Conspicuity of breast lesions at different b values on diffusion-weighted imaging
© Chen et al.; licensee BioMed Central Ltd. 2012
Received: 29 November 2011
Accepted: 27 July 2012
Published: 2 August 2012
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© Chen et al.; licensee BioMed Central Ltd. 2012
Received: 29 November 2011
Accepted: 27 July 2012
Published: 2 August 2012
Diffusion-weighted (DW) imaging has shown potential to differentiate between malignant and benign breast lesions. However, different b values have been used with varied sensitivity and specificity. This study aims to prospectively evaluate the influence of b value on the detection and assessment of breast lesions.
Institutional review board approval and informed patient consent were obtained. Between February 2010 and September 2010, sixty women suspected of having breast cancer by clinical examination and mammography underwent bilateral breast MRI and DW imaging (with maximum b values of 600, 800, and 1000 s/mm2). Conspicuity grades of lesions at different b values on DW images were performed. Signal intensity and apparent diffusion coefficient (ADC) values were recorded and compared among different b values by the signal-to-noise ratio (SNR), contrast-to-noise ratio (CNR) and receiver operating characteristic (ROC) curve.
Fifty-seven lesions from 52 recruited patients including 39/57 (68%) malignant and 18/57 (32%) benign were confirmed with pathology. DCE MRI accurately detected 53 lesions with the sensitivity of 93.0% and specificity of 66.7%, and DW imaging accurately detected 51 lesions with the sensitivity of 89.5% and specificity of 100%. There were no significant differences in conspicuity grades compared among the three b values (P = 0.072), although the SNR and CNR of breast lesions decreased significantly with higher b values. Mean ADCs of malignant lesions (b = 600 s/mm2, 1.07 ± 0.26 × 10-3 mm2/s; b = 800 s/mm2, 0.96 ± 0.22 × 10-3 mm2/s; b = 1000 s/mm2, 0.92 ± 0.26 × 10-3 mm2/s) were significantly lower than those of benign lesions (b = 600 s/mm2, 1.55 ± 0.40 × 10-3 mm2/s; b = 800 s/mm2, 1.43 ± 0.38 × 10-3 mm2/s; b = 1000 s/mm2, 1.49 ± 0.38 × 10-3 mm2/s) with all P values <0.001, but there were no significant differences among the three b values (P = 0.303 and 0.840 for malignant and benign lesions, respectively). According to the area under the ROC curves, which were derived from ADC and differentiate malignant from benign lesions, no significant differences were found among the three b values (P = 0.743).
DW imaging is a potential adjunct to conventional MRI in the differentiation between malignant and benign breast lesions. Varying the maximum b value from 600 to 1000 s/mm2 does not influence the conspicuity of breast lesions on DW imaging at 1.5 T.
Magnetic resonance imaging (MRI) is becoming a powerful tool to help with the detection, diagnosis, and staging of breast cancer [1–3]. Based on the morphology and enhancement pattern of lesions, contrast-enhanced MRI offers an overall sensitivity of 90% and specificity of 72% in detecting breast lesions according to a published meta-analysis . Therefore the classification of a breast lesion as malignant or benign still has its shortcomings when detected with MRI [2, 4].
In recent years, diffusion-weighted (DW) imaging has been applied to distinguish between malignant and benign breast lesions [5–11]. DW imaging allows for noninvasive characterization of biologic tissues based on their water diffusion properties. Additionally, it provides information about the biophysical properties of tissues, such as cell organization and density, microstructure, and microcirculation. DW imaging enables the quantitative evaluation of apparent diffusion coefficient (ADC), an important parameter since a lower ADC has been associated with malignancy (7‐11). This occurs because of restricted water movement in high cellularity tumours (5,12). ADC may be an effective parameter in distinguishing between malignant and benign breast lesions. However, sensitivity and specificity values vary and range from 62.5% to 92.8% and 45.8% to 96.7%, respectively . The reported mean ADC of malignant lesions ranges from 0.90 to 1.61 × 10-3 mm2/s and that of benign lesions from 1.41 to 2.01 × 10-3 mm2/s. These distributions have resulted in a recommended ADC cutoff value ranging from 1.1 to 1.6 × 10-3 mm2/s between malignant and benign lesions . Comparison of the diagnostic performance of breast DW imaging among the studies has been compromised by the lack of standardization [15–17].
