About this Journal Submit a Manuscript Table of Contents
BioMed Research International
Volume 2014 (2014), Article ID 421743, 8 pages
Research Article

Automated Identification of Dementia Using FDG-PET Imaging

1Shaanxi Provincial Key Lab of Speech & Image Information Processing (SAIIP), School of Computer Science, Northwestern Polytechnical University, Xi’an 710072, China
2Biomedical and Multimedia Information Technology (BMIT) Research Group, School of Information Technologies, The University of Sydney, Sydney, NSW 2006, Australia
3Department of Molecular Imaging, Royal Prince Alfred Hospital, Sydney, NSW 2050, Australia
4Sydney Medical School, The University of Sydney, Sydney, NSW 2006, Australia
5Med-X Research Institute, Shanghai Jiao Tong University, Shanghai 200030, China

Received 30 April 2013; Revised 1 October 2013; Accepted 17 November 2013; Published 2 February 2014

Academic Editor: Annalena Venneri

Copyright © 2014 Yong Xia et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.


Parametric FDG-PET images offer the potential for automated identification of the different dementia syndromes. However, various existing image features and classifiers have their limitations in characterizing and differentiating the patterns of this disease. We reported a hybrid feature extraction, selection, and classification approach, namely, the GA-MKL algorithm, for separating patients with suspected Alzheimer’s disease and frontotemporal dementia from normal controls. In this approach, we extracted three groups of features to describe the average level, spatial variation, and asymmetry of glucose metabolic rates in 116 cortical volumes. An optimal combination of features, that is, capable of classifying dementia cases was identified by a genetic algorithm- (GA-) based method. The condition of each FDG-PET study was predicted by applying the selected features to a multikernel learning (MKL) machine, in which the weighting parameter of each kernel function can be automatically estimated. We compared our approach to two state-of-the-art dementia identification algorithms on a set of 129 clinical cases and improved the performance in separating the dementia types, achieving accuracy of 94.62%. There is a very good agreement between the proposed automated technique and the diagnosis made by clinicians.

1. Introduction

Dementia is a chronic and progressive brain disorder, that is, characterized by the progressive loss of memory and cognitive impairment with an attendant disruption of normal daily activities [1]. In 2010, it was estimated that 35.6 million people worldwide were suffering from dementia and it is predicted that this number will double every 20 years [2]. Dementia is now a global health and social problem [3]. The common types of dementia include Alzheimer’s disease (AD), vascular dementia (VD), Lewy body dementia (LBD), and frontotemporal dementia (FTD). AD accounts for about 65% of the cases [4]. FTD is the second most common and accounts for between 4% and 20% of all dementia cases in memory disorders clinics [5]. Once dementia is clinically apparent, the pathological changes are irreversible; hence, it is critical that, for therapies to be affective, the underlying dementia must be accurately diagnosed at an early stage. Cognitive tests, including the mini-mental state examination (MMSE) [6], provide an assessment of overall cognitive functioning but cannot discriminate between the different dementias.

The molecular medical imaging technique of positron emission tomography (PET) and anatomical imaging from magnetic resonance (MR) imaging are able to detect focal hypometabolism (PET) and atrophy (MR), which are characteristics of neurodegenerative disorders [710]. These imaging techniques are dependent upon the skill and experience of the reader and interpretation can be time-consuming and prone to operator bias. A computer-aided automated dementia classification, thus, would provide a useful “second opinion.” Automated dementia classification, however, is a challenging task, especially early in the course of the illness [11]. A feasible automated approach would be based on learning the statistical models of each dementia from a set of training samples, where each training sample is associated with a class label. Pattern detection techniques used in such a system then shift from visual inspection by an expert to image-based feature extraction and selection. Patterns that have been considered include global features, computed from the entire brain volume, and local features such as statistics, histograms, and gradients calculated from volumes of interest (ROIs) [1214]. Advanced pattern classification techniques, including the K-means clustering [15], artificial neural network [9, 10], and support vector machine (SVM) [11, 12], have also been applied. Davatzikos et al. [16] used the multiscaled principal component analysis (PCA) to extract image features in T1-weighted MR images and applied those features to a nonlinear SVM to generate a real-valued score for each MR study to differentiate AD and FTD from normal controls (NCs). Hinrichs et al. [17] separated AD from patients with mild cognitive impairment (MCI) and NCs by applying features extracted from MR and PET images to the multikernel learning (MKL) machine. Zhang et al. [18] extended this work to a grid-search process to generate the optimal kernel weights for the MKL machine and improved the dementia classification.

