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REVIEW ARTICLE
Ahead of print publication  

Ultrasound elastography


1 Department of Medical Ultrasound, Tongji Hospital, Tongji Medical College, Huazhong University of Science and Technology, Wuhan, Hubei Province, China
2 Department of Ultrasound, The First People's Hospital of Yueyang, Yueyang, Hunan Province, China
3 Department of Internal Medicine, Hirslanden Clinic, Bern, Switzerland

Date of Submission27-May-2021
Date of Acceptance30-Nov-2021
Date of Web Publication02-May-2022

Correspondence Address:
Christoph F Dietrich,
Department Allgemeine Innere Medizin, Kliniken Hirslanden Beau Site, Salem und Permancence, Bern
Switzerland
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Source of Support: None, Conflict of Interest: None

DOI: 10.4103/EUS-D-21-00151

  Abstract 


Physicians have used palpation as a diagnostic examination to understand the elastic properties of pathology for a long time since they realized that tissue stiffness is closely related to its biological characteristics. US elastography provided new diagnostic information about elasticity comparing with the morphological feathers of traditional US, and thus expanded the scope of the application in clinic. US elastography is now widely used in the field of diagnosis and differential diagnosis of abnormality, evaluating the degree of fibrosis and assessment of treatment response for a range of diseases. The World Federation of Ultrasound Medicine and Biology divided elastographic techniques into strain elastography (SE), transient elastography and acoustic radiation force impulse (ARFI). The ARFI techniques can be further classified into point shear wave elastography (SWE), 2D SWE, and 3D SWE techniques. The SE measures the strain, while the shear wave-based techniques (including TE and ARFI techniques) measure the speed of shear waves in tissues. In this review, we discuss the various techniques separately based on their basic principles, clinical applications in various organs, and advantages and limitations and which might be most appropriate given that the majority of doctors have access to only one kind of machine.

Keywords: ultrasound, elastography, acoustic radiation force impulse, shear wave, strain



How to cite this URL:
Cui XW, Li KN, Yi AJ, Wang B, Wei Q, Wu GG, Dietrich CF. Ultrasound elastography. Endosc Ultrasound [Epub ahead of print] [cited 2022 May 22]. Available from: http://www.eusjournal.com/preprintarticle.asp?id=344249

Dr. Xin-Wu Cui and Kang-Ning Li contributed equally to this article.



  Introduction Top


Physicians have understood the elastic properties of pathology since the first time they used palpation as a diagnostic examination. They realized that tissue stiffness is closely related to its biological characteristics. In 1991, Ophir Equate first invented a model of ultrasound (US) elastography,[1] overcoming the weakness of subjectivity by manual palpation and gaining the ability to detect deep lesions as well as superficial masses. US elastography provided new diagnostic information about elasticity comparing with the morphological feathers of traditional US, and thus expanded the scope of the application in clinic. US elastography is now widely used in the field of diagnosis and differential diagnosis of abnormality, evaluating the degree of fibrosis and assessment of treatment response for a range of diseases.

Classification

The World Federation of Ultrasound Medicine and Biology divided elastography techniques into three major categories according to their different processes:[2] (i) strain elastography (SE) evaluates tissue deformation by manual compression or physiological motion; (ii) transient elastography (TE) generates a shear wave with an external vibration; and (iii) acoustic radiation force impulse (ARFI) is a method that uses acoustic radiation force to produce shear waves. The ARFI techniques can be further classified into point shear wave elastography (p-SWE), 2D shear wave elastography (2D SWE), and 3D shear wave elastography (3D SWE) techniques. The SE measures the strain, while the shear wave-based techniques (including TE and ARFI techniques) measure the speed of shear waves in tissues [Table 1].
Table 1: Classification of ultrasound elastography

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The first commercial equipment for elastography was released in 2003 and has developed rapidly over the last 20 years. Today, most manufacturers offer an elastographic option either strain or shear wave-based approaches. Therefore, we discuss the various techniques separately based on their basic principles, clinical applications, and advantages and limitations and which might be most appropriate given that the majority of doctors have access to only one kind of machine.


  Strain Imaging Top


Strain imaging was the earliest commercially available US elastography, initially designed for the diagnosis of breast cancers using manual compression. As the pressure is applied on the body surface by hand, the deep organs such as the liver can hardly be detected. Hitachi invented a new method that exploited either cardiovascular pulsation or respiration to produce a deformation.

Basic principles

When an operator applies pressure to a tissue with a probe in the direction of US beam propagation, a tissue deformation is induced. The strain (the deformation rate) can be obtained by comparing the echo signal before and after compression. The tissue stiffness is expressed as Young's modulus (E), which is calculated using the formula (E = s/ε) after applying stress s and measuring strain ε.[3] As the stress distribution in body is hard to know, it is assumed to be uniform. As a result, strain is negatively related with stiffness. The strain image is overlaid as a color scale (usually with red being soft and blue being hard) on the B-mode image. Gray-coded and other color-coded elastograms can also be seen in different ultrasonic equipment [Figure 1]. A quality indicator is displayed in real time as a reminder whether the degree of compression is appropriate. As discussed above, strain is a relative index of stiffness and changes proportionately with the intensity of compression. Therefore, one cannot make direct comparisons between cases. Some indicators have been proposed to solve this problem:[4] (i) elasticity score, details shown in the breast section; (ii) the strain ratio, the strain of mass divided by the strain of the surroundings; (iii) the strain size ratio (EI/B ratio), the ratio of the tumor size in elastogram to that in B-mode image.
Figure 1: An example of strain image (breast cancer). The strain image is overlaid as a color scale with red being soft and blue being hard on the B-mode image

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Clinical applications

Breast

Tips and tricks

To obtain a good elastogram, three tips are necessary.[5] The first one is to obtain an optimal B-mode image before starting to perform elastography, including the breast gland, the surrounding fat, and the lesion. Next, make sure that the probe is perpendicular to the skin. Finally, appropriate compression is applied based on the depth of the target: no or minimal pressure is applied when detecting shallow lesions, while significant vibration is necessary for deep and large lesions. Precompression should be avoided as it changes the primary elastic condition of the target.

