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J Opt Soc Am A Opt Image Sci Vis. Author manuscript; available in PMC 2009 July 20.

Published in final edited form as:

PMCID: PMC2713058

NIHMSID: NIHMS120322

Aydogan Ozcan,^{1,}^{*} Alberto Bilenca,^{1} Adrien E. Desjardins,^{1} Brett E. Bouma,^{1} and Guillermo J. Tearney^{1,}^{2}

The publisher's final edited version of this article is available at J Opt Soc Am A Opt Image Sci Vis

See other articles in PMC that cite the published article.

Speckle noise is a ubiquitous artifact that limits the interpretation of optical coherence tomography images. Here we apply various speckle-reduction digital filters to optical coherence tomography images and compare their performance. Our results indicate that shift-invariant, nonorthogonal wavelet-transform-based filters together with enhanced Lee and adaptive Wiener filters can significantly reduce speckle and increase the signal-to-noise ratio, while preserving strong edges. The speckle reduction capabilities of these filters are also compared with speckle reduction from incoherent angular compounding. Our results suggest that by using these digital filters, the number of individual angles required to attain a certain level of speckle reduction can be decreased.

Optical coherence tomography (OCT) is a promising technology for imaging the microscopic structure of human tissue *in vivo* [1–14]. Owing to the coherent nature of the image formation process, OCT images suffer from speckle noise. Speckle noise limits the contrast and the signal-to-noise ratio (SNR) of OCT images, making the interpretation of architectural morphologic features required for clinical diagnosis difficult.

Speckle is problematic for other imaging modalities as well, including synthetic aperture radar (SAR), remote sensing, ultrasound, sonar, etc. In these fields, a substantial amount of signal processing research has been conducted to combat speckle noise, resulting in the development of powerful digital filters for reducing speckle while preserving edge sharpness [15–23]. Speckle reduction in OCT has been addressed by modifying imaging configurations and through the use of signal processing. Recently, some digital algorithms [6,9,12,13] have been applied to OCT images with encouraging results. Optical approaches that physically reduce speckle by incoherent averaging (compounding) have also been demonstrated [5,8,10,14].

In this paper, we evaluate classes of digital filters that are optimized to reduce speckle in an OCT image while maintaining strong edge sharpness. For this purpose, the performance of seven different speckle-reduction filters [15–23] were compared, namely, an enhanced Lee filter (ELEE) [15,17], two *à trous* wavelet-transform-based filters [18,19], a hybrid median filter (HMF) [20], a symmetric nearest-neighbor (SNN) filter [21], a Kuwahara filter [22], and an adaptive Wiener filter [23]. These filters have been successfully applied to the problem of speckle reduction for other imaging technologies as summarized in Table 1 [24–45]. Even though each filter will perform differently for different imaging modalities (depending on the physical origin of speckle), a quantitative comparison of the performance of these filters for different speckle patterns (e.g., OCT versus ultrasound) is beyond the scope of this paper.

We also compare digital filtering with a physical speckle-reduction technique [8,14], which involves acquiring several angularly resolved images and incoherently compounding these images to reduce speckle. With angular compounding, use of a large number of angles increases the complexity of the imaging system and the overall acquisition time. We therefore studied the possibility that by combining digital filtering and angular compounding, fewer angles could be utilized to attain a given speckle-reduction performance level.

Among the filters summarized in Table 1, the ELEE filter [17] is an improved version of the original Lee filter [15], which operates on the assumption that speckle is a multiplicative noise process, i.e., the speckle pattern is fully developed. In terms of performance and principles of operation, the Lee filter [15] is very similar to the Kuan filter [16], and for speckle reduction, the ELEE filter performs better than the original versions of both the Lee [15] and the Kuan [16] filters. For this reason, in this study we focus only on the ELEE filter from this class of filters. This class of filters is based on computing the local coefficient of variation, which measures the image homogeneity [17].

We also used two speckle-reduction filters that are based on a shift invariant, nonorthogonal wavelet transform called the *à trous* wavelet transform [18]. These algorithms reduce visual artifacts in filtered images that usually occur in regular shift-variant wavelet-transform-based filters due to the nature of the decimated orthogonal wavelet basis [18]. The main difference between the two *à trous* wavelet-transform filters used in this work is that the second filter [19], which we refer to as wavelet 2, applies a separate threshold value for each individual wavelet level. This operation results in speckle reduction with reduced ringing artifacts that usually occur with wavelet-transform-based filters.