On clinical MRI scanners, diffusion sensitivity is easily altered by changing the diffusion gradient factor, which is also known as the “b value”. This value is proportional to the gradient amplitude and duration. By using at least two different b values, the ADC can be calculated. Tsushima et al. reported that the maximum b value (bmax) correlated with the mean ADC of malignant and benign tumours. In previous studies, it should be noted that bmax ranged from 300 to 1000 s/mm2, with a total of two to five values in between . For DW imaging, a higher b value provides more tissue diffusivity and less T2 shine-through effect [19, 20]. However, higher b values may result in poor image quality due to an inferior signal-to-noise ratio (SNR) at 1.5 T [21, 22]. Therefore, Matsuoka et al. proposed a systematic evaluation of b values . The optimum b value should sufficiently suppress the background signal of the glandular parenchyma and provide a lesion signal that is strong enough to allow image interpretation. Additionally, it should differentiate malignant and benign lesions with the best accuracy.
Based on these concepts we have carried out a prospective study to evaluate the influence of different b values on lesion conspicuity, the ADC measurement and the performance of ADC for the differential diagnosis between malignant and benign breast lesions.
The study was approved by our institutional review board. Informed consent was obtained from all patients before participation in the study. Sixty patients with palpable breast mass and clinical indication for breast MRI were enrolled from February 2010 to September 2010. Three patients were excluded because of movement or susceptibility artifacts seen on DW imaging. Two additional patients were lost without sufficient follow-up. Thus, 55 women (mean age, 49.6 years; range, 23-75 years) who met the following inclusion criteria were included in our study. 1) Insufficient or suspicious mammography findings (breast mass, architectural distortion, and focal asymmetry) diagnosed as Breast Imaging Reporting and Data System (BI-RADS) 0, 4, 5; 2) The final diagnosis was confirmed by means of surgery or core needle biopsy; 3) Clinical and imaging follow-ups were performed for at least 12 months by using a combination of ultrasound and mammography.
MRI examination was performed with a 1.5 T system (Signa; GE Medical Systems, Milwaukee, Wisconsin) using a dedicated four-channel breast coil on patients in the prone position. The imaging protocol began with standard anatomical series, including fast spin-echo (FSE) T1-weighted imaging, FSE T2-weighted imaging, and short T1 inversion recovery (STIR) imaging. Subsequently, three distinct DW sequences using b = 0 and b = 600, 800 or 1000 s/mm2 were performed by using single-shot echo-planar imaging (SSEPI) and frequency selection fat-suppression with the same following parameters: TR/TE = 5000/72.1 ms, matrices = 128 × 128, number of excitations = 4, section thickness/interslice gap = 5/0 mm, and field of view = 320 mm. The DW series were acquired in the transverse plane and covered both breasts. Diffusion gradients were encoded in 3 orthogonal axes (x, y, and z). Acquisition time was 1 minute 20 seconds with 20-24 slices. Finally, a T1-weighted 3D fast spoiled gradient-recalled echo sequence with parallel imaging (VIBRANT) sequence was used for dynamic contrast-enhanced imaging. Precontrast T1-weighted images were subtracted from the postcontrast T1-weighted dynamic images on a pixel-by-pixel basis.
All images were transferred to a workstation (Advantage Windows, version 4.2; GE Healthcare) for analysis, and the DW images were postprocessed with commercial software (FuncTool, GE Healthcare) to obtain ADC maps. Each patient had 3 ADC maps created using two b values, 0 and either 600, 800, or 1000 s/mm2. Two radiologists (both with 5 years of experience in breast imaging; 11 and 6 years of experience in MRI, respectively) independently evaluated each DW image and ADC map alone. To resolve disagreement between observers, a third radiologist (with 5 years of experience in breast imaging; 20 years of experience in MRI) assessed all involved items. The majority opinion was used for analysis.