Our aim was to develop an automated approach to classify AD, FTD, and NCs using a generic computer-aided system to analyze 18-fluorodeoxyglucose (18F-FDG) PET images. In our previous work, we used global and local features from parametric FDG-PET images to identify the different dementias [19]. The global features were obtained by applying the entire gray matter volume to the linear transformation derived from the PCA [20]. Local features were defined as the statistics of voxel values in anatomical volumes of interests (VOIs) and we adopted the AdaBoost technique to adaptively combine those feature groups [21]. In this paper, we propose the GA-MKL algorithm, which is a hybrid feature extraction, selection, and classification approach, for the automated identification of AD, FTD, and NCs using parametric FDG-PET. Based on the observation that the volume loss and reduced glucose metabolism in FTD are mainly seen in the frontal and temporal lobes and the AD changes are usually located more posteriorly in the parietotemporal cortices, our approach extracted three groups of local features in 116 anatomical VOIs characterizing the average glucose metabolism rate in each VOI, the variation of metabolic rates in each VOI, and the asymmetry of metabolic rates in left-right VOI pairs. We selected a subset of the most effective features from each group to reduce the redundancy in these groups and formulated the feature selection task as an optimization problem and solved it using the genetic algorithm (GA), which has the ability to search the global optimum. To identify each clinical condition, we applied three groups of selected features to the MKL machine, in which the weighting parameter of each kernel was automatically estimated. We compared our GA-MKL algorithm to two state-of-the-art dementia classification methods on 129 clinical studies.

2. Materials and Methods

2.1. Data Acquisition

We used 129 clinical brain FDG PET studies with a clinical diagnosis of AD in 46 and FTD in 43 and there were 40 NCs. All studies were acquired on an ECAT 951/R whole body PET scanner (Siemens/CTI, Knoxville, TN, USA) in the Department of Molecular Imaging at the Royal Prince Alfred Hospital (Sydney, Australia) between 1998 and 2007. Approximately 400 MBq of 18F-FDG was infused at a constant rate over a 3-minute period. Two arterialised-venous blood samples were taken at 10 minutes and 45 minutes after injection to calibrate the population-based input function using a method published previously [22]. PET scanning commenced at least 30 minutes after tracer injection with scan duration of 20 minutes. Each FDG-PET data volume had a dimension of 128 × 128 × 31 and a voxel size of 1.84 × 1.84 × 3.38 mm3. The autoradiographic method [23] was used to calculate parametric images of cerebral metabolic rate of glucose consumption (CMRGlc).

2.2. Spatial Normalization

To differentiate cortical gray matter from white matter, we used the automated anatomical labeling (AAL) cortical parcellation map [24], which was built by applying a set of anatomical parcellation rules to the spatially normalized single subject high resolution T1 volume provided by the Montreal Neurological Institute (MNI) [25]. It consisted of 116 anatomical VOIs, including 54 left-right pairs. The transverse, coronal, and sagittal views of the AAL cortical parcellation map are displayed in Figure 1. In these images, different gray levels indicate different anatomical volumes. A full list of all anatomical VOIs can be found in the AAL package [24].

Figure 1: Transverse (a), coronal (b), and sagittal (c) views of the AAL cortical parcellation map.

The AAL cortical parcellation map is well aligned with the template brain PET image supplied with the statistical parametric mapping (SPM, Version 8) package (Wellcome Trust Centre for Neuroimaging, London, UK) [26], which conforms to the space defined by the international consortium for brain mapping (ICBM) and approximates to the space described in the atlas of Talairach and Tournoux [27]. To map the anatomical labels from the atlas onto each study, we spatially normalized each reconstructed CMRGlc image to the SPM brain PET template using the spatial normalization procedure supplied with the SPM package. Each spatially normalized CMRGlc image had a dimension of 91 × 109 × 91 and a voxel size of 2 × 2 × 2 mm3.

