wave elastography (pSWE) and shear wave elastography (SWE). These are simple to use and can detect liver cirrhosis with high accuracy. The advantages and limitations of VCTE, pSWE and SWE have been summarized in Table 2.39 Although US elastography is an inexpensive and accurate technique for diagnosing liver cirrhosis, it has significant limitations and confounders (Tables 2,3). The methods are operator-dependent and in general have reduced sensitivity and specificity in detecting early fibrosis.40,41
Diagnosing fibrosis/cirrhosis on CT relies on morphological changes, such as irregular or nodular liver surface, blunt edges, heterogeneous texture, widened fissures, segmental atrophy and hypertrophy and features of portal hypertension.42 CT is useful for evaluating complications such as esophageal varices, hepatocellular carcinoma, and ascites. Nevertheless, CT is not the preferred modality for primary diagnosis of liver fibrosis because of the risk of radiation and its lower sensitivity for early hepatic fibrosis. Clinically occult liver fibrosis is often underdiagnosed in routine abdominal CT, and its sensitivity (77.1%–84.3%) and specificity (52.9%–67.6%) for liver cirrhosis is mediocre.43
Conventional MRI probably has slightly better accuracy than CT as parenchymal heterogeneity due to underlying fibrosis can be better appreciated on MRI sequences which helps to detect earlier stages of fibrosis. However, conventional MRI is still limited in the detection of early hepatic fibrosis and hence, not reliable for disease staging. Newer MR imaging techniques such as diffusion-weighted imaging (DWI), perfusion imaging, texture analysis, hepatocellular function imaging, t1-p imaging, susceptibility weighted imaging (SWI) and MR elastography are now being explored for application in hepatic fibrosis. 44,45
Diffusion weighted imaging is useful for identifying advanced fibrosis and cirrhosis, but the technique lacks standardization across platforms and has low accuracy, as apparent diffusion coefficient (ADC) values overlap between normal liver and fibrotic/cirrhotic liver.46 Extrapolating the DWI technique, utilizing several b-values an intravoxel incoherent motion (IVIM) analysis is performed, especially with low b-values (<200 s/mm2). Several studies have evaluated the relationship between ADC and fibrosis stage, with conflicting results.46 While some studies have noted a reduction in ADC values with increasing fibrosis stage, a study46 observed this pattern only in live, not dead, rats, suggesting that perfusion rather than diffusion is affected by fibrosis stage. DWI and IVIM techniques are limited by lack of standardization and have confounding factors of fat and iron deposition in the liver.47
MRE of the liver was introduced into clinical practice in 2007. MRE is currently the most accurate non-invasive MRI technique for detecting and staging of liver fibrosis.29,38,48 MRE can reliably differentiate NAFLD from NASH prior to patients developing liver fibrosis.49 Similar to ultrasound based shear wave elastography, MRE utilizes propagating shear waves produced by a vibrating passive driver placed over the liver and imaged with a special phase encoded MRI sequence. The wave information is automatically processed with software and produces maps for liver stiffness measurement.50 Liver stiffness increases in higher stages of fibrosis and is easily distinguishable from normal liver stiffness (<2.5kPa) (Figure 4). Liver stiffness measurement with MRE has proven to have a higher sensitivity and specificity for each stage of fibrosis when compared to DWI.51 MRE has 98% sensitivity and 99% specificity detection of hepatic fibrosis and is considered an alternative gold standard to liver biopsy. MRE can be easily added to standard liver MRI protocols, allows a large sample of liver to be assessed, is not influenced by ascites, obesity or hepatic steatosis, is unaffected by intravenous contrast administration, and has high intra- and interobserver agreement for measurement of stiffness. However, MRE has a few limitations and these include potential failure in patients with moderate-to-severe iron accumulation due to low signal of the liver parenchyma, additional time required for positioning the driver, and lack of availability at all centres. Clinically useful LSM cut-offs are provided in Table 4.
MRI techniques estimating fractional extracellular space estimation52 and magnetic transfer ratio (MTR) have been less successful in differentiating normal from cirrhotic liver.53 MR perfusion requires the use of intravenous contrast and early studies have reported encouraging results54 but has technical limitations, requires patient co-operation for several breath holds and is susceptible to motion artifacts. Perfusion imaging is also not widely available.
T1ρ imaging is another MRI technique which uses the spin-lattice relaxation time for evaluation of hepatic fibrosis. It has been shown useful for hepatic fibrosis staging, as demonstrated by a preclinical study conducted on rat livers.55 Preliminary T1ρ MRI studies have shown that, compared to normal liver, fibrotic liver exhibits higher T1ρ values and has high diagnostic accuracy to differentiate normal from cirrhotic livers.56,57 However, this technique is influenced by magnetic field inhomogeneity and breath-hold artifacts. Further evaluation with more subjects is required to establish its role in assessing liver fibrosis.
Texture analysis is an emerging method for evaluation of hepatic fibrosis and can be performed with any technique. Currently there is no standardized approach and several different software methods exist. Diagnostic performance of texture analysis is variable.58, 59
Hepatocellular function imaging can be performed easily on any clinical MRI scanner; however, this requires hepatobiliary contrast medium– gadoxetate sodium--that is invasive and adds scan time. Relative enhancement parameters are derived from hepatobiliary phase and non-contrast-enhanced T1-weighted images. The enhancement is reduced in hepatic fibrosis and cirrhosis. Early studies have been encouraging and shown high accuracy of 0.93 for diagnosis of advanced fibrosis. This technique needs further evaluation.
Recent advances in diagnostic imaging have led to an early and improved detection of diffuse liver diseases. MRI is the main modality for imaging diffuse liver diseases and provides accurate quantification of liver fat, iron, and fibrosis.
Mathew RP, Venkatesh SK. Imaging diffuse liver disease. Appl Radiol. 2019;48(5):13-20.
Dr. Mathew is a Clinical Fellow in Body Imaging, in the Department of Radiology & Diagnostic Imaging, at the University of Alberta Hospital, Edmonton, Alberta, Canada; and Dr. Venkatesh is a Professor of Radiology at the Mayo Clinic College of Medicine, Rochester, MN. The authors have no conflicts of interest to disclose.