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Automatic and Rapid Identification of Infarct Slices and Hemisphere in DWI Scans

Rationale and Objectives

Accurate, free of observer’s bias, and fast identification of acute infarct is critical in visual and automatic processing of stroke images. An automatic and rapid algorithm has been developed to identify the infarct slices and the hemisphere in diffusion-weighted imaging (DWI) scans.

Materials and Methods

Thirty-six DWI scans were acquired from five centers with the slice thickness of 4–14 mm. We also derive images from the original scans to assess the accuracy of the algorithm by using a wide range of infarct size and number of artifacts per unit area. Based on the difference in percentile characteristics of intensity normalized (infarct/noninfarct) images, two parameters are defined: R s for infarct slice identification and R h for infarct hemisphere identification. Using the identified infarct slices the infarct hemisphere is subsequently determined.

Results

The average sensitivity and specificity for slice and hemisphere identification were 98.1%, 51.4% and 91.7%, 91.7%, respectively. The processing time is ∼3–5 seconds on Matlab platform and on VC++ it is predicted ∼10 milliseconds. Based on simulation study, we can infer that the algorithm produces accurate results in most of the situations although the sensitivity goes down by ∼15% when the infarct size is small (<2–3% of image area) and the artifacts per unit area are large.

Conclusions

The proposed algorithm applied as a preprocessor can be useful to: 1) estimate location (hemisphere) and extent of infarct (number and location of slices), 2) reduce time and labor of infarct volume study, 3) cross-check visual interpretation, 4) form a part of an infarct segmentation module, and 5) improve localization of the midsagittal plane.

Diffusion-weighted Imaging (DWI) is used to evaluate infarct in acute ischemic stroke patients. Automatic and rapid identification of infarcts in DWI images is important both in visual scan reading and automatic image processing as it reduces time and increases confidence. More importantly, as a recent study ( ) shows, infarct location is fundamentally linked to neurologic deficits. Several automatic or semiautomatic segmentation techniques are proposed to reduce the total time of infarct segmentation compared with manual processing of data, which may have errors and observer’s bias. A semiautomatic method ( ) was developed to determine infarct volume by diffusion tensor magnetic resonance imaging. Another study ( ) proposed an unsupervised segmentation method using multiscale statistical classification and partial volume voxel reclassification in the case of diffusion tensor magnetic resonance images. A method based on the probabilistic neural network for selecting infarct slices and an adaptive (two-level) Gaussian mixture model for infarct segmentation was suggested by Bhanu Prakash et al ( ).

In this article, an automatic framework to detect the infarct slices and hemisphere is presented. We propose a conceptually simple and fast approach that utilizes the difference in image intensity distribution for infarct (hyperintense) and normal tissue (isointense). The difference in intensity percentile characteristics in isointense and hyperintense regions is used to define two parameters: 1) slice parameter R s to quantify the difference in infarct/noninfarct slices and 2) hemisphere parameter R h to identify the infarct hemisphere. The proposed method is applied to 36 DWI scans obtained from five different sources. The accuracy is assessed using images derived from combinations of infarcts of different sizes and normal tissue region containing different artifact densities (number of artifacts per unit area). The algorithm can be useful to: 1) estimate location (hemisphere) and extent of infarct (number and location of slices), 2) reduce time and labor of infarct volume study, 3) cross-check visual interpretation, 4) form a part of an infarct segmentation module ( ), and 5) improve localization of the midsagittal plane ( ). It can be applied as a preprocessor in a stroke computer-assisted diagnosis system ( ).

Materials and methods

Data Acquisition

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Data Description

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Algorithm

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Stage 1: Identification of infarct slices

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Figure 1, Flowchart diagram to explain summary of slice identification procedure.

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Concept of the algorithm

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Figure 2, An example of (a) diffusion-weighted image and (b) its histogram.

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Figure 3, (a) Synthetic image with a distribution of isointense pixels and its histogram, A/B = 1.2 and (b) synthetic image with a few isointense pixels replaced by hyperintense pixels and its histogram A/B = 0.8.

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Normalization of image

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Inorm=f*I−IminImax−Imin I

n

o

r

m

=

f

*

I

I

min

I

max

I

min

where I max and I min are the maximum and minimum intensity on a given slice and f is the normalization parameter. In our study, we selected f = 1 so that the maximum intensity is 1 and the minimum intensity is 0. The histograms of all the images have been plotted with 256 bins.

