Simplified PCNN Based MR Images Grayscale Inhomogeneity Real-Time Calibration


Magnetic resonance imaging is a powerful diagnostic technique which can provide high spatial resolution, slice selection at any orientation and excellent soft tissue contrast. However, automated quantitative analysis of MR images remains a difficult problem. One impediment to automated, quantitative MR image processing and analysis is the presence of low spatial frequency grayscale nonuniformities (Brinkmann et al., 1998). These inhomogeneities affect the measured gray level values so that pixels representing the same tissue class have different gray levels in different regions of the image. Without question, this increases the gray scale variances of the tissue classes and brings some difficulties for image segmentation and classification (Brinkmann et al., 1996).

Generally speaking, bias correction methods can be broadly categorized into two classes: prospective methods (Li et al., 2009; Wicks et al., 1993) and retrospective methods (Li et al., 2008; Pham and Prince, 1999a; Wells et al., 1996). The former can only correct some of the intensity inhomogeneity caused by MR scanner, however, they are no use for sources of inhomogeneity (Likar et al., 2001). The later can be applied to remove patient dependant effects. Moreover, segmentation-based methods that use fuzzy C-means clustering can be found by Pham and Prince (1999b), the usage of Markov random fields was considered by Rajapakse and Kruggel (1998). Other parameter optimization based methods were introduced by Guillemaud and Brady (1997), Wells et al. (1996). These methods can acquire a bias field at the cost of higher computation complexity and more time-consuming, this is very adverse for real-time image analysis. In this study, has proposed a novel MR image bias field estimation method based on simplified PCNN model, this method can obtain satisfied results, while avoiding the complex calculations at a fast rate.


The PCNN was originally presented by Eckhorn in order to explain the synchronous neuronal burst phenomena in the cat and other little mammals’ visual cortex (Eckhorn et al., 1990). With the development of PCNN research, it has been widely applied in the image-processing realm. The model neuron consists of three parts: dendritic tree receptive field, the linking modulation field and the pulse generator field. Now, the common PCNN model that was applied to image processing is an improved model by Lindblad and Kinser (1998) on the basis of Eckhorn proposed original model (Lindblad and Kinser, 1998).

Fig. 1: Simplified PCNN neuron model

In every computational iteration, this model parameters adjustment process is very inconvenient. So, in this study, we employ a simplified PCNN model, the single neuron model of simplified PCNN is shown as Fig. 1.

The mathematic expressions of this simplified PCNN system can be described as follows:






where, Fij, Iij, Lij, Uij, θij and Yij are the feeding input, external input stimulus (neuron corresponding pixel value), linking input, internal activity, dynamic threshold and output of the neuron ij, respectively; the linking coefficient wijkl among surrounding neurons is local gaussians; the constant β is the linking strength; αθ is decay coefficient; n represent iterations. In addition, neuron neighborhood size is 3×3, each neuron can fire and create pulse only once during a pulsing cycle in the simplified model.


The PCNN model has a strong biological background; it has many advantageous characteristics, which are similar to human vision. In the practical image processing, the neighboring neurons stimulate its neighboring neurons to be fired in succession and will yield a pulse wave propagating far away at activation areas. For image processing, those adjacent pixels with similar intensity will incline to synchronously fire.

Fig. 2: The flowchart of the proposed method

This is the reason that we select this model to estimate MR image bias field.

Our main method is to use Pulse synchronization theory to realize clustering of Gray Matter (GM) and White Matter (WM) and adjust parameters of PCNN model to yield a satisfied result as bias field of tested image. Here, using time signature G (n) to determine whether end PCNN’s iteration, we can obtain firing map corresponding to G (n) maximum as tested image’s bias field. G (n) is computed as:


The method main process is shown in Fig. 2.


Experiments for validating the correction method: Here, we tested the proposed correction method using two simulated MR T1-weighted images (Cocosco et al., 1997; Collins et al., 1998), one with 0% (normal image) and the other with 40% intensity non-uniformity. InFig. 3 the recovery of the gray distribution can be observed by comparing the histograms of normal, non-uniform and corrected image. The corresponding Statistic histogram of crest value correction shows in Fig. 4.

Evaluation criteria: In order to demonstrate the proposed method’s effectiveness, we must adopt some evaluation criteria to judge this method. Generally, the performance of a grayscale inhomogeneity correction method is commonly evaluated by comparing the coefficients of variations (CV) within the individual tissue classes in the original and corrected images. The CV which is invariant to the uniform multiplicative intensity transformation (Likar et al., 2001), is computed as follows:

Fig. 3: Simulated normal, non-uniform (40% intensity inhomogeneity), corrected, bias field images and the corresponding histograms

Fig. 4: Statistic histogram of crest value correction


where, σ (C) and μ (C) are the standard deviation and mean intensity of class C, respectively. To reflect more overlap information between the intensity distributions of distinct tissue classes. We adopt the coefficient of joint variations (CJV) to estimate correction results of the proposed method in this study:


Which is the sum of the standard deviations of two distinct classes; C1 and C2, the other parameters are same as the above. The CJV is invariant to the uniform linear and is more quantitative measure than the CV. The smaller of CJV index, the better of correction result.

Comparisons and analysis: To show the proposed method’s robustness and self-adaption, we select additional 3T brain MR image as a real testing image, the experimental result is illustrated in Fig. 5, the corresponding histogram distributions can be seen in Fig. 6.