2.3. Feature Extraction

After the spatial normalization, each CMRGlc image and the AAL cortical parcellation map lie in the same coordinate system. Consequently, 116 anatomical VOIs can be identified on each study by using the corresponding voxel labels in the AAL cortical parcellation map. For each study , we used the mean and standard deviation of voxel values in each anatomical VOI in the spatially normalized CMRGlc image as two groups of image features, denoted by and . Metabolic asymmetry is also prominent in the dementia syndromes; hence, we used the difference between the mean voxel values of each of 54 left-right VOI pairs as the third group of features, denoted by . As a result, for the th brain PET study, we extracted three groups of image features, 286 features in total, denoted by . These three groups of features characterized the average cerebral metabolic rate and the spatial variation of cerebral metabolic rates in each VOI and the asymmetry in glucose metabolism between the left and right brain hemispheres. Since the image features could have a variable dynamic range over all studies, each of the 286 features was normalized by subtracting the sample mean and dividing by the sample standard deviation before applying subsequent processing.

2.4. Feature Selection

Although 116 anatomical VOIs were used in feature extraction, not every VOI was equally important for dementia classification. So we removed those features that contributed little to the classification. Feature selection was performed on a group-by-group basis. Let the th group of features extracted from brain PET studies be denoted by , where and is the number of features in this group. Let be a -dimensional binary vector, where 1 means that the corresponding feature is selected and 0 means that the feature is discarded. Each binary vector acts as a mask to “filter” all features to preserve the selected ones. The subset of selected features can be denoted by . Our aim was to identify a subset of features that produce the most accurate classification of all studies. Let the accuracy of classifying the data set with the classifier be formally represented as ; the feature selection can be formulated into the following optimization problem:

Due to the relatively large number of features, it is not feasible to solve this combinatorial optimization by attempting every possible combination of features. Thus, we used the binary-coded GA (bGA) to find a satisfactory feature subset [28]. The GA is a heuristic-guided parallel and stochastic search strategy, searching through an evolving population of individuals. The bGA-based optimization started with a population of 500 randomly initialized binary individuals, each representing a candidate solution and having the fitness value . Since the number of studies was relatively small and the number of features is large, SVM with a linear kernel function was adopted as the classifier [29]. To efficiently use all available studies, the 10-fold cross validation scheme was performed. All PET studies were randomly partitioned into 10 equal size subsamples. Of the 10 subsamples, a single subsample was retained as the validation data for testing the classifier, and the remaining 9 subsamples were used as training data. The cross-validation process was then repeated 10 times, with each of the 10 subsamples used once as the validation data. The fitness of the individual that represented the solution was then defined as the average classification error achieved in the 10-fold cross validation when the selected features were used.

During the evolutionary optimization process, each new generation was created by using several genetic operators, including the best solution inheritance, roulette wheel selection, one-point crossover, random mutation, and gene modification. Since the classifier prefers lower dimensionality of the feature space, gene modification is designed to produce new solutions by modifying the current optimal solution by discarding 1 to 3 selected features which make the least contribution to the fitness. To avoid the optimization process being trapped in a local maximum, we used a variable mutation probability, given as follows: where was the increasing rate of mutation probability and and are the mutation probability and the highest fitness of the th generation. When the mutation probability reaches its threshold , it will be reset to its initial value to prevent the bGA from degenerating to random searching. Another operator is triggered when the evolution has been halted for more than 4 generations. In this case, all individuals whose fitness equals the highest fitness will be replaced by their offspring produced by mutating. This operator aims to diversify genes in the population and thus speed up the evolution. Finally, the evolution terminates when the predetermined number of generations is reached. In the final population, let the individual with the highest fitness be denoted by . The optimal subset of features we selected is and the overall selected feature set is denoted by .

2.5. MKL-Based Classification

Based on the selected features, the classification of FDG-PET studies was obtained by using a MKL machine, which is a linear combination of soft-margin SVMs with multiple linear and nonlinear kernels [30, 31]. The prototype soft margin SVM is defined as the following minimization problem: where is the slack variable for each data sample , is the vector orthogonal to the decision hyperplane, is the target value for feature vector , and is the number of training cases. The dual optimization problem of (3) derived using the Lagranian technique is where is the Lagranian multiplier. Generally, the inner product can be denoted by a linear kernel function . In this study, we employed the linear, second-order polynomial and Gaussian kernel functions to handle three groups of selected features. Thus, the objective function in (4) can be rewritten as where is the weighting parameter for the th feature group and three kernel functions are as follows: Different from traditional MKL approaches [17, 18], the optimal weight vector in our approach was automatically estimated by the real-coded GA with the procedures similar to those used in feature selection. The Lagranian multiplier was obtained by using the traditional SVM technique. For each test case , we first calculated the vote for each possible class label () using the trained MKL: The test case was grouped into the class that had the maximum accumulated votes.