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Reference point and slice parameter R s

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Figure 4, (a) Percentiles of intensity of a real noninfarct slice and (b) percentiles of intensity of a real infarct slice.

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Rs=(1P50)(Pa+20−PaPb+20−Pb) R

s

=

(

1

P

50

)

(

P

a

+

20

P

a

P

b

+

20

P

b

)

where P a are percentiles in a slice above P 50 and P b are percentiles below P 50 .

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R s for different bands

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NormalizedRs=(Rs−min[Rs])/(max[Rs]−min[Rs]) Normalized

R

s

=

(

R

s

min

[

R

s

]

)

/

(

max

[

R

s

]

min

[

R

s

]

)

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Occurrence of peaks and flat region

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Figure 5, Plot of normalized R s for a volume in different B1-B4 bands the flat region corresponding to the predicted infarct is limited by the peak regions.

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Final width of flat region=[max (width of flat region in B1−B4)] Final width of flat region

=

[

max (width of flat region in B1

B4

)

]

In the example discussed ( Fig 5 ), the extrema of flat region for B1 is at 12 and 28, for B2 at 12 and 28, for B3 at 12 and 28 and for B4 at 11 and 28. The maximum width corresponds to B4 (28 − 11 = 17), so we take the final extrema of flat region as 11 to 28.

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Hypothesis of flat region and infarct slices

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Stage 2: Localization of Infarct Hemisphere

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Figure 6, Flowchart of a summary of hemisphere identification procedure.

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Figure 7, (a) Midsagittal plane dividing the image into left and right hemisphere, (b) plot of histogram and percentiles for an infarct hemisphere, and (c) plot of histogram and percentiles for noninfarct hemisphere. Note the density of percentiles is different to that observed in slice identification. This is because of different intensity range for both the hemispheres. The infarct hemisphere intensity distribution has both iso- and hyperintense, whereas normal hemisphere has only isointense pixel intensities.

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Selection of reference point (r i )

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Percentile characteristics and hemisphere parameter R h

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Rh=P50(Pa+20−PaPb+20−Pb) R

h

=

P

50

(

P

a

+

20

P

a

P

b

+

20

P

b

)

Also a higher value of P 50 is observed in case of the infarct hemisphere. Multiplying by P 50 enhances the difference of Hemisphere parameter between the infarct (noninfarct) hemispheres.

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R h for infarct and noninfarct hemisphere

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Synthetic Data Creation for Accuracy Estimation

Slice identification

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Figure 8, (a) An example of synthetic noninfarct slice created from original infarct slice and (b) example of synthetic images with combination of different foreground (infarct types) on the same background.

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Hemisphere identification

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Results

Slice Identification

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Figure 9, (a) Comparison of ground truth slices, algorithm-identified infarct slices, and whole volume, and (b) results of sensitivity, specificity, and Dice statistical index for the slice identification procedure.

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Hemisphere Identification

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Table 1

Results of Hemisphere Identification

Case GT AR 1 L L 2 R R 3 L R 4 R R 5 R R 6 R R 7 L L 8 L L 9 R R 10 L L 11 L L 12 L L 13 L L 14 R R 15 R R 16 R R 17 R R 18 R R 19 R R 20 L L 21 R R 22 R R 23 L L 24 L L 25 R R 26 R R 27 R R 28 L L 29 L R 30 R R 31 L L 32 L L 33 R L 34 R R 35 L L 36 L L

GT: ground truth, AR: Algorithm result, L: Left hemisphere, R: Right Hemisphere.

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Accuracy of the Algorithm

Slice identification

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Figure 10, (a) Area under receiver operating characteristic curves (AUC) corresponding to normalized R s determined for real cases with different artifact densities. AUC decreases by about 15% when the artifact density increases. (b) Sensitivity of hemisphere identification decreases by ∼10%–20% when artifact density goes from low to high.

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Hemisphere identification

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Discussion

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Figure 11, Illustration of sensitivity of slice parameter as compared with a median or ratio of difference of percentiles (see A/B in Fig 3 ) alone. Infarct slices are 13 to 29 in this example.

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Infarct Slice Detection

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Infarct Hemisphere Detection

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Limitations and Further Improvements

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Figure 12, Multistep postprocessing of diffusion-weighted images.