Results

SE is widely used as a complimentary technique to B-mode imaging to characterize breast tumors as benign or malignant by using Tsukuba score, EI/B ratio, and Lesion to fat ratio (FLR):[6]

Tsukuba score (elasticity score)

The Tsukuba score is a five-point scale that grades the stiffness of a mass visually based on the size ratio of color: (i) score 1, the lesion is entirely soft; (ii) score 2, the lesion has a mixed pattern; (iii) score 3, the lesion is hard but smaller in the elastogram; (iv) score 4, the lesion is hard but the same size in the elastogram as in the B-mode image; (v) score 5, the lesion is hard and larger in the elastogram [Table 2]. The score 3-5 is considered to indicate a high probability of malignancy with biopsy recommended, while the score 1 or 2 is probably benign [Figure 2]. A prospective study evaluated the value of Tsukuba score for differentiating between benign and malignant breast tumors, showing a sensitivity and a specificity 92.7% and 85.8%, respectively.[7] However, there is an intrinsic limitation that the judgment is subjective and the region of interest (ROI) may not cover the whole tumor and the surrounding tissue if the tumors are large.
Figure 2: A breast mass of a 56-year-old woman which proved to be adenopathy with fibroadenomatous nodules (a and b). The Tsukuba score was 1 (a) and the strain ratio was 0.90 (b). A breast mass of a 72-year-old woman, which proved to be invasive carcinoma (c and d). The Tsukuba score was 4 (c) and the strain ratio was 3.04 (d)

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Table 2: Tsukuba scoring system

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EI/B ratio

EI/B ratio is proposed to discriminate malignant from benign lesions based on the fact that the benign lesions are smaller than the corresponding B-mode image, while malignant masses are larger due to the infiltration of the surrounding areas. A large multicenter research study assessed 635 biopsy-proven lesions using the classification (EI/B ratio <1 as benign and EI/B ratio ≥1 as malignant), reporting a sensitivity of 99% and a specificity of 87%.[8] The EI/B ratio is also found to be significantly positively correlated with the grade of invasive ductal cancers.[9] However, when the strain of the lesion (e.g., fibroadenoma) is similar to the dense breast tissue, the lesion size on elastogram may be overestimated creating a false-positive result.

Lesion to fat ratio

Lesion to fat ratio (LFR) is a kind of strain ratio, the ratio of strain in a mass to that in the surrounding fat at the same depth. The method is suitable for the condition that the size of tumor is larger than the ROI. When faced with the situation that the lesion strain is the same as the background tissue, LFR could solve the problem of EI/B ratio. In a meta-analysis including nine studies of 2087 lesions, a pooled sensitivity of 88% and specificity of 83% were acquired.[10] The strain ratio can also be used in the assessment of nonmass abnormalities, such as intraductal carcinoma in situ. It was found that LFR was also effective for identifying the extent of tumor spread before breast-conserving surgery in Nakashima et al.'s research.[11]

Artifacts

There are some typical artifacts that can help characterize the pathological features, especially for cystic lesions. One is the BGR sign, a characteristic as three layers of blue, green, and red from the shallow to deep areas, which is usually identified in liquids (e.g., ascites, cysts). The other is the “Bull's eye” artifact, usually observed in both the simple and complicated cysts with the equipment of Siemens and Philips. This artifact shows as a black outer ring with a central and posterior bright spot, resulting from the movement of fluid.[3] In one series, the Bull's eye artifact is reported to decrease the number of biopsies. 10% of solid lesions on B-mode were in fact complicated cysts.[12]

Thyroid

Tips and tricks

The tips for thyroid examination are similar to those of breast, except that the deformation can be generated either by manual vibration or by carotid pulsations.[13] The ROI should be as large as possible, covering the nodule and some adjacent thyroid tissue. As a result, a longitudinal scan is recommended for performing transient elastography (TE) with manual compression, while a transverse scan is suggested for the utilization of carotid pulsation.

Results

SE can be used to improve the diagnostic accuracy of thyroid nodules, combined with traditional US,[14] by several semi-quantitative methods.

Tsukuba score

The Tsukuba score system can be also applied for thyroid nodules. In a study of 92 patients, scores 4 and 5 were found to be highly predictive of malignancy (P < 0.0001), with a sensitivity of 97%, specificity of 100%, positive predictive value of 100%, and negative predictive value of 98%.[15] A new four-pattern score system has been created based on the Tsukuba score system:[16] (i) score 1, the nodule is entirely soft; (ii) score 2, the nodule is mostly soft, with some hard areas; (iii) score 3, the nodule is mostly hard, with some soft areas; and (iv) score 4, the nodule is entirely stiff [Table 3]. Scores 1 and 2 are considered as probably benign, whereas scores 3 and 4 are likely to be malignant [Figure 3]. Sensitivity and specificity of this indicator were 94.1% and 81%, respectively.
Figure 3: An example of score 3 thyroid nodule, which is proven as papillary carcinoma; almost the whole lesion is displayed in hard blue (a), the strain ratio is 4.94 (b)

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Table 3: A new four-pattern score system created based on the Tsukuba score system

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The strain ratio

The strain ratio has been categorized into two types: (i) parenchyma-to-nodule strain ratio (PNSR), the mean strain in the normal thyroid parenchyma divided by the mean strain within the thyroid nodule [Figure 3] and [Figure 4], and (ii) muscle-to-nodule strain ratio (MNSR), the mean strain in surrounding muscles divided by the strain in the nodule.[17] There is no significant difference between PNSR and MNSR in the discrimination between benign and malignant lesions, suggesting that, for patients without adjacent normal thyroid tissue, a surrounding muscle can be used for instead.[18] Several studies have assessed the strain ratio, but there remains no consensus regarding the optimal cutoff for differentiating between benign and malignant lesions.[19],[20],[21],[22],[23],[24],[25] Cutoff values ranging from 1.5 to 5.0 have been suggested, with a sensitivity of 81.8%–97.8% and a specificity of 82.9%–85.7%. It has been shown that the SR has a lower interobserver variability and a shorter learning curve than scoring systems.[13]
Figure 4: A 44-year-old female patient with a papillary microcarcinoma in the left thyroid gland. The strain ratio was 2.39

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Pathology

It is well documented that most papillary carcinomas are stiff; however, other types of carcinomas may appear soft on elastogram [Figure 5] and [Figure 6]. For example, follicular carcinoma reported a 44% false-negative rate.[26] Calcification within a nodule is associated with increased stiffness, irrespective of the underlying pathology, and may lead to unreliable results. Fibrosis inside benign nodules or associated with subacute or Hashimoto thyroiditis may also cause stiffening within nodules[27],[28],[29] [Figure 7]. Therefore, the SE features are inferior to the conventional ultrasonographic findings in determining whether there is malignancy. If the nodule is suspicious on US, fine needle aspiration should be recommended even if the lesion looks soft on SE.
Figure 5: Strain elastography with Virtual Touch image showing a papillary carcinoma (a and b) is hard

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Figure 6: Strain elastography with Virtual Touch image showing a nodular goiter (a and b) is soft

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Figure 7: Strain elastography with Virtual Touch image showing Hashimoto thyroiditis is hard

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Prostate

Tips and tricks

The prostate is located directly in front of rectum, which enables transrectal US (TRUS) to better visualize the features of lesions than abdominal US. Thus, SE can be conducted after high-quality TRUS with a same transrectal probe. A water-filled balloon can improve the homogeneity of the deformation when placed between the transducer and the rectal wall.[30] The ROI should include the entire prostate gland and the surrounding tissues but exclude the bladder.

