The State of Prostate MRI in 2013

The State of Prostate MRI in 2013

Figure 1: A 49-year-old male with a prostate-specific antigen (PSA) le...
Figure 2: A 65-year-old male with a prostate-specific antigen (PSA) le...
Figure 3: A 69-year-old male with a prostate-specific antigen (PSA) le...
Figure 4: A 63-year-old male with a prostate-specific antigen (PSA) le...

ABSTRACT: Compared with earlier prostate MRI techniques that suffered from relatively poor sensitivity and specificity for detecting prostate cancer because of their reliance predominantly on morphology, multiparametric prostate MRI (mpMRI) in 2013 provides a wealth of functional information that has made possible vastly improved detection and characterization of prostate cancer. Our aims in this article are to describe the various imaging sequences that comprise the mpMRI exam, as well as to review current literature on the strengths/weaknesses of these sequences; to delineate strategies for standardizing interpretation and reporting of MRI results; and finally, to expound on the role that prostate MRI currently does and potentially can play in clinical practice.


Over the last decades, prostate-specific antigen (PSA) screening has lead to earlier detection of prostate cancer (PCa), with a resultant decrease in average clinical and pathologic stage at the time of diagnosis. In addition to facilitating early diagnosis of aggressive lesions, the relatively high sensitivity of PSA screening can also result in the detection of small and low-grade prostatic malignancies that may not be life-threatening. Radical whole-gland therapy for indolent lesions exposes patients to the potential for treatment-related morbidities, which could in some cases outweigh the benefits of therapy. Concerns about potential overtreatment of indolent disease has lead to interest in gland-preserving strategies, including active surveillance and various types of focal therapy.

Clinical parameters, including digital rectal examination results, PSA values, and the results of transrectal ultrasound (TRUS)-guided biopsies, among others, can be used to stratify patients into risk categories (D’Amico criteria),[1] to predict the likelihood of disease extension outside the prostate (Partin tables),[2] and to predict recurrence after prostatectomy (Kattan nomogram).[3] Such predictive tools aid clinicians in choosing among various treatment strategies based on a patient’s underlying risks. However, sampling error intrinsic in TRUS-guided prostatic biopsy[4] has been shown to lead to the undergrading of disease in a substantial proportion of patients, which could potentially result in a suboptimal initial choice of therapeutic strategy. In one series of 1,565 patients considered candidates for active surveillance who proceeded to radical prostatectomy, Mufarrij et al reported that approximately 46% were upgraded to a Gleason score of 7 or greater at final histopathology.[5] Three-dimensional transperineal mapping biopsies (TPMB) provide a more thorough sampling of the gland, facilitating improved pretreatment staging[6]; however, TPMB can still miss clinically significant disease, typically requires general anesthesia, and may carry a higher complication rate than TRUS-guided biopsy.

Given the backdrop of increasing diagnosis of early-stage disease and the inherent challenges in choosing an optimal treatment strategy in some patients using current clinical paradigms, there is a need for improved disease detection, staging, and risk-stratification via noninvasive imaging. Among the various imaging modalities used in the management of prostate cancer patients, only MRI has both the spatial resolution and soft-tissue contrast necessary to most accurately characterize localized PCa.

The use of MRI to evaluate the prostate dates back over 3 decades.[7] Earlier iterations of prostate MRI relied predominantly on morphologic and signal changes present on T1- and T2-weighted images and suffered from relatively poor sensitivity and specificity for detecting PCa. Newer MRI sequences, including diffusion-weighted imaging (DWI) and dynamic contrast-enhanced MRI (DCE-MRI), provide additional functional information about tissues and have enabled significant improvements in the ability of MRI to detect and characterize focal prostatic lesions. MR spectroscopic imaging is also used in some centers to help differentiate between malignant and benign tissue within the prostate. Current state-of-the-art prostate MRI consists of a multiparametric approach, in which two or more functional sequences complement the morphologic information provided by T2-weighted imaging. This article will attempt to summarize the hardware and various sequences that comprise a prostate multiparametric MRI (mpMRI) exam, and where applicable, will emphasize limitations and areas for future improvement. Strategies for interpretation and reporting of MRI results will be discussed, and finally, the role of prostate MRI in clinical practice will be explored.