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Potential

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Conclusion

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Appendix

Testing for Peak Location

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Location of Flat Region

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if slope>−0.01, extrema=x_i else consider [x_i+1:x_i+3] if slope

0.01

, extrema

=

x_i else consider [x_i+1:x_i+3]

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Figure A, Different shapes of peaks and flat regions.

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References

  • 1. Menezes N.M., Ay H., Wang Zhu M., et. al.: The real estate factor: quantifying the impact of infarct location on stroke severity. Stroke 2007; 38: pp. 194-197.

  • 2. Martel A.L., Allder S.J., Delay G.S., et. al.: Measurement of infarct volume in infarct patients using adaptive segmentation of diffusion weighted MR images. MICCAI 1999; 1679: pp. 22-31.

  • 3. Li W., Li E., et. al.: Robust unsupervised segmentation of infarct lesion from diffusion tensor MR images using multiscale statistical classification and partial volume voxel reclassification. Neuroimage 2004; 23: pp. 1507-1518. J Tan

  • 4. Bhanu Prakash K.N., Gupta V., Bilello M., et. al.: Identification, segmentation and image property study of acute infarcts in diffusion-weighted images by using a probabilistic neural network and adaptive gaussian mixture model. Acad Radiol 2006; 13: pp. 1474-1484.

  • 5. Bhanu Prakash KN, Gupta V, Nowinski WL. Segmenting infarct in diffusion weighted imaging volumes. PCT/SG2006/000292, filed 3 October 2006.

  • 6. Nowinski W.L., Bhanu Prakash K.N., Volkau I., et. al.: Rapid and automatic calculation of the midsagittal plane in magnetic resonance diffusion and perfusion images. Acad Radiol 2006; 13: pp. 652-663.

  • 7. Nowinski W.L., Qian G., Bhanu Prakash K.N., et. al.: A CAD system for stroke MR and CT.2006.pp. 789. 92 Radiological Society of North America Scientific Assembly and Annual Meeting Program 2006, Chicago, IL: 25 November–1 December

  • 8. Bezdec J.C.: Pattern recognition with fuzzy objective function algorithms.1981.Plenum PressNew York

  • 9. Weisstein EW. Gaussian function. Available online from MathWorld: http://mathworld.wolfram.com/GaussianFunction.html

  • 10. Gibbons J.D.: Nonparametric statistical inference.ed 21985.M. Dekker

  • 11. Mann H.B., Whitney D.R.: On a test of whether one of 2 random variables is stochastically larger than the other. Annals of Mathematical Statistics 1947; 18: pp. 50-60.

  • 12. Linn S.: A new conceptual approach to teaching the interpretation of clinical tests. J Stat Educ 2004; 12: Available online from: www.amstat.org/publications/jse/v12n3/linn.html

  • 13. Zou K.H., Warfield S.K., Bharatha A., et. al.: Statistical validation of image segmentation quality based on spatial overlap index. Acad Radiol 2004; 11: pp. 178-189.

  • 14. Kinnard L.M., Lo S.C.B., Duckett E., et. al.: Mass segmentation of dense breasts on digitized mammograms: Analysis of probability-based function. Medical Imaging 2005; 5747: pp. 1813-1823. Image Processing. Proceedings of the SPIE 2005

  • 15. Hanley J.A., McNeil B.J.: The meaning and use of area under a receiver operating characteristic (ROC) curve. Radiology 1982; 143: pp. 29-36.

  • 16. Moritani T., Ekholm S., Westesson P.L.: Diffusion weighted MR imaging of the brain.2005.Springer-VerlagBerlin

  • 17. Bammer R., Markl M., Barnett A., et. al.: Analysis and generalized correction of the effect of spatial gradient field distortions in diffusion-weighted imaging. Magnet Reson Med 2003; 20: pp. 560-569.

  • 18. Nowinski W.L., Qian G., Bhanu Prakash K.N., et. al.: Analysis of ischemic stroke MR images by means of brain atlases of anatomy and blood supply territories. Acad Radiol 2006; 13: pp. 1025-1034.

  • 19. Nowinski W.L., Thirunavuukarasuu A.: The Cerefy clinical brain atlas on CD-ROM.2004.ThiemeNew York

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