Results

Prostate cancer (PCA) has a high incidence rate in men worldwide. Currently, prostate-specific antigen (PSA) screening and systematic biopsy (SB) are the two most frequently used methods for PCA diagnosis, although PSA testing has low specificity and SB has low sensitivity.[31] TRUS has an advantage of high resolution. Nearly 58% of PCAs are multifocal and grow beyond the prostate capsule, appearing as ill-defined nodules in contrast to other malignant tumors. Therefore, it is difficult to detect lesions accurately using traditional US.[32] PCA is generally stiffer than normal prostate tissue and benign tissue; therefore, SE can be used as an effective technique to complement conventional US for the diagnosis of PCA.

Characterization of prostatic lesions

The addition of SE increases the diagnostic performance of PCAs compared with using TRUS alone. There are several methods proposed to interpret the SE images as follows:

Five-point scoring system

A five-point scale has subjectively classified SE images according to degree and distribution of stiffness in relation to simultaneously displayed hypoechoic lesion on US. (i) Score 1: normal appearance (homogeneous relatively soft); (ii) Score 2: probably normal (symmetric heterogeneous mostly soft); (iii) Score 3: indeterminate (focal asymmetric stiff lesion not related to hypoechoic lesion); (iv) Score 4: probably carcinoma (the peripheral part of the lesion is relatively soft and the central part stiff); and (v) Score 5: definitely carcinoma (the entire lesion and the surrounding areas are stiff). This scoring method showed a sensitivity of 68% and a specificity of 81% when using a cutoff value of 3, which is comparable to power Doppler US and superior to B-mode US. The combination of SE with power Doppler US increases the sensitivity to 78%.[33]

Another five-point scoring system

This scale focuses on outer parts of the gland. (i) Score 1: there is no stiff area in the peripheral gland; (ii) Score 2: a small symmetric stiff area in the peripheral gland which is less than 5 mm; (iii) Score 3: a small symmetric stiff area in the peripheral gland which is equal to or more than 5 mm; (iv) Score 4: asymmetric stiff area in the peripheral gland which is equal to or more than 5 mm; (v) Score 5: asymmetric stiff area larger than 50% of a single peripheral gland. The sensitivity and specificity of this scoring system are 68.6% and 69.4% respectively, with a cutoff value of 3.[34]

Strain ratio index

This method compares the stiffness of a lesion with that of normal prostate tissue. The peak strain ratio index refers to the strain of background tissue divided by the strain of the stiffest area in the target lesion, which is more useful to reduce the false-positive rate. Zhang et al. reported that a cutoff value of 17.4 yielded a highest sensitivity (74.5%) and specificity (83.3%) in differentiating between benign and malignant lesions.[35]

Guiding prostate biopsy

SB is considered as the standard technique for PCA detection. However, 20%–30% of clinically significant PCAs are missed in one biopsy; on the other hand, many insignificant PCAs are detected, resulting in an over-treatment rate from 27% to 56%.[36] Aigner et al. compared SE-targeted biopsy with SB, reporting that their PCA detection rate per patient was comparable, but the detection rate of SE-targeted per core was 2.9–4.7-fold higher than that of SB;[37] SE-targeted sampling was also found to have the advantage of detecting high-risk PCA.[38],[39],[40],[41] This makes it attractive for patients who wish to reduce the number of cores as much as possible without increasing the risk of missing significant PCA. However, currently, SE-targeted biopsy is recommended to be used in combination with SB, as a high percentage of PCAs are missed when SE-targeted sampling is used alone.[42],[43],[44] As a result, more research regarding the method to be useful to improve the success rate of biopsy is needed.

Staging of prostate cancer

The Gleason score is one of the most frequently used histological grading systems and is closely related to the prognosis of PCA.[45] The elastic modulus seems much greater in PCA with a Gleason score ≥7,[46] and this may be explained by the higher cell density of high-grade tumors, leading to stiffer tissue. A pericapsular “soft rim” is often seen on SE, corresponding to the capsule of the prostate; its absence may indicate extracapsular extension (ECE).[47],[48] Pelzer reported a sensitivity of 79% and a specificity of 89% for the prediction of ECE with the sign of disrupted soft rim, which improved the staging ability compared with TRUS alone.

Liver

Tips and tricks

SE measures the strain response of tissue to stress usually generated by manual compression or cardiovascular pulsation. The reason why the strain response can reflect the tissue stiffness is that soft tissue can be more easily compressed than hard tissue. On US, the strain of the tissue is shown as a color map overlaid to the gray scale image. Both qualitative and semi-quantitative methods have been developed to evaluate the tissue stiffness. Qualitative technique evaluates the color pattern within a ROI, while semi-quantitative method is performed either with strain ratio which measures the relative strain between two areas inside a ROI or with strain histogram which computes the strain values of elemental areas inside a ROI.[49],[50]

Results

SE is less well defined than other elastic techniques in the field of liver fibrosis. There is a lack of standardization in the assessment of liver fibrosis using SE, as experience is limited. In a meta-analysis of 15 studies with 1626 patients, SE was found to have a reasonable performance with the sensitivities for significant fibrosis (F ≥2), severe fibrosis (F ≥3), and cirrhosis (F4) as 79%, 82%, and 74%, respectively, and specificities as 76%, 81%, and 84%, respectively[51] [Figure 8]. However, the authors noted that the sensitivity and specificity might have been overestimated because there were signs of bias. In a study that compared p-SWE and transient elastography, there was no significant difference between the three techniques for the diagnosis of cirrhosis, but p-SWE and transient elastography performed better than SE in diagnosing significant fibrosis.[52] A small study revealed that the combined use of strain and shear wave imaging with a single machine might increase accuracy in the diagnosis of liver fibrosis.[53],[54] Another study demonstrated that the combination of SE and serum fibrosis tests gives a better diagnostic performance than either of them applied alone.[55]
Figure 8: Strain elastography with Virtual Touch image showing liver cirrhosis (F4) (a and b) is hard

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Pancreas

Tips and tricks

The elastographic properties of the pancreas could be studied with SE through either transabdominal or endoscopic approach. EUS is a minimally invasive technique with high resolution, which is widely used in the assessment of small pancreatic lesions (SPLs).