2.6. Summary

The scheme of the proposed GA-MKL dementia classification algorithm is illustrated in Figure 2.

Figure 2: Scheme of the proposed GA-MKL dementia classification algorithm.
2.7. Evaluation

We compared our GA-MKL algorithm to the methods reported by Zhang et al. [18] and Xia et al. [21], which employ the GA-based feature selection and MKL-based classification, respectively. We adopted a 10-fold cross validation scheme to ensure a comprehensive comparison. In each experiment, 90% of studies were used to train the feature selection and classification system and the other 10% of studies were left for testing. In this way, it was guaranteed that test data were used to train the algorithm. After the experiment was repeated 10 times, each study was then tested once. The performance of each approach was evaluated for overall classification accuracy, which was calculated as the percentage of correctly classified studies. Similar experiments were performed to differentiate studies from each pair, including AD versus NCs, FTD versus NCs, and AD versus FTD. For each pair, the performance of each algorithm was measured by accuracy, sensitivity (true positive rate), and specificity (true negative rate), which were defined as follows:

3. Results and Discussion

Table 1 lists the accuracy of the three algorithms. It shows that the proposed GA-MKL algorithm achieves an identification accuracy of 94.62%, substantially higher than the accuracy achieved by other two algorithms.

Table 1: Accuracy of three dementia identification algorithms on 129 FDG-PET studies.

In Table 2, the sensitivity, specificity, and accuracy for the pairs of conditions are recorded. Our GA-MKL algorithm showed the best results, in particular, when separating FTD from NCs. However, in the differentiation of AD from FTD, our algorithm had slightly lower specificity when compared to Zhang et al. [18], but it still produced the highest sensitivity and accuracy across the three algorithms.

Table 2: Performance of the algorithm in binary comparisons.

All algorithms have difficulty in separating AD from FTD and this problem is also recognized in clinical practice [32]. We applied the paired -test to these image features to explicitly display this problem. The percentage of data in each group rejecting the hypothesis that those data are drawn from the normal distribution with an identical mean and variance is shown in Table 3. We found that the majority of data rejected the identical distribution hypothesis when mixing dementia cases with normal controls, whereas only 43.7% data rejected this hypothesis when AD and FTD cases were grouped together. These results show that the features extracted and selected by our algorithm are more capable of separating AD or FTD cases from normal controls but less capable of differentiating AD from FTD. Image features that can more effectively characterize the asymmetric hypometabolism in FTD will be further investigated in our future work.

Table 3: Percentage of data in each group rejecting the hypothesis in paired -test.

In our GA-MKL algorithm, image features were extracted in all anatomical VOIs defined by the AAL cortical parcellation map [24], without evaluating the relevance between each VOI and the dementia type. Hence, feature selection plays a pivotal role in improving the performance of dementia classification. We formulated this task as a maximization problem in (1) and solved it using the GA. The optimal subset of features can be determined in alternative ways. For example, as a classical statistical hypothesis test method, -test has been adopted to select features in the form of bagged -test [33] and modified -statistics [34] in research areas such as genotype data classification [35] and hippocampal shape features discrimination [36]. In our work, we also attempted to select features based on the -test in an iterative manner such as the forward/backward search [37]. Table 4 gives the classification accuracy when features are not selected or selected by using the -test method or the proposed GA. Our results show that, if all features are used or the features selected by -test, our algorithm has much lower accuracy. This is mainly because the features with less discriminatory power do not contribute to the classification and decrease the performance of a classifier, since they increase the dimensionality of the feature space. It also explains why dimensionality reduction always plays a pivotal role in high-dimensional pattern classification. In the meantime, the -test-based feature selection method ignores the interrelationship among multiple features. Nevertheless, it is widely recognized that a feature considered to be useless in itself may help improve the overall separability of the sample data if it is combined with other features [38].

Table 4: Accuracy of our algorithm with different feature selection methods.

