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A Perceptually Tempered Display for Digital Mammograms1

Harold L. Kundel, MD , Susan P. Weinstein, MD , Emily F. Conant, MD , Lawrence C. Toto, BS and Calvin F. Nodine, PhD

1 From the Pendergrass Diagnostic Research Laboratory, Department of Radiology, University of Pennsylvania Medical Center, 308 Stemmler Hall, 3600 Hamilton Walk, Philadelphia, PA 19104. Recipient of a Certificate of Merit award for an infoRAD exhibit at the 1998 RSNA scientific assembly. Received April 9, 1999; revision requested May 12 and received June 10; accepted June 21. Supported by grants DAMD17-96-1-6153 and DAMD17-97-1-7130 from the U.S. Army Medical Research and Materiel Command. Address reprint requests to H.L.K.



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Figure 1.   The digital mammography workstation.

 


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Figure 2.   Input-output transfer characteristic of the CRT (top curve) and final minimal detectable contrast (MDC) look-up table (bottom curve). The curves have a common pixel driving level axis. The nonlinearity of the MDC curve is exaggerated for purposes of illustration; the actual difference from the linear curve is usually more subtle. The effect of the MDC look-up table on the displayed image can be seen by following the dotted lines, which represent extrapolation from the image pixel value to the display luminance.

 


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Figure 3.   MDC test pattern. G = typical observer response.

 


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Figure 4.   Approximation of the contrast sensitivity curve with a parabola. Heinemann (4) measured human contrast sensitivity at different levels of adapting luminance. Examples of this relationship at two adapting luminance levels are shown (solid lines). In reality, there is a whole family of curves of similar shape that have a minimum that shifts with the adapting luminance. Consider the lower curve, which corresponds to an adapting luminance of 100 cd/m2. The eye is maximally sensitive at a display luminance of 100 cd/m2, with an MDC of about 0.05. However, an object located in a dark part of the image at 10 cd/m2 would have to have a contrast of 0.1 to be seen. The practical solution in radiology is to use a spotlight to raise the luminance to 100 cd/m2 and improve the contrast sensitivity. As the adapting luminance decreases, the curves shift upward and maintain roughly the same shape. Attempts have been made to fit the curves from Heinemann's experimental data with simple equations (5). The algorithm of Liu and Nodine (8) required advanced information about adaptation level and was computationally intensive. We simplified that algorithm by assuming that a parabola (dashed lines) could be used to approximate contrast sensitivity at different levels of adapting luminance. The fit is reasonable at high adapting luminance (100 cd/m2), where radiologists prefer to operate. The fit for a lower adapting luminance (10 cd/m2 [upper curve]) is not very good. However, this luminance is well below a practical average viewing luminance.

 


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Figure 5.   Pattern used for sampling pixel intensities on the breast images. The intensities of the breast are sampled, and nontissue regions beyond the breast are eliminated.

 


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Figure 6a.   Mammographic image displayed with standard perceptually linearized display (a) and MDC-tempered display (b). The skin line (arrow in b) is not visible in the standard perceptually linearized display (a).

 


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Figure 6b.   Mammographic image displayed with standard perceptually linearized display (a) and MDC-tempered display (b). The skin line (arrow in b) is not visible in the standard perceptually linearized display (a).

 





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