Among other digital filters that we investigated, HMF is an edge preserving speckle-reduction filter that combines the advantages of median filters with adaptive filters [20]. The HMF type of filtering is especially suitable for nonstationary signals, and the filter output is basically the median of two adaptive subfilters and the input image [20]. The SNN filter [21] uses spatial-symmetry and nearest-neighbor constraints within the smoothing window to preserve the edges and corners in an image. One of the main advantages of the SNN filter is that it operates without searching the location and the orientation of the edges within the smoothing window, thereby saving computation time and decreasing complexity.

With the Kuwahara filter [22], the mean and variance of four subquadrants of a windowed section of the image is computed, and the output value of the center pixel in the window is replaced by the mean value of the region that has the smallest variance. Finally, the adaptive Wiener filter [23] computes the local mean and variance and nearest-neighbor constraints within the smoothing inside a window centered on each pixel of the input image. These local statistics are then used adaptively to generate a pixelwise Wiener filter. The entire image is filtered by repeating the same procedure for each pixel [23].

In this work, all of the above digital filters were implemented using MATLAB (version 7.1) on a 1.6 GHz Pentium M personal computer. Filter performance was evaluated using established speckle-reduction performance metrics [6,9,12,13], including SNR, contrast-to-noise ratio (CNR), and equivalent number of looks (ENL), which is a measure of the smoothness of a *homogeneous* region of interest. The following definitions for these image quality metrics were used [6,9,12,13]:

$$\begin{array}{l}\text{SNR}=10{log}_{10}(max\{{F}_{\text{lin}}^{2}\}/{\sigma}_{\text{lin}}^{2}),\\ \text{CNR}=(1/R)\sum _{r=1}^{R}({\mu}_{r}-{\mu}_{b})/\sqrt{{\sigma}_{r}^{2}+{\sigma}_{b}^{2},}\\ \text{ENL}=(1/H)\sum _{h=1}^{H}({\mu}_{h}^{2}/{\sigma}_{h}^{2}),\text{}\end{array}$$

(1)

where *F _{lin}* is the

We also defined an average figure of merit (FOM), FOM=SNR* _{n}*+ENL

To further quantitatively compare the performance of the filters, we defined the resultant image of the above-described angle compounding technique [14] (where *N*=64 mutually incoherent images were combined) as our *gold standard* image, *I _{G}*(

$$\text{MSE}=\frac{\int \int |{I}_{F}(x,y)-{I}_{G}(x,y){|}^{2}\text{d}x\text{d}y}{\int \int |{I}_{G}(x,y){|}^{2}\text{d}x\text{d}y}.\text{}$$

(2)

To compare the performance of the digital filters, we imaged a bovine retina *ex vivo* with an angle-resolved optical frequency-domain imaging (OFDI) system [14]. The OFDI system is composed of a wavelength-swept source (centered at 1295 nm with a range of 130 nm and a sweep rate of 25 Hz) and an InGaAs line-scan camera with 512 pixels [14]. We utilized 400 pixels of the InGaAs line camera to simultaneously record the backscattered light collected from an angular range of 32°. From these 400 images, approximately, 64 were determined to be mutually incoherent; these 64 were subsequently used for angular compounding.

The quantitative performance of the angle compounding is summarized in Fig. 1, and image data are presented in Fig. 2. The top row in Fig. 2 shows the unfiltered images of the same bovine retina for *N*=1, 4, and 64, where *N* refers to the number of angles used to form the compound image. Other rows of Fig. 2 (as will be explained in detail later on) show four different filter outputs for *N*=1, 4, and 64. Therefore each *column* in Fig. 2 shows the comparison (for a given *N*) between the unfiltered image and the filtered images. As can be seen in the top row of Fig. 2, it is evident that as *N* increases, speckle noise diminishes, due to the speckle reduction capability of the physical, angular compounding approach [14].

(Color online) Performance summary of various speckle-reduction filters applied to a bovine retina OFDI image. (a) and (b) show SNR, ENL, and CNR computed for each case. The results of (a) have been obtained by filtering the final image *after* angle compounding **...**

(Color online) Image recovery results for the *à trous* wavelet-transform-based filters (1 and 2), the ELEE, and the adaptive Wiener filters applied to the unfiltered images (postcompounding filtering). *N* number of angles; linear, filter applied **...**

Digital speckle-reduction filters can be applied in two different ways to OCT images (for *N*>1). (1) Postcompounding digital filtering, where the digital filter is applied to the final image after the angle compounding is done; and (2) precompounding digital filtering, where the digital filter is applied to each individual angle separately, and *N* of these filtered images are combined to form the final image. Next, we present the results of these two methods in separate sections.