We chose the MKL machine to classify the FDG-PET studies. Lanckriet et al. [31] reported that MKL is a semidefinite programming mechanism, which is bonded to SVM naturally and is suitable for handling data from heterogeneous data sources. The selection of the kernel function for each feature group is also critical to our algorithm. In our experiments, 62 out of 116 features were selected in the first group, 58 out of 116 in the second group, and 23 out of 54 in the third group. The advantage of SVM is that low-dimensional features can be converted into high-dimensional space, in which data samples may have improved separability, by using nonlinear kernel functions. Thus, we applied the linear and second-order polynomial kernel functions to the first and second groups of features, which have higher dimensionality, and applied the nonlinear Gaussian kernel to the third group of features. We swapped the three kernel functions and the accuracy is listed in Table 5. It shows that the settings that we used achieved the best results.

Table 5: Accuracy of our algorithms when different kernel functions were used.

It should be noted that we used the clinical diagnosis as gold standard classification for each PET study. It is accepted that the clinical diagnosis can be problematic and a definitive diagnosis can only be made with pathological confirmation after death. The patients in our cohort were all assessed by experienced neurologists/geriatricians in a dementia clinic setting and cases without a diagnosis of probable AD or FTD were excluded. Hence, a relatively accurate classification rate was achieved by all algorithms. However, it would be expected that all the algorithms would perform poorly if atypical studies were included in training and testing. So we also selected 12 AD, 11 FTD, and 11 normal cases, which were described by doctors as “atypical,” and added them to the dataset. The performance of three algorithms on these 163 studies is shown in Table 6. All algorithms have poorer accuracy but our GA-MKL algorithm was still the most accurate.

Table 6: Accuracy of the three algorithms on the larger dataset ().

4. Conclusion

We have proposed a novel dementia classification algorithm, namely, the GA-MKL algorithm, which extracts three groups of features, selects a subset of features from each group using the GA, and classifies the selected features using the MKL machine with automatically estimated weighting parameters. Our results show that the GA-MKL algorithm produces improved sensitivity, specificity, and accuracy when compared to two other state-of-the-art approaches. We chose FDG-PET images to test our algorithm, but we suggest that our algorithm is generic and can be applied to other scanning techniques such as amyloid imaging scans using the Pittsburgh compound B (PiB) [39]. In future work, we will apply our methodology to these newer PET ligands.

Conflict of Interests

The authors declare that there is no conflict of interests regarding the publication of this paper.


This work was supported by the Australian Research Council grants.