Conspicuity grades of breast lesions on the high b value DW imaging
1 = not seen
Isointensity (symmetric signal intensity of bilateral breast)
2 = probably seen
Nonlocalized, mild to moderate signal with indistinct margin
3 = seen
Circumscribed, mild to moderate signal with definite margin
4 = readily seen
Nonlocalized, strong signal with indistinct margin
5 = well seen
Circumscribed, strong signal with definite margin
Signal intensity (SI) was recorded on the high b value DW imaging and ADC was documented. Circular regions of interest (ROIs) were drawn manually in the central region of the homogeneous lesions, or in the hypointensity region of the heterogeneous lesions on ADC maps using narrow window width. Lesion signal intensity (SIlesion) and ADC were then automatically calculated. Signal intensity (SInormal) and ADC of normal tissue were measured by placing ROIs in homogeneous breast parenchyma without enhancement in the centre of the contralateral breast, avoiding contamination by fatty tissue. Finally, ROIs were drawn manually in the anterior area outside of the breast to measure noise intensity (SInoise) and standard deviation (SDnoise). The area of ROI was measured to be 10 ± 2 mm2.
The surgeon and study coordinator recorded the lesion location for all patients who underwent surgery or biopsy. A pathologist then performed pathological examination blinded to imaging diagnosis. The results of anatomy and histology were correlated with the results of MRI by the study coordinator who had access to all images and clinical data of the patients, including their pathology.
Data were analyzed using the SPSS13.0 software package (SPSS Inc, Chicago, IL, USA). Probability values of less than 0.05 were considered significant. The conspicuity grades of the lesions on 3 DW series (b = 0, 600), (b = 0, 800), (b = 0, 1000) were compared using a Friedman signed rank test. SI was analyzed by measurement of SNR and contrast-to-noise ratio (CNR). SNR was calculated by SNR = SIlesion/SDnoise. CNR was calculated by CNR = (SIlesion-SInormal)/SDnoise. Comparisons of the mean SIlesion, SInormal, SInoise, SNR, CNR, and ADC among different b values were performed using one-way analysis of variance (ANOVA) test. For comparison of the mean ADC between malignant and benign lesions, we used the independent samples t-test. Receiver operating characteristic (ROC) curve analysis was used to quantify the diagnostic accuracy of ADC measurements. Nonparametric testing was performed to compare the area under the curve (AUC).
Histological composition of malignant and benign lesions
Malignant (n = 39)
Benign (n = 18)
Mean SI, SNR and CNR at the three b values on DW images (Mean ± SD)
B value (s/mm2)
853.2 ± 58.6
719.4 ± 34.4
254.2 ± 89.2
133.4 ± 20.4
117.5 ± 7.2
89.7 ± 15.9
77.3 ± 5.9
629.3 ± 47.5
571.6 ± 28.6
178.4 ± 60.8
97.9 ± 6.8
83.7 ± 8.9
64.1 ± 4.8
54.5 ± 8.0
473.4 ± 40.3
441.4 ± 21.1
150.1 ± 45.8
69.6 ± 4.0
59.6 ± 8.9
46.0 ± 3.4
40.3 ± 7.9
Mean ADCs of malignant and benign lesions at the three b values with corresponding P values for analyzed subgroups (×10 -3 mm 2 /s)
B value (s/mm2)
Mean ADC of malignant lesions (Mean ± SD)
95% Confidence interval
Mean ADC of benign lesions (Mean ± SD)
95% Confidence interval
0.92 ± 0.26
1.49 ± 0.38
1.96 ± 0.22
1.43 ± 0.38
1.07 ± 0.26
1.55 ± 0.40
DW imaging involves the random motion of water molecules, which is detected as attenuation of the measured SI . The motion of water molecules is more restricted in tissues with a higher cellular density and associated with numerous intact cell membranes [5, 12, 24]. Therefore, highly cellular areas will appear to be higher in SI on DW images. Our study demonstrates that breast lesions displayed mild to strong SI on DW images compared to surrounding breast parenchyma, and intensity of malignant lesions was generally higher than that of benign lesions. Mean conspicuity grades of malignant lesions were 4.44 ± 0.97 at b = 600 s/mm2, 4.38 ± 1.04 at b = 800 s/mm2 and 4.36 ± 0.96 at b = 1000 s/mm2. Those of benign lesions were 2.56 ± 1.38 at b = 600 s/mm2, 2.56 ± 1.38 at b = 800 s/mm2 and 2.17 ± 0.99 at b = 1000 s/mm2. There was a highly significant difference in the conspicuity between malignant and benign lesions (P < 0.0001). Most malignant lesions were circumscribed and displayed strong signals with definite margins on DW images. Margin characteristics, such as the appearance of being spiculated, could not be displayed on DW images for inferior spatial resolution and partial-volume effect. Most benign lesions displayed mild to moderate signal with indistinct or definite margins on DW images. However, DW imaging cannot detect all lesions detected by other conventional MRI. This has been described previously, with 6–37.5% of malignant breast lesions reportedly not visible on DW imaging [25–27]. One DCIS and 1 hyperplastic lesion presented as non-mass enhancement on contrast-enhanced imaging but were invisible on DW imaging in the study. One fibroma displayed significant hypointensity on both T1WI and T2WI, but it was not detected on DW imaging because the signal intensity was similar to background.