Figure 1(a) shows the performance of the filters, when the filter is applied to the *final* image of the angle compounding (postcompounding filtering), and it clearly indicates that, for the unfiltered [no filtering (NF)] images, as *N* increases, all the image quality metrics improve as expected. However, except for the ENL criteria, the improvement by moving from *N*=16 to *N*=64 becomes less visible for the unfiltered images. Figure 1(a) also shows that especially the ELEE filter, the *à trous* wavelet-transform-based filters (1 and 2), and the adaptive Wiener filter significantly increase SNR and CNR (by >20 dB and ~2 times, respectively), and reduce speckle (an ENL increase of >2 times). Figure 1(c) shows the average FOM computed from the results of Fig. 1(a). The results show that the FOM was highest for the ELEE filter, the adaptive Wiener filter, and the wavelet-based filters [see Fig. 1(c)].

In terms of the MSE image quality metric [Eq. (2)], one can clearly see in Fig. 1(e) that as *N* increases the MSE drops rapidly, illustrating once again the speckle-reduction capability of the angular compounding approach [14]. For the NF image, an increase in *N* from 1 to 4 results in a decrease in MSE by more than a factor of 3 [see the dashed gray curves in Fig. 1(e)]. But what is more important is that *for each N*, the filtered images (except the SNN and Kuwahara filters) perform significantly better than the NF image corresponding to the *same N*. This property of Fig. 1(e) illustrates that for a given image (corresponding to a certain *N* value) digital filtering significantly reduces the speckle noise, making the final image look more like the gold standard image, *I _{G}*(

The resulting images obtained using these filters for *N*=1, 4, and 64 are also shown in Fig. 2, as rows. The filtered images indicate that the homogeneous regions of the image are smoothed out due to speckle reduction without any noticeable degradation in the edge sharpness. To further illustrate the effect of the filters on the edges, in Fig. 3, the retina edge in front of the background region is plotted in a single *A* line (400th *A* line of Fig. 2) for *N*=1, 4, 16, and 64 for the NF images as well as for the filtered images of Fig. 2. Figure 3 clearly demonstrates the excellent edge preserving properties of the filters: the background region (corresponding to pixel numbers ~1–25 in Fig. 3) is significantly smoothened for all *N* values with the digital filters when compared with the NF image; whereas the retina edge (corresponding to pixel numbers ~28–32 in Fig. 3) remained unchanged.

Figure 1(b) shows the performance metrics for the filters, when the filter was applied to *each individual angle* separately. Unless noted as “linear,” for each individual angle the logarithmic image was filtered, and this filtered image was then transformed back to linear units before the final compounding. For filters that are marked as linear in parentheses, for each angle the filter was applied to the linear image, and then the compounding of these filtered angles was again done in linear units. Therefore the compounding operation of *N* filtered images was always done in linear units. After compounding, the performance metrics (except SNR) were calculated for the logarithmic final compound image. The results of this second numerical study are only presented for the most promising filters, i.e., for the ELEE filter [17], the adaptive Wiener filter [23], and the wavelet-based filters [18,19]. The results indicate that, in the case of precompounding filtering, especially the adaptive Wiener filter together with the wavelet-based filter (e.g., wavelet 2, applied to linear images) perform relatively well, showing an SNR improvement of >25 dB with significant ENL and CNR improvements [see Fig. 1(b)]. Similar to Fig. 1(c), Fig. 1(d) shows the average FOM computed from the results of Fig. 1(b). This time wavelet 1 and the adaptive Wiener filters performed significantly better with respect to the above image quality metrics than the other filters, followed by the ELEE and wavelet 2 (applied to linear images).

The MSE performance [shown in Fig. 1(f)] of the precompounding approach was slightly worse than the MSE performance of the postcompounding approach [Fig. 1(e)]. Overall, in the case of precompounding filtering, the adaptive Wiener filter performed the best in terms of MSE criterion, providing for *N*=4 the same level of MSE as the unfiltered *N*=8 image yielded [see Fig. 1(f)]. This again illustrates that digital filtering can help to reduce the total number of angles used in an angle-compounding speckle-reduction scheme.

Figures 4 and and55 show the filtered images for the wavelet-transform-based filters (1 and 2), the ELEE filter, and the adaptive Wiener filter illustrating the improved speckle reduction with respect to the NF images at the top rows.