Results

SE allows better visualization and semi-quantification of focal pancreatic lesions; a soft SPL is typically benign whereas a harder SPL in healthy pancreatic parenchyma can be malignant or benign. A multicenter study evaluated 218 small SPLs (≤15 mm) with endoscopic SE using histological pathology as a gold standard, reporting a high level of certainty of ruling out malignancy if the lesion is displayed as soft; however, the results would be less reliable in larger SPLs due to the heterogeneity of the lesions and the concomitant changes of the surrounding pancreatic parenchyma.[56] Another prospective multicenter research indicated that the best diagnostic performance of the focal pancreatic masses was obtained with an initial use of endoscopic SE and followed by contrast-enhanced EUS.[57] However, it remains difficult for endoscopic SE to decisively differentiate focal chronic pancreatitis from pancreatic ductal adenocarcinoma (PDAC), since they share a similar stiffness.[58]

SE may be used as a complimentary imaging technique for the diagnosis and staging chronic pancreatitis. A study reveals a positive correlation between a higher strain ratio (SR) value and insufficient pancreatic exocrine.[59] SE has a unique advantage in diagnosing autoimmune pancreatitis, with a specific appearance of diffuse stiff pattern both in the lesion and the surrounding tissue, since the entire gland shows stiffer properties earlier than B-mode changes occur.[60]

Others

SE has also been reported to be used in the field of gastrointestinal tract, lymph nodes, vascular, and musculoskeletal.

Gastrointestinal tract

SE is applied to assess the stiffness of the thickened bowl wall associated with inflammation or neoplasm. It is recommended to use a transducer with frequency above 7.5 MHz to better visualize the wall layers. SE can help distinguish whether a stenosis in Crohn's disease (CD) is caused by inflammation or fibrosis, which is relevant with regard to prognosis and choice of treatment, since fibrotic stenoses appear stiffer than inflammatory stenoses.[61],[62] Furthermore, patients with active CD have a higher strain ratio between the inflammatory and normal segments than patients in remission.[63] A recent prospective study of 30 patients revealed that SE may predict the treatment response by using SR, reporting a significant negative relationship between the SR at baseline and wall thickness after 52 weeks of anti-tumor necrosis factor therapy.[64]

Lymph nodes

Accurate distinction between benign and malignant lymph nodes is important for predicting prognosis and making a treatment plan. Superficial and mediastinal lymph nodes can be assessed with transcutaneous and endoscopic SE, respectively. A meta-analysis including 936 superficial lymph nodes of 578 patients yielded a sensitivity of 76% using a scoring system and 83% by SR.[65] However, it should be noted that not all malignant lymph nodes are stiff as is the case of lymphoma[66] [Figure 9],[Figure 10],[Figure 11]. Therefore, SE is more suitable as a complimentary method for differential diagnosis, especially in identifying the most suspicious lymph nodes for needle aspiration.[67]
Figure 9: Strain elastography revealed a metastatic lymph node in the neck with the Tsukuba score of 3 (a); inguinal metastatic lymph nodes with the Tsukuba score of 4 (b)

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Figure 10: The neck lymph node metastasis appeared to be hard on strain elastography with Virtual Touch image

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Figure 11: Non-Hodgkin's lymphoma is not so hard on strain elastography with Virtual Touch image (a) and shear wave elastography with Virtual Touch quantification (b) and Virtual Touch tissue quantification (c)

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Vascular

It is well established that atherosclerosis is associated with increased arterial wall stiffness,[68] and elastography biomarkers are emerging as potential indicators to characterize vulnerable plaque, which indicate a high risk for diseases such as stroke and cardiovascular disease.[69] Evidence from animal and human studies[70],[71],[72] demonstrated that vulnerable plaque is less stiff than the stable plaque. A systematic review demonstrated that SE is a feasible aid to differentiate acute from chronic deep vein thrombosis, providing additional information for clinical decision-making.[73]

Musculoskeletal

The musculoskeletal elastography is an area of active research, especially for tendons, muscles, and nerves.

Tendons

The healthy Achilles tendon is rigid and there is an increase with age,[74] while the tendon becomes less stiff in Achilles tendinopathy, with a higher strain ratio of tendon to Kager's fat.[75] Furthermore, SE can detect the pathology before the emergence of morphologic changes, which is superior to B-mode US.[76]

Muscles

The normal relaxed muscle appears heterogeneous, has intermediate stiffness, and becomes stiffer when contracted; a lot of physiological (age, sex, fatigue, and training) and pathological (trauma, degeneration, and neuromuscular disease) factors have an influence on muscle elasticity. Song et al. reported that the stiffer muscles displayed on SE significantly correlate with histological findings in inflammatory myopathies.[77]

Nerves

SE can be used in the evaluation of median nerve in carpal tunnel syndrome, where it is much stiffer than in healthy volunteers.[78] The increased stiffness is because of nerve edema or fibrosis. Combined with B-mode US, SE can be used to follow up the recovery of the median nerve after local corticosteroid injection guided by US or carpal tunnel release.[79]

Advantage and limitations

Strain imaging has the advantages of a short learning curve and wide application across almost the whole body. However, some disadvantages remain. The biggest limitation is that it is a nonquantitative technique and does not directly measure tissue elasticity but rather identify elasticity relative to adjacent regions. In addition, due to the attenuation of vibration energy during propagation, a decrease of accuracy is occurred in deeper regions compared with superficial ones.


  Shear Wave-Based Elastography Top


Shear wave-based elastography is a method of exciting the tissue to generate shear waves and to measure shear wave speeds (SWSs). Based on the formula of Young's model: E = 3 ρ Cs2, where E is the Young's modulus, ρ is the tissue density, and Cs is the shear wave velocity, the tissue stiffness can be reported as the Young's modulus or the shear wave velocity using various commercially available systems.[3] Shear wave-based elastography can be further grouped into transient elastography and ARFI techniques according to the excitation method, as described below.

Transient elastography

Transient elastography (TE) was the first shear wave technique applied in clinical practice, with the system called FibroScan™ (Echosens, Paris, France). The equipment does not have a traditional US probe nor does it display B-mode images. It is currently only applied to the liver, mainly to evaluate the liver stiffness measurements (LSMs) of patients with chronic viral hepatitis and some other diseases.

Basic principle

A mechanical piston is integrated with the ultrasonic transducer, which can induce a thrust to the body surface under the control of a manual operation. The thrust acts on the liver through the intercostal space, causing transient shear deformation and traveling shear waves. The stiffer the liver parenchyma, the faster the shear wave propagates. Pulse-echo US acquisition is used to track the resulting shear waves and to measure SWSs. The Fibroscan™ displays the corresponding Young's modulus computed based on the SWS.