Table 1: Correction of simulated and real data of the testing image. CJV (GM, WM) in [%]

Comparing with classical fuzzy C-means clustering correction method by Pham and Prince (1999b), so-called FCM method. Quantitative evaluation of the proposed method, FCM method was performed by computing the CJV (GM,WM) of the gray and white matters for all images from the two experimental images. Table 1 includes the results of non-uniformity correction of the images from the above two images.

In general, the clustering result of FCM method is better than other clustering method. But, from the above data, the proposed method outperformed the FCM method in this study and was also faster than the FCM and other methods.

Fig. 5: Real normal, non-uniform, corrected, bias field images and the corresponding histograms

Fig. 6: Statistic histogram of crest value correction

To a simulated MR T1-weighted image, the average processing time of the proposed method is about 0.6 sec and usual clustering method is about 1.5 sec on the same processing platform.


A novel simplified PCNN model based is proposed which is used to correct intensity inhomogeneities in MRI and the iterative firing map of PCNN model as bias field which is corresponding to the time signature G (n) maximum. This method is simply and also very effective, it needn’t acquire transcendental information of intensity non-uniform MR images and require no any assumptions and user interaction. The corrected results are very satisfied to simulated and real MR images at a fast rate, and I think this method is valuable tool in MR image analysis.


This study has been supported by the Postdoctoral Foundation of China (Grant No. 20100471665).

Brinkmann, B.H., A. Manduca and R.A. Robb, 1996. Quantitative analysis of statistical methods of grayscale inhomogeneity correction in magnetic resonance images. Proc. SPIE., 2710: 542-542.
CrossRef  |  Direct Link  | 

Brinkmann, B.H., A. Manduca and R.A. Robb, 1998. Optimized homomorphic unsharp masking for MR grayscale inhomogeneity correction. IEEE Trans. Med. Imaging, 17: 161-171.
CrossRef  | 

Cocosco, C.A., V. Kollokian, R.K.S. Kwan and A.C. Evans, 1997. BrainWeb: Online Interface to a 3D MRI Simulated Brain Database.

Collins, D.L., A.P. Zijdenbos, V. Kollokian, J.G. Sled, N.J. Kabani, C.J. Holmes and A.C. Evans, 1998. Design and construction of a realistic digital brain phantom. IEEE Trans. Med. Imaging, 17: 463-468.
CrossRef  |  PubMed  |  Direct Link  | 

Eckhorn, R., H.J. Reitboeck, M. Arndt and P. Dicke, 1990. Feature linking via synchronization among distributed assemblies: Simulations of results from cat visual cortex. Neural Comput., 2: 293-307.
CrossRef  |  Direct Link  | 

Guillemaud, R. and M. Brady, 1997. Estimating bias field of MR images. IEEE Trans. Med. Imaging, 16: 238-251.
CrossRef  | 

Li, C., C. Gatenby, L. Wang and J.C. Gore, 2009. A robust parametric method for bias field estimation and segmentation of MR images. Proceedings of the IEEE Conference on Computer Vision and Pattern Recognition, June 20-25, Miami, FL., pp: 218-223.

Li, C., R. Huang, Z. Ding, C. Gatenby, D. Metaxas and J. Gore, 2008. A variational level set approach to segmentation and bias correction of medical images with intensity ihhomogeneity. Proc. Med. Image Comput. Comput. Assisted Interven., 5242: 1083-1091.
CrossRef  |  Direct Link  | 

Likar, B., M. Viergever and F. Pernus, 2001. Retrospective correction of MR intensity inhomogeneity by information minimization. IEEE Trans. Med. Imaging, 20: 1398-1410.
CrossRef  |  Direct Link  | 

Lindblad, T. and J.M. Kinser, 1998. Image Processing using Pulse-coupled Neural Networks. Springer-Verlag, Berlin, Heidelberg.

Pham, D.L. and J.L. Prince, 1999. Adaptive fuzzy segmentation of magnetic resonance images. IEEE. Trans. Med. Imaging, 18: 737-752.
CrossRef  |  Direct Link  | 

Pham, D.L. and J.L. Prince, 1999. An adaptive fuzzy C-means algorithm for image segmentation in the presence of intensity inhomogeneities. Pattern Recog. Lett., 20: 57-68.
CrossRef  | 

Rajapakse, J.C. and F. Kruggel, 1998. Segmentation of MR images with intensity inhomogeneities. Image Vision Comput., 16: 165-180.
CrossRef  | 

Wells, W.M., W.E.L. Grimson, R. Kikinis and F.A. Jolesz, 1996. Adaptive segmentation of MRI data. IEEE Trans. Med. Imaging, 15: 429-442.
CrossRef  |  PubMed  |  Direct Link  | 

Wicks, D.A., G.J. Barker and P.S. Tofts, 1993. Correction of intensity nonuniformity in MR images of any orentation. Magn. Reson. Imaging, 11: 183-196.
PubMed  |  Direct Link  | 

作者:Changtao He, Fangnian Lang, Hongliang Li and Haixu Wang


About 智足者富


电子邮件地址不会被公开。 必填项已用*标注

You may use these HTML tags and attributes:

<a href="" title=""> <abbr title=""> <acronym title=""> <b> <blockquote cite=""> <cite> <code> <del datetime=""> <em> <i> <q cite=""> <s> <strike> <strong>