DW imaging also allows quantitative calculation of ADC for each pixel of the image and is displayed as a parametric map. ADC is measured by acquiring the MR signal at least twice, typically with (Sb) and without (S0) diffusion weighting by the following formula: ADC = [In (S0/Sb)]/b, where Sb and S0 are the signal intensities on the DW imaging and the reference imaging without diffusion weighting, respectively . Areas of restricted diffusion in highly cellular areas show low ADC compared with less cellular areas that return higher ADC values. Malignant tumours are frequently more cellular than benign lesions from which they originate and, thus, appear to be of relatively low ADC levels on ADC maps. Furthermore, ADC of invasive tumours appears to be lower than that of carcinoma in situ [5–7, 9, 29–31]. High-grade lesions with the highest cell proliferation rate would have the lowest ADC, which is still controversial [12, 31–33]. Our results are in good agreement with previously published results on breast ADC calculation. The mean ADCs of breast cancers were significantly lower than those of benign lesions with all P values <0.001 at b values of 600, 800 and 1000 s/mm2. However, for some malignant and benign lesions, there is overlap between ADC values. This is based both on our study and the studies of others. Based on pathological analysis, 1 invasive ductal carcinoma and 1 medullary carcinoma showed ADCs that were within the confidence interval for benign lesions because of lower cellular density. One plasma cell mastitis showed a very small ADC value, possibly because of an increase in macromolecule protein and phlogocyte infiltration. Therefore, detection and characterization of breast lesions based solely on DW imaging is not sufficiently accurate, and DW imaging cannot solely substitute for other MR methods. DW imaging can be a potential adjunct to conventional MRI in the differentiation between malignant and benign lesions for fast imaging without the use of a contrast agent.
The diffusion gradient factor, also known as the “b value”, is an important parameter of DW imaging and determined by the following formula: b = γ2 G2 δ2(Δ – δ/3), where γ is the magnetogyric ratio, G is the gradient intensity, δ is the duration of the applied gradient, and Δ is the time interval between the paired gradients. A greater b value indicates a more severe phase dispersion of water molecules and a more reduced signal under the effect of gradient pulse on DW imaging . Our study demonstrates that the average SIlesion and SInormal decreased with increasing b values, and SI was more severely reduced in malignant than in benign lesions and normal parenchyma. Although SNR and CNR of lesions decreased significantly, the degree was not great enough to be visually identified on DW imaging with b value increasing from 600 to 1000 s/mm2. Most malignant (33/38) and benign (10/13) lesions showed the same conspicuity grades on the three DW imaging. All of lesions detected on the DW imaging at b = 600 s/mm2 remained at significant level on the DW imaging at the higher b values although the SI of some lesions decreased with increasing b values. The conspicuity grades of breast lesions were not significantly different among the three b values (P = 0.072). Bogner et al.  also compared CNR of breast lesions at different b values on DW imaging. They have found that mean CNR for malignant and benign tumours rose with increasing b values from 0 to 850 s/mm2, but decreased with even higher b values from 850 to 1200 s/mm2. The result of our study was not consistent with that of theirs. There are two considerable differences in materials and methods compared between our study and their study. First, we performed DW imaging at 1.5 T and they performed at 3.0 T. Second, CNR were calculated differently. We directly measured SDnoise in the anterior areas outside of breast . They calculated the standard deviation of intensities σ lesion and σ tissue in both volumes as SDnoise.