Clinical applications

A variety of etiological factors, e.g., viral hepatitis, alcoholic and nonalcoholic fatty liver disease, autoimmune hepatitis and primary biliary cholangitis, and drug-induced liver injury, may contribute to liver fibrosis. Diagnosing liver fibrosis accurately is an important role for staging disease, predicting prognosis and assessing treatment response. Liver biopsy has been considered as the gold standard for grading liver fibrosis, but several disadvantages are obvious: it is invasive, inevitably associated with rare but serious complications, and it can only sample a small portion of the liver parenchyma, making it susceptible to sampling variation.[80] To overcome these problems, noninvasive methods have been studied over decades for the assessment of liver stiffness (LS). So far, there are three main techniques established in the clinical practice: (i) serum marker of liver fibrosis, (ii) magnetic resonance elastography (MRE), and (iii) US elastography. Different methods have their own advantages and limitations: the serum maker of fibrosis is highly reproducible but has low specificity, while MRE has the potential to evaluate almost the entire liver at the same time, however is time and cost-consuming. Furthermore, US elastography is most widely used as it yields a best tradeoff between accurate results and simple operation. Shear wave elastography (SWE) is more commonly used for evaluating hepatic fibrosis compared with SE in clinical practice, with TE as a starter.

Tips and tricks

For patients

Patients should fast for at least 4 h before examination, as ingestion of food increases blood flow to the liver, increasing its stiffness.[81] Ingestion of food can only increase the LS; therefore, if patients eat and their stiffness values are normal, they are suggestive of no or mild fibrosis. Examinations should be performed with the patient in the supine position with the right arm raised above the head to expand the intercostal space. The patient is instructed to take a short breath hold in the mid-respiratory position (avoiding breath hold in deep inspiration) at the time of measurement.

Technique

The TE measurement is taken 1.5–2 cm below the right lobe of the liver capsule to avoid reverberation artifact via the intercostal space. The probe covered with coupling gel is placed perpendicular to the liver capsule. Once the ROI is fixed, the operator manually presses the button to start an acquisition. The software determines automatically whether each measurement is successful or not and controls choice between M and XL probe according to the distance between skin and liver capsule. LS is measured in kPa, ranging from 2.5 to 75 kPa. Ten measurements should be obtained from the same sites with the median value reported. The quality assessment of TE results depends on two important parameters:[82] (i) success rate (the ratio of the number of successful measurements to the total number of measurements) ≥60%; (ii) the interquartile range (IQR) reflecting the variability of measured values is less than 30% of the median measurements.

Results

Assessing fibrosis

TE is used as an alternative to liver biopsy for assessing hepatic fibrosis mainly in viral hepatitis or HIV co-infection. Based on METAVIR scoring system for chronic liver diseases, the degree of liver fibrosis can be classified into five histological stages: (i) F0, no evidence of fibrosis; (ii) F1, mild fibrosis, no formation of septum; F2, significant fibrosis with few of septum; F3, severe fibrosis with lots of septum; and F4, cirrhosis. LS correlates strongly with the METAVIR scoring system. A meta-analysis that included 50 studies utilizes the area under the receiver operator characteristic (AUROC) curve to estimate the performance of transient elastography for the staging of liver fibrosis:[83] the mean AUROC for the diagnosis of significant fibrosis (F ≥2), severe fibrosis (F ≥3), and cirrhosis (F4) was 0.84, 0.89, and 0.94, with a cutoff of 7.0, 9.5, and 12.5, respectively. A better diagnostic performance of TE was reported for lower fibrosis degrees. However, there is a substantial overlap in LS between adjacent stages of hepatic fibrosis,[84] thus making differentiation between F0 and F1 or between F1 and F2 difficult. The LS also depends on the underlying etiology. Optimal cutoff values for diagnosing cirrhosis appear to be lower for patients with chronic hepatitis B virus (HBV) than for patients with hepatitis C virus (HCV). Studies in patients with chronic HCV report optimal cutoff values of 11–14 kPa for cirrhosis.[80],[85],[86] In patients with chronic HBV, the cutoff values for diagnosing cirrhosis are between 9.0 and 10 kPa, based on the studies performed primarily in Asian populations.[87],[88] Autoimmune hepatitis tends to have much higher LSMs compared with HBV and HCV, due to the concomitant inflammatory activity, which can increase LS. Other liver diseases need to be further investigated to gain sufficient evidence.

Predicting complications

In patients with cirrhosis, LSMs obtained with TE are able to predict liver-related complications as confirmed in a meta-analysis;[89] the higher the LSM, the greater the risk of clinical complications. LSM is significantly and positively correlated with the hepatic venous pressure gradient (HVPG, gold standard for portal hypertension in cirrhosis), with a correlation coefficient of 0.55–0.86.[90] LSM accurately discriminates between patients with and without clinically significant portal hypertension (CSPH, defined as HVPG ≥10 mmHg, threshold for the appearance of complications); the summary AUROC is 0.93 with a cutoff >20–25 kPa according to a meta-analysis.[91] High LSM values are also significantly associated with the presence and size of gastroesophageal varices, with summary AUROCs of 0.78–0.84.[90] Platelet count and spleen size significantly improve the prediction of varices, obtained by LSM alone.[92] It has been reported that compensated patients with values of LSM <25 kPa and normal platelet counts (>110 g/l) bear a very low risk of varices requiring treatment, which can eliminate unnecessary endoscopies.[93] Spleen stiffness measurement (SSM) has been proposed as an additional parameter, potentially better correlating with portal pressure, irrespective of its cause. One study found that SSM cutoff values of 3.36 and 3.51 m/s identified patients with esophageal varices and high-risk esophageal varices, respectively.[80] Recent studies using TE found that LS was more accurate than spleen stiffness (SS) for the diagnosis of CSPH (AUROCs of 0.95 vs. 0.85).[94]

Monitoring treatment

The decision to start antiviral therapy can, in most cases, be made based on serum alanine aminotransferase (ALT) and HBV DNA levels, as well as noninvasive tests of fibrosis.[95] During antiviral treatment, LS usually decreases associated with the normalization of ALT, reflecting suppression of hepatic inflammation, even when there is no improvement in histologic fibrosis.[96] However, although long-term treatment can reverse histological cirrhosis,[97] the risk of hepatocellular carcinoma and portal hypertension after sustained virologic response is much lower than untreated persons but still higher than those who never had cirrhosis.[98] The screening strategies should continue despite decreased LS.

Confounding factors

Although fibrosis is the main determinant of LS,[99],[100] other factors also influence LS,[80],[82],[101] often resulting in a false-positive diagnosis of advanced fibrosis or cirrhosis. This is similar across all shear wave techniques as they all measure SWS. First, liver steatosis causes attenuation of ARFI pulse and can lead to more variability in the measurements. Second, elevated ALT levels (>5 times upper limit of normal) resulting from inflammatory causes such as acute hepatitis, acute-on chronic hepatitis, chronic viral hepatitis, and cholestasis are associated with increased hepatic stiffness. In a study of 104 patients with chronic hepatitis B (CHB) and 453 patients with chronic hepatitis C (CHC), histological necroinflammatory activity was found to be an independent risk factor for the overestimation of LSM in HCV and HBV, while histological steatosis was a risk factor in HCV patients only.[102] At last, the increase of central venous pressure leads to more liver perfusion along with the stiffer liver; thus, cardiopulmonary disease should be excluded. In conclusion, clinicians should exercise caution when interpreting the results of LS in such situations, with full knowledge of the patient history, disease etiology, and essential serum parameters.