The stronger main magnetic field of 3.0 Tesla MRI systems provides a higher signal-to-noise ratio (SNR) compared with 1.5 Tesla systems.[8] This increased SNR can be used to improve the spatial resolution and/or the acquisition time of the MR images. Acceptable images of the prostate can be obtained at both 1.5 and 3.0 Tesla when using appropriate coil and sequence selection.[9] However, in the authors’ opinion, use of a 3.0 Tesla system can improve the performance of any underlying mpMRI protocol and is advantageous whenever available in one’s practice.

While prostate MRI at a minimum entails use of a phased-array coil laid directly across the patient’s pelvis, in many centers, an endorectal coil (ERC) is also employed to complement the external pelvic coil. Because an ERC is located only a few millimeters from the prostate gland, it can further augment the amount of signal available for image generation. The additional signal available from an ERC is likely most advantageous at 1.5 Tesla, whereas the higher overall signal available at 3.0 Tesla makes the necessity of ERC use at this field strength less certain. Heijmink et al did report improved image quality, tumor detectability, and staging performance with the use of an ERC compared with body array coils at 3.0 Tesla[10]; however, Kim et al more recently reported equivalent performance of ERC and body array coils for prostate cancer staging.[11] It is important to note that these two studies only evaluated the diagnostic performance of T2-weighted images, and the applicability of the findings to multiparametric exams incorporating additional functional sequences is uncertain.

Although employing an ERC can provide very high-quality images, there are substantial trade-offs to be considered, including discomfort secondary to ERC placement, which can be fairly significant in some patients and can lead to poor compliance with the exam; magnetic susceptibility and motion-related artifacts that can be related to ERCs, particularly at 3.0 Tesla; and finally, workflow considerations regarding the incorporation of ERC into a prostate MRI practice—namely, increased examination time resulting from the placement and removal of the coil, as well as the personnel required to do this and the cost of the coil itself. In summary, ERCs afford both advantages and disadvantages in mpMRI; at 3.0 Tesla, the necessity for ERC use has not been clearly established, and adoption varies on a center-by-center basis.

Components of a Multiparametric Prostate MRI Exam

T2-weighted imaging

T2-weighted fast-spin echo images acquired in multiple planes represent key components of a prostate mpMRI exam. Images should be acquired with high resolution, accomplished by using a small field-of-view and a narrow image thickness of 3 to 4 mm. High-resolution T2-weighted imaging (T2WI) currently provides the best assessment of the prostate’s morphology, margins, and internal structure. The ejaculatory ducts, urethra, and verumontanum are frequently visualized on high-quality T2WI, and these internal landmarks can aid in the correct identification of zonal anatomy, and thus in lesion localization. Differentiation between the peripheral zone (PZ) and central gland (CG) is essential for accurate lesion localization, and making this distinction is typically easy on T2WI. The term “central gland” is often used in prostate MRI reports to refer to the combined central zone (CZ) and transition zone (TZ), which may be difficult to distinguish in a fraction of patients.[12] Vargas et al recently showed that the CZ can be identified as a distinct region in most patients. Appropriate recognition of the CZ is important to avoid its misinterpretation as a potential tumor; however, a very small fraction of tumors may in fact occur within the CZ, and these tend to have more aggressive features compared with CG tumors that only involve the TZ.[12] In terms of staging, the superior morphologic information provided by high-resolution T2WI facilitates assessment of seminal vesicle invasion, extracapsular extension, and invasion of the neurovascular bundles.