We also found that there were no significant differences for ADC calculation among the three b values (P = 0.436). The results are consistent with previously published data . Conversely, Peters et al.  have found that ADC of breast lesions varied substantially with the choice of different b values. However, they used quite different b values at 0, 150, 499, and 1500 s/mm2. ROC analysis revealed AUC of 0.858 ± 0.075 at b = 600 s/mm2, 0.870 ± 0.081 at b = 800 s/mm2 and 0.866 ± 0.073 at b = 1000 s/mm2 for the differentiation between malignant and benign lesions. No statistical significances were seen among the three b values (P = 0.743). The result is in good with previously published data involving the degree of b values ranged from 150 to 1500 s/mm2[35, 36].
It is first to prospectively evaluate the influence of b values on both the display and ADC measurement of breast lesions on DW imaging at 1.5 T. So far, only one similar study performed using 3.0 T . Our results suggest that there were significant differences in morphologic pattern and signal strength between malignant and benign lesions (P < 0.0001). Most malignant lesions were circumscribed and displayed strong signals with definite margins on DW images. Most benign lesions displayed mild to moderate signal with indistinct or definite margins on DW images. Other studies also demonstrated that strong signal on DW images could be help to diagnose malignant lesions, which is especially meaningful for patients who can’t accept contrast agent [37, 38]. The ductus or branch distribution and the sign of ring-shape were only seen on malignant lesions in our initial study. Many articles have investigated the performance of ADC in discriminating breast lesions. However, the pooled ADC of malignant and benign lesions and their diagnostic performance vary with pathophysiologic characteristics, MRI techniques, and diagnostic criteria for malignancy in the studies. We think that the appearance pattern on DW imaging has potential value for differentiating malignant and benign breast lesions. This hypothesis should be verified by more clinical investigations.
Our study has some limitations. First, ROIs to measure SI and ADC were set by the operators, which is subjective and that little is known about the reproducibility of measurements. We found that some breast lesions were heterogeneous on DW images and ADC maps. Most tumours, especially malignant, have heterogeneous microenvironments. By drawing an ROI around a tumour, the summary statistical value does not adequately reflect lesion characteristics . In order to reduce the measurement biases and avoid contamination of the data by adjacent structures, we used a fixed small size of ROI. We selected the hypointensity region of the heterogeneous lesions on ADC maps which was the highest cellular density area on histopathological specimens as ROI to avoid omitting a malignant component of any given lesion.
In addition, we combined the minimal b value of 0 mm2/s and the maximum b values ranging from 600 to 1000 mm2/s to calculate ADC. According to previously published articles, the use of multiple b values did not increase the precision of ADC measurements. Instead, it increased vulnerability of patient movement due to longer acquisition times . A study performed with a 3.0 T MR imager suggested that ADC determination and DW imaging quality was optimum with a combined b value of 50 and 850 s/mm2. Therefore, further investigation is needed to estimate whether another minimum b value, other than 0 mm2/s, can reduce the perfusion effect and T2-shine through effect on DW imaging.
DW imaging is a potential adjunct to conventional breast MRI in differentiating between malignant and benign lesions. The performance of DW imaging at 1.5 T is not significantly influenced by varying the maximum b value from 600 to 1000 s/mm2. Further studies with larger populations are needed to confirm the use of DW imaging in the evaluation of breast lesions.
Apparent Diffusion Coefficient
Receiver Operating Characteristic
Magnetic Resonance Imaging
Maximum b Value
Breast Imaging Reporting and Data System
Short T1 Inversion Recovery
Single-shot Echo-planar Imaging
Regions of Interest
Lesion Signal Intensity
Normal Tissue Signal Intensity
Noise Standard Deviation
One-way Analysis of Variance
Area Under the Curve
Ductal Carcinoma in Situ.
This study was supported by National Natural Science Foundation of China (No.30701008).
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