  1. American Psychiatric Association, Diagnostic and Statistical Manual of Mental Disorders, American Psychiatric Association, Washington, DC, USA, 4th edition, 1994.
  2. International AsD, World Alzheimer Report 2009 Executive Summary, 2009.
  3. R. Brookmeyer, E. Johnson, K. Ziegler-Graham, and H. M. Arrighi, “Forecasting the global burden of Alzheimer's disease,” Alzheimer's and Dementia, vol. 3, no. 3, pp. 186–191, 2007. View at Publisher · View at Google Scholar · View at Scopus
  4. M. D. Devous Sr., “Functional brain imaging in the dementias: role in early detection, differential diagnosis, and longitudinal studies,” European Journal of Nuclear Medicine, vol. 29, no. 12, pp. 1685–1696, 2002. View at Publisher · View at Google Scholar · View at Scopus
  5. M. Sjögren and C. Andersen, “Frontotemporal dementia—a brief review,” Mechanisms of Ageing and Development, vol. 127, no. 2, pp. 180–187, 2006. View at Publisher · View at Google Scholar · View at Scopus
  6. M. F. Folstein, S. E. Folstein, and P. R. McHugh, “‘Mini mental state’. A practical method for grading the cognitive state of patients for the clinician,” Journal of Psychiatric Research, vol. 12, no. 3, pp. 189–198, 1975. View at Publisher · View at Google Scholar · View at Scopus
  7. D. Chan, N. C. Fox, R. Jenkins, R. I. Scahill, W. R. Crum, and M. N. Rossor, “Rates of global and regional cerebral atrophy in AD and frontotemporal dementia,” Neurology, vol. 57, no. 10, pp. 1756–1763, 2001. View at Scopus
  8. N. C. Fox and J. M. Schott, “Imaging cerebral atrophy: normal ageing to Alzheimer's disease,” Lancet, vol. 363, no. 9406, pp. 392–394, 2004. View at Publisher · View at Google Scholar · View at Scopus
  9. S. M. Resnick, D. L. Pham, M. A. Kraut, A. B. Zonderman, and C. Davatzikos, “Longitudinal magnetic resonance imaging studies of older adults: a shrinking brain,” Journal of Neuroscience, vol. 23, no. 8, pp. 3295–3301, 2003. View at Scopus
  10. M. Grossman, C. McMillan, P. Moore et al., “What's in a name: voxel-based morphometric analyses of MRI and naming difficulty in Alzheimer's disease, frontotemporal dementia and corticobasal degeneration,” Brain, vol. 127, no. 3, pp. 628–649, 2004. View at Publisher · View at Google Scholar · View at Scopus
  11. H. Adeli, S. Ghosh-Dastidar, and N. Dadmehr, “Alzheimer's disease and models of computation: imaging, classification, and neural models,” Journal of Alzheimer's Disease, vol. 7, no. 3, pp. 187–199, 2005. View at Scopus
  12. C. Hinrichs, V. Singh, G. Xu, and S. C. Johnson, “Predictive markers for AD in a multi-modality framework: an analysis of MCI progression in the ADNI population,” NeuroImage, vol. 55, no. 2, pp. 574–589, 2011. View at Publisher · View at Google Scholar · View at Scopus
  13. A. Caroli, A. Prestia, K. Chen et al., “Summary metrics to assess Alzheimer disease-related hypometabolic pattern with18F-FDG PET: head-to-head comparison,” Journal of Nuclear Medicine, vol. 53, no. 4, pp. 592–600, 2012. View at Publisher · View at Google Scholar · View at Scopus
  14. R. Higdon, N. L. Foster, R. A. Koeppe et al., “A comparison of classification methods for differentiating fronto-temporal dementia from Alzheimer's disease using FDG-PET imaging,” Statistics in Medicine, vol. 23, no. 2, pp. 315–326, 2004. View at Publisher · View at Google Scholar · View at Scopus
  15. M. Pagani, V. A. Kovalev, R. Lundqvist, H. Jacobsson, S. A. Larsson, and L. Thurfjell, “A new approach for improving diagnostic accuracy in Alzheimer's disease and frontal lobe dementia utilising the intrinsic properties of the SPET dataset,” European Journal of Nuclear Medicine and Molecular Imaging, vol. 30, no. 11, pp. 1481–1488, 2003. View at Publisher · View at Google Scholar · View at Scopus
  16. C. Davatzikos, S. M. Resnick, X. Wu, P. Parmpi, and C. M. Clark, “Individual patient diagnosis of AD and FTD via high-dimensional pattern classification of MRI,” NeuroImage, vol. 41, no. 4, pp. 1220–1227, 2008. View at Publisher · View at Google Scholar · View at Scopus
  17. C. Hinrichs, V. Singh, G. Xu, et al., “MKL for robust Multi-modality AD Classification,” in Proceedings of the International Conference on Medical Image Computing and Computer-Assisted Intervention (MICCAI '09), vol. 5762, pp. 786–794, 2009.
  18. D. Zhang, Y. Wang, L. Zhou, H. Yuan, and D. Shen, “Multimodal classification of Alzheimer's disease and mild cognitive impairment,” NeuroImage, vol. 55, no. 3, pp. 856–867, 2011. View at Publisher · View at Google Scholar · View at Scopus
  19. L. Wen, M. Bewley, S. Eberl, M. Fulham, and D. Feng, “Classification of dementia from FDG-PET parametric images using data mining,” in Proceedings of the 5th IEEE International Symposium on Biomedical Imaging: From Nano to Macro (ISBI '08), pp. 412–415, May 2008. View at Publisher · View at Google Scholar · View at Scopus