The normal glandular tissue in the PZ is predominantly high in signal on T2WI, whereas PCa lesions in the PZ appear as dark (hypointense) foci, possibly round or oval in shape.[13] Unfortunately, some foci of PCa may appear isointense to adjacent benign PZ on T2-weighted images, especially when small or of lower grade. Moreover, in many patients referred for prostate MRI, the PZ is not homogeneously bright, but rather a patchwork of varying signal intensities, secondary to factors such as atrophy, prior episodes of prostatitis, or post-biopsy hemorrhage.[13] Because post-biopsy changes can mimic PCa on T2WI, it is generally recommended to delay mpMRI for at least 8 to 12 weeks after biopsy,[9] and it is also important to evaluate non-contrast T1-weighted images for evidence of biopsy-related hemorrhage.[13]

Several recent publications concerning mpMRI have reported on the diagnostic performance of T2WI for PCa localization.[14-19] In a recent meta-analysis, Tan et al incorporated data from 14 studies with histopathologic correlation and reported an overall sensitivity and specificity for T2WI alone of 0.57−0.62 and 0.74−0.78, respectively.[20] Even when images are acquired using optimal technique, the overall moderate performance of T2WI alone has resulted in the need to incorporate additional functional sequences to facilitate more accurate lesion identification.

Diffusion-weighted imaging

DWI provides functional information about tissue microstructure. (For a concise review of the technical aspects of DWI and its applications in oncologic imaging, a recent review by Koh and Collins[21] is recommended.) DWI relies on the application of a diffusion-weighting gradient to water protons, which generates sensitivity of the measured signal to the ability of water protons to move freely in space. Water protons that are relatively hindered in their motion will appear as bright on DWI due to the application of this additional gradient. Changing the amplitude of the diffusion-weighting gradients varies the degree of diffusion weighting for a given set of DWI images, which is referred to as its “b-value.” At different b-values, DWI interrogates water movement over different length scales[21]; at low b-values, DWI predominantly reflects water movement over larger length scales, mainly secondary to capillary perfusion, whereas at higher b-values, DWI interrogates movement over small length scales, such as within cells or intracellular organelles. Importantly, the signal present on a DWI image represents a combination of both diffusion-related signal and signal secondary to T2 relaxation. If images with a minimum of two different b-values are acquired, an apparent diffusion coefficient (ADC) map can be generated that is intended to better represent the diffusivity of protons within tissue without the confounder of T2-related signal.[21] The ADC map generated from DWI is particularly helpful for PCa identification.

The role of DWI in the noninvasive evaluation of malignancy has grown tremendously over the past decade. The higher cellular density present in many tumors, in conjunction with more complex intracellular microstructure and likely other factors, leads to restricted diffusion of water, which is detectable on DWI images. The value of DWI for PCa imaging has been established in numerous publications in recent years.[16-20,22,23] In a recent meta-analysis pooling data from 627 patients, including both PZ and CG tumors, Wu et al reported a summary sensitivity and specificity for DWI combined with T2WI of 0.76 and 0.82, respectively, and this was shown to be superior to T2WI alone.[22] A separate meta-analysis by Tan et al, pooling data from a total of 5,892 lesions, reported a sensitivity, specificity, and area under the receiver operating characteristic (ROC) curve of 0.69, 0.89, and 0.85, respectively, for DWI alone, which was significantly better than the performance of T2WI alone (0.60, 0.76, and 0.75, respectively).[20] Interestingly, in this study, the specificity of DWI alone was superior to the combination of DWI+T2WI and was also found to be superior to the specificity of DCE imaging.

In addition, ADC values derived from DWI images have been shown to be inversely correlated with the Gleason score of lesions at biopsy or surgery.[24-27] Attempts have been made to define ADC cutoff values, both to differentiate PCa from benign tissue and to further subdivide foci of PCa into categories of different degrees of aggressiveness (see section on assessment of lesion aggressiveness below). However, the wide overlap in the ranges of ADC values for normal PZ tissue and PCa,[27-30] as well as differences in scanner hardware/software between centers, have made it difficult to define consistently reliable cutoff values. Furthermore, there is a strong dependence of the calculated ADC values on the specific b-values employed by a DWI sequence,[29] and this is also thought to contribute to the differing ranges of ADC values reported for PZ tissue and PCa in different publications.