Evaluating steatosis

An additional function, available on the FibroScan 502 Touch System of TE, allows the measurement of any decrease in US signal of the liver with the controlled attenuation parameter (CAP) tool. The CAP results are related to the amount of fat in the liver and are expressed as decibels per meter (dB/m).[103],[104] This can only be successfully displayed when the LSM is valid, because it is derived from the US signals used for acquiring LSM. CAP is a point-of-care, standardized, and reproducible technique, promising for the detection of liver steatosis. However, for quantifying steatosis, there is a large overlap between adjacent grades and there is no agreement regarding cutoffs or quality criteria.

Advantages and limitations

Advantages

TE is easy to learn and can be used even in the outpatient clinic or bedside with the results available immediately. In addition, if a standardized protocol is followed, TE has excellent reproducibility with both good intra- and inter-observer agreement. For example, in a study with 200 patients with various liver diseases examined by two operators, reproducibility was high, with intraclass correlation coefficients of 0.98 for inter- and intra-observer agreement; however, interobserver agreement was lower in patients with mild fibrosis, steatosis, or an increased body mass index (>25 kg/m2).[105] Standard M-type probe can detect a cylinder volume of 10 mm wide and 40 mm long, which is approximately 1/500 of the entire liver parenchyma and at least 100 times the sampling volume of a biopsy. Therefore, it was pointed out that compared with liver biopsy, TE results are more representative of the stiffness of liver parenchyma.

Limitations

This technique still has some limitations: first, the absence of gray scale image guidance makes it difficult to avoid large blood vessels, bile ducts, and masses at the site of measurement. Second, TE can only be performed through a few intercostal spaces, and therefore, it is not suitable for the left liver lobe scanning. In addition, TE can only detect to a depth of 2.5–6.5 cm below the liver capsule with M probe. As a result, insufficient signals may be obtained with obese patients. The XL probe has been developed for overweight patients and the S probe for patients with narrow intercostal spaces, especially for children. However, there remains no solution for patients with ascites around the liver, since shear waves cannot propagate in liquid.

Acoustic radiation force impulse techniques

Basic principle

ARFI techniques differ from TE in the way the mechanical excitation is applied. An acoustic radiation force is used to generate tissue displacement and shear waves via a focused acoustic beam.[3] Shear waves propagate in a direction perpendicular to that of the ultrasonic waves; thus, SWSs are calculated by monitoring the time to peak displacement at each lateral position. B-mode image guidance is possible during the measurement because they share the same transducer. According to the extent of detected area, three subtypes are discussed below.

Point shear wave elastography

p-SWE only excites the acoustic radiation force at one point and then detects the shear wave velocity in a small ROI. The output is expressed in either m/s or kPa converted by the Young's model formula. Because only a small area is measured in shear wave imaging, it is recommended to take at least 5–10 measurements and take the average value. Currently, there are mainly two systems commercially available in clinical practice: VTQ from Siemens and ELasto-Q from Philips.

2D shear wave elastography (Supersonic, VTIQ)

If the acoustic radiation force is continuously excited at multiple points, and the arrival time of the shear wave is sequentially measured with a time-of-flight estimation technique, a shear wave image of a larger ROI can be obtained and coded with gray or color scale. This kind of shear wave image can be separately displayed or superimposed on the conventional B-US image. A measurement box can be placed within the ROI to get the stiffness value. If possible, the measurement box should be placed near the center of the ROI, as there are often errors at the borders of the ROI. Superior to p-SWE, the measurement box size of 2D-SWE is changeable and 2D-SWE reports both the average and the standard deviation of the stiffness values, as well as the minimum and maximum values. If the system has a quality measure that confirms the area of measurement has high-quality shear waves, three to five measurements are recommended.[106]

3D shear wave elastography

At present, only supersonic imagine has implemented 3D-SWE. Its 3D probe contains a mechanical scanning 2D sensor sequence and has a relatively high-speed calculation capability, which can perform three-dimensional reconstruction of tissue stiffness. 3D SWE is in development, and no recommendations regarding its use can be made at this time.

Clinical applications

Liver

Tips and tricks

The procedures of ARFI-based techniques are similar to those of TE, with an identical transducer with B-mode US. A convex probe is more widely used than a linear probe for liver examinations. In a study on 89 chronic HCV-infected patients, the linear probe gave SWS values higher than those obtained with the convex probe.[107] Due to the attenuation of the ARFI pulse, measurement accuracy decreases significantly below 6 cm from the transducer. A study has evaluated the variability of SWS assessed with a p-SWE technique at various depths using different frequencies. In the liver, the depth with the lowest variability was 4 cm from the skin with a convex probe and 3 cm with a liner probe.[108]

Results

ARFI-based techniques can measure the stiffness of the left lobe as well when the transducer is placed in the epigastric region. Higher values are often noted in the left lobe of the liver, but the accuracy of p-SWE appears to be higher in the right lobe of the liver compared with the left lobe.[50]

Assessing fibrosis

Overall, the ARFI technique has a diagnostic accuracy similar to TE but a lower failure rate, especially among obese patients. A meta-analysis that included nine studies with a total of 518 patients with chronic liver disease evaluated the overall diagnostic performance of p-SWE for staging liver fibrosis.[109] Optimal cutoff value for diagnosing F ≥2 was 1.34 m/s with a sensitivity of 79% and specificity of 85%; F ≥3: 1.55 m/s, sensitivity 86%, specificity 86%; and F4: 1.80 m/s, sensitivity 92%, specificity 86%. Another meta-analysis of 13 studies with 1163 patients with chronic liver disease compared p-SWE with TE, using liver biopsy as the gold standard.[110] It found that p-SWE had a lower failure rate than TE (2.1 vs. 6.6%). The sensitivities of p-SWE and TE were similar for diagnosing significant fibrosis (F ≥2; 74% and 78%, respectively) and cirrhosis (87% and 89%, respectively), as were the specificities (F ≥2: 83% and 84%, respectively; cirrhosis: 87% for both modalities) [Figure 12] and [Figure 13]. Another study of 336 patients revealed that the cutoff of 2D SWE for F ≥1–4 was 7.8 kPa (sensitivity 68%, specificity 100%), 8.0 kPa (sensitivity 83%, specificity 82%), 8.9 kPa (sensitivity 90%, specificity 81%), and 10.7 kPa (sensitivity 8.5%, specificity 83%), respectively. The study also compared the accuracy of 2D SWE with p-SWE and TE. The accuracy of 2D SWE was higher than that of TE for diagnosing severe fibrosis (F ≥3) and higher than that of p-SWE for diagnosing significant fibrosis (F ≥2). There were no significant differences among the three techniques for the diagnosis of mild fibrosis or cirrhosis [Figure 14].
Figure 12: Acoustic radiation force impulse techniques with Virtual Touch quantification for diagnosis F2 (a), F3 (b), F4 (c) in hepatitis B patients