  20. Y. Xia, L. Wen, S. Eberl, M. Fulham, and D. Feng, “Genetic algorithm-based PCA eigenvector selection and weighting for automated identification of dementia using FDG-PET imaging,” Proceedings of the Annual International Conference of the IEEE Engineering in Medicine and Biology Society, vol. 2008, pp. 4812–4815, 2008. View at Scopus
  21. Y. Xia, Z. Zhang, L. Wen, et al., “GA and AdaBoost-based feature selection and combination for automated identification of dementia using FDG-PET imaging,” in Intelligent Science and Intelligent Data Engineering, Y. Zhang, Z. H. Zhou, C. Zhang, and Y. Li, Eds., pp. 128–135, Springer, Berlin, Germany, 2012.
  22. S. Eberl, A. R. Anayat, R. R. Fulton, P. K. Hooper, and M. J. Fulham, “Evaluation of two population-based input functions for quantitative neurological FDG PET studies,” European Journal of Nuclear Medicine, vol. 24, no. 3, pp. 299–304, 1997. View at Publisher · View at Google Scholar · View at Scopus
  23. G. D. Hutchins, J. E. Holden, and R. A. Koeppe, “Alternative approach to single-scan estimation of cerebral glucose metabolic rate using glucose analogs, with particular application to ischemia,” Journal of Cerebral Blood Flow and Metabolism, vol. 4, no. 1, pp. 35–40, 1984. View at Scopus
  24. N. Tzourio-Mazoyer, B. Landeau, D. Papathanassiou et al., “Automated anatomical labeling of activations in SPM using a macroscopic anatomical parcellation of the MNI MRI single-subject brain,” NeuroImage, vol. 15, no. 1, pp. 273–289, 2002. View at Publisher · View at Google Scholar · View at Scopus
  25. D. L. Collins, A. P. Zijdenbos, V. Kollokian et al., “Design and construction of a realistic digital brain phantom,” IEEE Transactions on Medical Imaging, vol. 17, no. 3, pp. 463–468, 1998. View at Scopus
  26. R. S. J. Frackowiak, J. T. Ashburner, W. D. Penny, et al., Human Brain Function, Elsevier Academic Press, Amsterdam, The Netherlands, 2004.
  27. J. Talairach and P. Tournoux, Co-Planar Stereotaxic Atlas of the Human Brain, vol. 122, Thieme, New York, NY, USA, 1988.
  28. Y. Xia, L. Wen, S. Eberl, M. Fulham, and D. Feng, “Genetic algorithm-based PCA eigenvector selection and weighting for automated identification of dementia using FDG-PET imaging,” in Proceedings of the 30th Annual International Conference of the IEEE Engineering in Medicine and Biology Society (EMBS '08), pp. 4812–4815, August 2008. View at Scopus
  29. C. Chang and C. Lin, “LIBSVM: a Library for support vector machines,” ACM Transactions on Intelligent Systems and Technology, vol. 2, no. 3, article 27, 2011. View at Publisher · View at Google Scholar · View at Scopus
  30. B. Schölkopf and A. J. Smola, “Learning with kernels: support vector machines, regularization, optimization, and beyond,” in Adaptive Computation and Machine Learning, vol. 18, pp. 1–626, MIT Press, Cambridge, Mass, USA, 2002.
  31. G. R. G. Lanckriet, N. Cristianini, P. Bartlett, L. El Ghaoui, and M. I. Jordan, “Learning the kernel matrix with semidefinite programming,” Journal of Machine Learning Research, vol. 5, pp. 27–72, 2004. View at Scopus
  32. D. S. Knopman, S. T. DeKosky, J. L. Cummings et al., “Practice parameter: diagnosis of dementia (an evidence-based review): report of the quality standards subcommittee of the american academy of neurology,” Neurology, vol. 56, no. 9, pp. 1143–1153, 2001. View at Scopus
  33. L. Breiman, “Bagging predictors,” Machine Learning, vol. 24, no. 2, pp. 123–140, 1996. View at Scopus
  34. V. N. Vapnik, Statitical Learning Theory, John Wiley & Sons, New York, NY, USA, 1998.
  35. N. Zhou and L. Wang, “A modified T-test feature selection method and its application on the HapMap genotype data,” Genomics, Proteomics and Bioinformatics, vol. 5, no. 3-4, pp. 242–249, 2007. View at Publisher · View at Google Scholar · View at Scopus
  36. E. Gerardin, G. Chételat, M. Chupin et al., “Multidimensional classification of hippocampal shape features discriminates Alzheimer's disease and mild cognitive impairment from normal aging,” NeuroImage, vol. 47, no. 4, pp. 1476–1486, 2009. View at Publisher · View at Google Scholar · View at Scopus
  37. S. Theodoridis and K. Koutroumbas, Pattern Recognition, Elsevier, Singapore, 4th edition, 2009.
  38. I. Guyon and A. Elisseeff, “An introduction to variable and feature selection,” Journal of Machine Learning Research, vol. 3, pp. 1157–1182, 2003.
  39. W. E. Klunk, H. Engler, A. Nordberg et al., “Imaging brain amyloid in Alzheimer's disease with Pittsburgh compound-B,” Annals of Neurology, vol. 55, no. 3, pp. 306–319, 2004. View at Publisher · View at Google Scholar · View at Scopus