(Color online) Recovery results for the ELEE and the adaptive Wiener filters applied to each angle separately and then added in linear units (precompounding filtering). *N*, number of angles. Each image has 1000 *A* lines, where the distance between two adjacent **...**

To be able to better compare the performance of these digital filters for postcompounding versus precompounding, in Figs. 6 and and7,7, a zoomed version of the same bovine retina image [Figs. 2–5] is illustrated for *N*=4 and 8, respectively. The two columns in these figures represent a comparison between postcompounding versus precompounding for the filtered images. And the top row in each figure shows, for comparison purposes, the NF image of the same region. The results indicate that the performance of each filter (Wiener filter, ELEE, and the wavelet filters) is very similar visually for both postcompounding and precompounding. This conclusion is further supported numerically by a comparison of Figs. 1(a) and 1(b). On the other hand, with respect to computational efficiency, the postcompounding approach is at least *N* times faster than precompounding filtering, making the postcompounding option computationally efficient. Moreover, the MSE performance of the postcompounding approach is slightly better than the precompounding approach making it even more advantageous. Meanwhile, in both of these filtering approaches, as one can clearly see in Figs. 6 and and7,7, the degree of speckle reduction is significant when compared with the unfiltered images (top rows in Figs. 6 and and77).

(Color online) Comparison of the performance of precompounding versus postcompounding. In this comparison *N*=4 is used. Each image has 250 *A* lines, where the distance between two adjacent *A* lines is ~5 *μ*m. One hundred pixels are shown for **...**

It is quite important to note that, as is evident in Fig. 1, digital filtering improves the image quality metrics (SNR, ENL, CNR, and MSE) such that the number of individual angles and hence the total image acquisition time may be decreased with digital filtering. Specifically, the reader should compare the performance of the unfiltered *N*=16 image [the first green dots (middle line of top panel) in each row of Fig. 1(a)] with the adaptive Wiener filter's output for *N*=4 [the last red point (middle line) in each row of Fig. 1(a)], where in all of the three image quality metrics (SNR, ENL, and CNR) the result of the Wiener filter for *N*=4 performs better than the unfiltered *N*=16 image. A similar comparison between the unfiltered *N*=16 image and the filtered *N*=4 images can also be made in Fig. 1(b) for wavelet 1, ELEE, and the Wiener filters. These results, combined with the above-discussed MSE results of Figs. 1(e) and 1(f) imply a possible reduction in the number of required individual angles to achieve a given level of speckle reduction, defined by SNR, CNR, ENL, and MSE metrics. A comparison between Figs. 6 and and77 further supports this argument, since the zoomed versions of the filtered images for *N*=4 appear to have less speckle noise than the zoomed unfiltered image of *N*=8, again suggesting an important reduction in the number of required individual angles for speckle reduction.

We also applied the above-discussed digital filters to other OCT images and obtained similar good results. Another example is illustrated in Fig. 8 for an *ex vivo* human colon image obtained using the same OFDI system described above (for *N*=1). The digitally filtered images of Fig. 8 show the ability of these filters to reduce speckle in the OCT image, while strong edges and fine features are still well preserved.

(Color online) Image recovery results for the *à trous* wavelet-transform-based filters (1 and 2), the ELEE, and the adaptive Wiener filters applied to the unfiltered image (top image) of an *ex vivo* human colon tissue imaged using an OFDI system. **...**

Finally, Table 2 summarizes the computational performance of the filters for a representative case (unfiltered *N*=4 image of Fig. 2). The relative speed of each of the filters is determined from the computer's CPU time required to complete the processing. The adaptive Wiener filter was the fastest of all the filters, followed by the wavelet 1 filter. However, the MATLAB codes of the filters were not necessarily optimized to reduce the running time. The CPU times listed in Table 2 should therefore be considered preliminary estimates of the speed of the algorithms.

We have compared the performance of various speckle-reduction digital filters applied to optical coherence tomography images. Our findings indicate that shift-invariant, nonorthogonal wavelet-transform-based filters together with enhanced Lee and adaptive Wiener filters can significantly reduce speckle and increase SNR while still preserving some of the fine details of the image. These filters are also compared with a physical speckle reduction technique that acquires several angularly resolved images and compounds these different angles to reduce speckle. Our results suggest that by using speckle-reduction filters, the number of compounded images required to achieve a given set of image quality metrics can be reduced. This finding may enable easier and more time-efficient implementation of angular compounding in future OCT systems.