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Figure 13: Acoustic radiation force impulse techniques with Virtual Touch quantification showing liver cirrhosis in a patient with alcoholic liver disease

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Figure 14: SWE images of the liver in patients with hepatitis B: F1 – (a) E mean 7.1 kPa; F2 – (b) E mean 7.8 kPa; F3 – (c) E mean 9.5 kPa; F4 – (d) E mean 24.5 kPa

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Predicting prognosis

Data regarding LSMs by p-SWE and 2D SWE in this field remain limited. Most data available concern TE. In summary, in the available studies, the applicability and diagnostic accuracy of both techniques closely resemble those of TE (for CSPH p-SWE: AUROC 0.820–0.90; 2D SWE: AUROC 0.80–0.92).[90] Similar considerations apply to the diagnosis of varices.[111],[112] Because of the limited evidence to date, noninvasive criteria to rule out varices based on p-SWE or 2D SWE cannot yet be recommended.

Diagnosing focal liver lesions

ARFI-based elastography has also been studied for the detection and characterization of focal liver lesions. However, US-based elastography cannot yet reliably differentiate benign from malignant lesions due to the overlap of the values[81] [Figure 15] and [Figure 16]. In addition, the limited depth of penetration makes it difficult to detect lesions. As a result, US-based elastography is not yet recommended for the differentiation of benign from malignant liver lesions.
Figure 15: Acoustic radiation force impulse techniques with Virtual Touch quantification (a) and Virtual Touch image (b) showing hepatocellular carcinoma is hard in a patient with hepatocellular carcinoma

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Figure 16: 2D SWE showing the lesion is hard in patients with metastasis (a), hemangioma (b), and focal nodular hyperplasia (c)

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Breast

Tips and tricks

For 2D SWE, since SWE images are generated based on the raw data from B-mode images, a good gray scale image should be obtained before switching to the SWE mode and get high-quality SWE images.[6] Keeping the angle of the probe perpendicular to the skin is essential because vibration energy is directly emitted from the probe. The probe should lightly touch the skin without any vibration or compression to avoid making the tissue harder which may result in artifactual stiffness.[6],[113] Therefore, enough contact jelly should be used. In addition, the patient should hold breath to reduce artifacts.[114] Before recording SWE images and measuring the elasticity of lesions, the probe should be held still for few to several seconds until the color display is completely stable to obtain reliable results.[6] Then, a ROI is placed over the stiffest part of the lesion to quantitatively measure the stiffness of breast lesion, which can be expressed in kPa or m/s, and the elasticity parameters include the mean (E mean), maximum (E max), minimum (E min), and standard deviation (E SD) of elasticity.

Results

SWE can effectively improve the diagnostic accuracy of BI-RADS classification in B-mode images, as malignant tumors tend to be more heterogeneous and stiffer than benign tumors. A large multicenter trial demonstrated that a sensitivity and specificity was 97.2% and 61.1, respectively, for BI-RADS alone and 98.6% and 78.5% with the addition of SWE using a cutoff of 80 kPa (5.2 m/s). The authors note that a BI-RADS 3 lesion which appears stiff should be upgraded to a 4a lesion, requiring a biopsy or vice versa.[115] Bai et al. found that the lesion is most likely to be malignant when no result is obtained with a solid lesion, with a sensitivity and a specificity of 63.4% and 100%, respectively.[116] The shear waves in these tumors demonstrate significant noise that may be incorrectly interpreted as low SWS by the system. A quality criterion is necessary to evaluate the resulting shear waves, whether they are adequate for an accurate measurement, helping to eliminate possible false-negative cases.[117],[118] Triple-negative breast cancer, which is tested negative for estrogen, progesterone, and HER2 receptors, are often misdiagnosed with BI-RADS 3 on B-mode US. These cases are reported to show increased stiffness in ARFI-based techniques and thus correctly assessed in clinical practice[104] [Figure 17]. A study of 396 breast cancers showed that SWE is an independent predictor of lymph node metastasis. With a mean elasticity value of <50 kPa, only 7% of the lymph nodes were positive, whereas 41% of the lymph nodes were positive when the mean elasticity value was >150 kPa.[119] One prospective study of 33 patients revealed that 3D SWE volume measurements correlated well with dynamic contrast-enhanced magnetic resonance imaging volume, and decreased stiffness during treatment was associated with good response.[120] A meta-analysis including 14 studies of 1951 patients with 2060 breast lesions compared the performance of traditional US and the combination of traditional US and 2D SWE or 3D SWE, suggesting a potential benefit of integrating SWE in the routine of breast lesion examination and no significant difference between 2D SWE or 3D SWE[121] [Figure 18].
Figure 17: Acoustic radiation force impulse with Virtual Touch quantification shows breast fibroadenoma is softer (a) and breast invasive ductal carcinoma is harder (b)

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Figure 18: 2D shear wave elastography shows fibroadenoma nodule is softer (a) and invasive ductal carcinoma is harder (b)

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Thyroid

Tips and tricks

The tips for thyroid examination refer to shear wave elastography of breast: a good gray scale image, the probe perpendicular to the skin without additional compression and patient holding breath are three key pointers to get high-quality results.