Dynamic contrast-enhanced imaging

Angiogenesis may lead to varying combinations of increased blood flow, microvascular density, and capillary leakiness in malignant lesions compared with the organ from which a cancer arises. DCE-MRI takes advantage of these vascular differences to facilitate lesion detection, and Verma et al recently provided a useful overview of the applications of DCE-MRI in PCa.[31] Several reports have demonstrated the utility of DCE-MRI for PCa lesion identification, either alone or in combination with other sequences.[14,15,32,33] There are a wide variety of techniques for performing and interpreting DCE-MRI. In general, a T1-weighted spoiled gradient-recalled echo sequence is run prior to contrast administration, and the sequence is re-run repetitively (dynamically) after the rapid infusion of an intravenous bolus of a low-molecular-weight gadolinium chelate.

There are three methods of interpreting DCE-MRI: qualitative, semi-quantitative, and quantitative. Qualitative analysis can range from visual inspection of the images for rapidly and intensely enhancing lesions, to the plotting of kinetic curves of signal intensity vs time. The semi-quantitative approach to DCE-MRI interpretation begins with the calculation of various kinetic parameters (such as time to peak enhancement, wash-in rate, or wash-out rate) on a voxel-by-voxel basis; then, colorized parametric maps representing these parameters are overlaid on top of morphologic images, such as T2WI, to facilitate interpretation. Finally, one can perform a quantitative interpretation of DCE-MRI data, which attempts to assess microvascular changes in tumors by converting the acquired signal intensity into the true gadolinium concentration in tissues; this method employs pharmacokinetic models to determine the rate of exchange of contrast between plasma and the extravascular, extracellular space.[31] Specific quantitative vascular parameters, such as Ktrans and Kep, have been shown to be elevated in tumors, and assessment of these parameters has been shown to improve the specificity of prostate MRI compared with T2WI alone.[32]

The different approaches to DCE-MRI interpretation each have advantages and disadvantages. Although simplistic, simple visual assessment of the source images has been shown to be effective[34] and is employed at some centers; in fact, recent mpMRI guidelines provided by the European Society of Urogenital Radiology (ESUR) rely on analysis of kinetic curves for DCE-MRI interpretation.[9] The advantages of this approach include the lack of a need for special dedicated software or computer workstations. The semi-quantitative and quantitative approaches to DCE-MRI interpretation require dedicated software and/or computer hardware for interpretation, and can be time-consuming. Proponents of the quantitative approach have noted that analysis based on kinetic curves or semi-quantitative kinetic parameters depends heavily on the rate of contrast injection, whereas the quantitative approach may be more robust in its resistance to variation in injection-related factors.[31] The quantitative approach has also been proposed to be more reproducible, enabling serial measurements of perfusion parameters over time to facilitate evaluation of treatment response. As an example, Low et al recently reported promising results by using serial quantitative DCE-MRI to monitor the response of PCa to stereotactic radiation therapy.[35] Ultimately, to the best of our knowledge, no report has clearly established the superiority of one DCE-MRI interpretation strategy over the others.

MR spectroscopic imaging

MR spectroscopic imaging (MRSI) provides information about relative concentrations of various metabolites in tissues and is most commonly performed with 3-dimensional chemical shift imaging.[9,36] The use of an ERC is strongly suggested for MRSI at 3.0 Tesla and is required for MRSI at 1.5 Tesla. Spectral tracings providing assessment of relative metabolite concentrations are acquired and overlaid on the T2 morphologic images. The metabolites of most interest in the setting of PCa are citrate and choline. Choline plays a key role in cell membrane synthesis, and choline and several related metabolites are present in higher concentrations in PCa compared with benign prostate tissue.[37] Citrate, on the other hand, is present in normal PZ tissue but is reduced in PCa. In general, the ratio of choline+creatine to citrate is higher in PCa compared with benign tissue, and the degree to which this ratio is elevated is used to determine the likelihood of PCa within a given voxel. Prostate MRSI is technically challenging and time-consuming, and many centers performing mpMRI do not include MRSI in their protocols. A prospective multicenter study conducted by the American College of Radiology Imaging Network evaluated 110 patients with MRSI (at 1.5 Tesla using ERC) and T2WI, and MRSI+T2WI showed an accuracy in PCa localization equivalent to that of T2WI alone.[38] Recent guidelines for mpMRI performance and interpretation provided by the ESUR list MRSI as optional, not required, for lesion detection and staging.[9]


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