The authors thank Brian Goldberg and Alex Chau of MIT for their valuable comments and fruitful discussions.

1. Huang D, Swanson E, Lin CP, Schuman JS, Stinson WG, Chang W, Hee MR, Flotte T, Gregory K, Puliafito CA, Fujimoto JG. Optical coherence tomography. Science. 1991;254:1178–1181. [PubMed]

2. Fujimoto JG, Brezinski ME, Tearney GJ, Boppart SA, Bouma B, Hee MR, Southern JF, Swanson EA. Optical biopsy and imaging using optical coherence tomography. Nat Med. 1995;1:970–972. [PubMed]

3. Fercher AF, Hitzenberger CK, Kamp G, El-Zaiat SY. Measurement of intraocular distances by backscattering spectral interferometry. Opt Commun. 1995;117:43–48.

4. Tearney GJ, Brezinski ME, Bouma BE, Boppart SA, Pitris C, Southern JF, Fujimoto JG. *In vivo* endoscopic optical biopsy with optical coherence tomography. Science. 1997;276:2037–2039. [PubMed]

5. Schmitt JM. Array detection for speckle reduction in optical coherence microscopy. Phys Med Biol. 1997;42:1427–1439. [PubMed]

6. Yung KM, Lee SL, Schmitt JM. Phase-domain processing of optical coherence tomography images. J Biomed Opt. 1999;4:125–136. [PubMed]

7. Asakura T. International Trends in Optics and Photonics ICO IV. Springer-Verlag; 1999. pp. 359–389.

8. Bashkansky M, Reintjes J. Statistics and reduction of speckle in optical coherence tomography. Opt Lett. 2000;25:545–547. [PubMed]

9. Rogowska J, Brezinski ME. Evaluation of adaptive speckle suppression filter for coronary optical coherence tomography imaging. IEEE Trans Med Imaging. 2000;19:1261–1266. [PubMed]

10. Pircher M, Gotzinger E, Leitgeb R, Fercher AF, Hitzenberger CK. Speckle reduction in optical coherence tomography by frequency compounding. J Biomed Opt. 2003;8:565–569. [PubMed]

11. Leitgeb RA, Drexler W, Unterhuber A, Hermann B, Bajraszewski T, Le T, Stingl A, Fercher A. Ultrahigh resolution Fourier domain optical coherence tomography. Opt Express. 2004;12:2156–2165. [PubMed]

12. Adler DC, Ko TH, Fujimoto JG. Speckle reduction in optical coherence tomography images by use of a spatially adaptive wavelet filter. Opt Lett. 2004;29:2878–2880. [PubMed]

13. Marks DL, Ralston TS, Boppart SA. Speckle reduction by I-divergence regularization in optical coherence tomography. J Opt Soc Am A. 2005;22:2366–2371. [PubMed]

14. Desjardins AE, Vakoc BJ, Tearney GJ, Bouma BE. Speckle reduction in OCT using massively-parallel detection and frequency-domain ranging. Opt Express. 2006;14:4736–4745. [PMC free article] [PubMed]

15. Lee JS. Speckle analysis and smoothing of synthetic aperture radar images. Comput Graph Image Process. 1981;17:24–32.

16. Kuan DT, Sawchuk AA, Strand TC, Chavel P. Adaptive noise smoothing filter for images with signal-dependent noise. IEEE Trans Pattern Anal Mach Intell. 1985;7:165–177. [PubMed]

17. Lopes A, Touzi R, Nesby E. Adaptive speckle filter and scene heterogeneity. IEEE Trans Geosci Remote Sens. 1990;28:992–1000.

18. Starck JL, Murtagh F, Bijaoui A. Image Processing and Data Analysis: The Multiscale Approach. Cambridge U. Press; 1998.

19. Fraser SI, Allen AR. A speckle reduction algorithm using the à trous wavelet transform. Proceedings of the IASTED International Conference on Visualization, Imaging and Image Processing; ACTA; 2001. pp. 313–318.

20. Nieminen A, Heinonen P, Neuvo Y. A new class of detail-preserving filters for image-processing. IEEE Trans Pattern Anal Mach Intell. 1987;9:74–90. [PubMed]

21. Harwood D, Subbarao M, Hakalahti H, Davis L. A new class of edge-preserving smoothing filters. Pattern Recogn Lett. 1987;6:155–162.