Results

Several meta-analyses showed that SWE (p-SWE and 2D SWE) has high sensitivity (80%–86%) and specificity (84%–90%) for evaluating the stiffness of thyroid nodules and differentiating between malignant and benign nodules with cutoff values (2.4–4.7 m/s), making it a useful complementary method to B-mode US[122],[123] [Figure 19]. A prospective research compared the diagnostic performance of TI-RADS classification alone and in association with SE or 2D SWE for thyroid nodule characterization and demonstrated a differential improvement for both techniques, particularly SE performing better than SWE.[124] Where there is coexistence of chronic autoimmune thyroiditis (CAT), ARFI techniques have a better diagnostic performance for thyroid nodules than SE, reporting a higher optimal cutoff value.[125],[126] The stiffness of extranodular tissue increased as fibrosis is the main pathological change in CAT, associated with the degree of thyroid function damage. As a result, SWE is also useful for diagnosing CAT and evaluating the fibrosis degree of CAT.[127],[128] Zhao et al. prospectively evaluated the diagnostic performance of 3D SWE for characterizing thyroid nodules, reporting that there is no significant difference concerning the diagnostic accuracy compared with 2D SWE, but the specificity was increased[129] [Figure 20]. A recent study including 237 patients with papillary thyroid carcinoma evaluated the clinical usefulness of nomogram based on SWE radiomics, showing a favorite predictive value of cervical lymph node metastasis, especially in the US-reported negative cases.[130]
Figure 19: Acoustic radiation force impulse shows papillary carcinoma (a, red area) is harder and adenoma (b and c) is softer, while follicular carcinoma (d) is not so hard as papillary carcinoma

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Figure 20: 2D shear wave elastography shows papillary thyroid carcinoma is harder (a) and nodular goiter is softer (b)

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Prostate

Tips and tricks

SWE is usually performed on TRUS. Digital rectal examination has shown that the PCA is usually stiffer than normal prostate tissue. SWE is helpful for detecting stiffer areas in the prostate, creating a color map, and quantitatively measuring the stiffness of prostate that facilitates the visualization of abnormal areas. Targeted biopsy facilitated by SWE may potentially reduce the number of necessary biopsy samples and thereby the morbidity and cost compared to multiple blind biopsies.[131] The tips and tricks are similar with SE of the prostate.

Results

SWE is the more recently developed technique, so less literature is available. A study[132] including 184 patients revealed that a stiffness value greater than 35 kPa is suspicious for malignancy with sensitivity and specificity being 97% and 70%, respectively. Another study of 12 patients with suspected PCA was performed with 3D SWE before biopsy in a prospectively study. In the targeted biopsy lesions, the cancer-positive area was significantly stiffer than the cancer-negative area (64.1 kPa vs. 30.8 kPa; P < 0.0001). When combined 3D SWE with Prostate Imaging Reporting and Data System, the diagnostic performance is improved.[133]

Pancreas

Tips and tricks

Nowadays, SWE is mainly performed with transabdominal US.[134] Only few literature from Japan reported SWE of the pancreas conducted by the EUS.[135],[136],[137]

Results

Data with regard to the role of SWE remain less extensive and convincing currently. Some literature reported a higher SWS in PDAC than the adjacent pancreatic parenchyma with a cutoff value >3 m/s.[138],[139],[140] A recent study compared the diagnostic performance of EUS-SWE and EUS-SE and demonstrated that EUS-SE was superior to EUS-SWE for the characterization of solid pancreatic lesions, but requiring further investigation.[135]

Others

SWE has also been reported to be used in the field of gastrointestinal tract, lymph nodes, vascular, and musculoskeletal.

Gastrointestinal tract

SWE is reported as a complimentary tool to B-mode endoscopic rectal US (ERUS) to characterize and stage the rectal tumors. A study showed that SWS has a good correlation with the tumor T-stage, largely improving the diagnostic accuracy of tumor staging from 76.7% (ERUS alone) to 93.3%.[141]

Lymph nodes

Preoperative assessment of the lymph nodes in patients with known primary cancer can be performed with SWE [Figure 21]. A meta-analysis including 481 patients with 647 lymph nodes evaluated the value of SWE in the distinction of malignant and benign superficial lymph nodes, indicating a sensitivity of 81% and a specificity of 85%.[142] An optimal cutoff of 40 kPa was reported to predict metastatic involvement, with a sensitivity of 80% and a specificity of 93.1%.[143] Another meta-analysis of 18 articles also validated the effectiveness concerning differential diagnosis with ARFI-based techniques; however, caution should be taken in the cases of tuberculosis and lymphoma.[144]
Figure 21: Metastatic lymph node is shown to be hard on 2D shear wave elastography (a), acoustic radiation force impulse with Virtual Touch quantification (b) and Virtual Touch tissue quantification (c), while inflammatory lymph nodes appear to be soft, which is shown on acoustic radiation force impulse with Virtual Touch quantification (d) and Virtual Touch tissue quantification (e)

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Vascular

SWE is helpful to improve the diagnostic performance of carotid plaque vulnerability. It was found that a lower mean Young's modulus indicated vulnerable carotid plaque, despite the values varying among different studies[145],[146],[147] [Figure 22].
Figure 22: 2D shear wave elastography image of a stable plaque in a 55-year-old man

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Musculoskeletal

SWE is emerging as a promising supplementary method to electromyography in the clinical application of diagnosis, treatment choice, and follow-up for various neurologic conditions, e.g., Parkinson disease, chronic stroke, and multiple sclerosis.[148],[149],[150],[151],[152] Both p-SWE and 2D SWE can be used for the diagnosis of carpal tunnel syndrome with a high sensitivity and specificity.[153] SWE showed a decreased stiffness of tibial nerve in diabetic patients, which reduced further after developing peripheral neuropathy,[154] making it a promising tool for the assessment of diabetic peripheral neuropathy.

Limitations and advantages

Advantages

Unlike TE, ARFI-based techniques can display US images, avoiding blind measurement. In addition, it focuses on the shear wave generated inside the tissue. Therefore, it can be used in patients with ascites when applied to the liver. Furthermore, it is more effective for obese patients, as the penetration of a focused acoustic beam is much higher than that of the mechanical wave generated by vibration.

Limitations

As ARFI-based techniques measure the SWSs as well as the TE does, the limitation of TE is also applied to the ARFI-based techniques. In addition, there exists an inner weakness of ARFI techniques. The SWSs are dependent on ARFI frequency, which is a phenomenon called dispersion: the higher the ARFI frequency, the higher the SWSs. As each system adopts a different ARFI frequency, the effects of dispersion could result in differences of the SWSs obtained with different systems in the same patient. Radiologic Society of North America reported an intersystem variability of commercially available system ranged from 6% to 12%. Therefore, the cutoff value of one system cannot be copied and applied to another system.[155]


  Conclusion and Future Perspectives Top


Elastography US is a promising additional imaging to traditional US, providing a more accurate evaluation of lesion stiffness than palpation, which can offer valuable information to clinicians. A number of other applications concerning elastography for determining tissue properties, structure, and function are being investigated, and new advanced techniques in the field will continue to grow rapidly in the coming years. Standard methodology is needed for future research to allow better comparison between studies and techniques.

Declaration of patient consent

The authors certify that they have obtained all appropriate patient consent forms. In the form, the patient has given her consent for her images and other clinical information to be reported in the journal. The patient understand that name and initials will not be published and due efforts will be made to conceal identity, but anonymity cannot be guaranteed.

Financial support and sponsorship

Nil.

Conflicts of interest

Christoph F. Dietrich is a Co-Editor-in-Chief of the journal. The article was subject to the journal's standard procedures, with peer review handled independently of this editor and his research groups.

 
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