22. Kuwahara M, Hachimura K, Eiho S, Kinoshita M. Digital Processing of Biomedical Images. Plenum; 1976. pp. 187–203.

23. Lim SJ. Two-Dimensional Signal and Image Processing. Prentice Hall; 1990.

24. Sauter D, Parson L. Spatial filtering for speckle reduction, contrast enhancement, and texture analysis of GLORIA images. IEEE J Ocean Eng. 1994;19:563–576.

25. Kofidis E, Theodoridis S, Kotropoulos C, Pitas I. Nonlinear adaptive filters for speckle suppression in ultrasonic images. Signal Process. 1996;52:357–372.

26. Zaitsev VV, Troshkin DV. Experimental study of speckle-noise filtering algorithms for radar images. Earth Observation and Remote Sensing. 1995;12:831–846.

27. Vassiliou AA, Bouluanne M, Blais JAR. On the application of averaging median filters in remote sensing. IEEE Trans Geosci Remote Sens. 1988;26:832–838.

28. Salo J, Neuvo Y, Hameenaho V. Improving TV picture quality with linear-median type operations. IEEE Trans Consum Electron. 1988;34:373–379.

29. Harauz G, Fonglochovsky A. Automatic selection of macromolecules from electron micrographs by component labeling and symbolic processing. Ultramicroscopy. 1989;31:333–344. [PubMed]

30. Kokaram AC, Persad N, Lasenby J, Fitzgerald WJ, McKinnan A, Welland M. Restoration of images from the scanning-tunneling microscope. Appl Opt. 1995;34:5121–5132. [PubMed]

31. Bohmig SD, Beilschmidt H, Reichl BM. Noise suppression in scanning Auger images—Comparison of various digital filters, Fresenius'. J Anal Chem. 1993;346:196–199.

32. Chandran V, Elgar S. Detection of sea mines in sonar imagery using higher-order spectral features. Proc SPIE. 1999;3710:578–587.

33. Wang XH, Istepanian RSH, Song YH. Microarray image enhancement by denoising using stationary wavelet transform. IEEE Trans Nanobiosci. 2003;2:184–189. [PubMed]

34. Wen J, Lu H, Li T, Liang Z. Analytical solution to 3D SPECT reconstruction with non-uniform attenuation, scatter, and spatially variant resolution variation for variable focal-length fan-beam collimators. Proc SPIE. 2003;5032:1858–1867.

35. Funama Y, Noguchi Y, Shimamura M. Reduction of artifacts in degraded CT image by adaptive Wiener filter. Jpn J Med Electron Biol Eng. 2002;40:1–6.

36. Wegner FV, Both M, Fink RHA. Automated detection of elementary calcium release events using the à trous wavelet transform. Biophys J. 2006;90:2151–2163. [PubMed]

37. Starck JL, Murtagh F. Automatic noise estimation from the multiresolution support. Publ Astron Soc Pac. 1998;110:193–199.

38. Stenborg G, Cobelli PJ. A wavelet packets equalization technique to reveal the multiple spatial-scale nature of coronal structures. Astron Astrophys. 2003;398:1185–1193.

39. Olivo-Marin JC. Extraction of spots in biological images using multiscale products. Pattern Recogn. 2002;35:1989–1996.

40. Muresan L, Heise B, Klement EP. Tracking fluorescent spots in wide-field microscopy images. Proc SPIE. 2006;6070:203–212.

41. Cornelis J, De Becker J, Bister M, Vanhove C, Demonceau G, Cornelis A. Techniques for cardiac image segmentation. Proceedings of the Annual International Conference of the IEEE Engineering in Medicine and Biology Society; IEEE; 1992. pp. 1906–1908.

42. Humphreys FJ, Bate PS, Hurley PJ. Orientation averaging of electron backscattered diffraction data. J Microsc. 2001;201:50–58. [PubMed]

43. Minato K, Tang YN, Bennett GW, Brill AB. Automatic contour detection using a fixed-point Hachimura–Kuwahara filter for SPECT attenuation correction. IEEE Trans Med Imaging. 1987;MI-6:126–133. [PubMed]

44. van Staalduinen M, van der Lubbe JCA, Backer E. Circular analysis-based line detection filters for watermark extraction in x-ray images of etchings. Proceedings of the Tenth Annual Conference of the Advanced School for Computing and Imaging; ASCI; 2004. pp. 305–310.

45. de Ridder D, Duin RPW, Verbeek PW, van Vliet LJ. The applicability of neural networks to non-linear image processing. Pattern Anal Appl. 1999;2:111–128.

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