Computers, Materials & Continua

A Feature Selection Strategy to Optimize Retinal Vasculature Segmentation

José Escorcia-Gutierrez1,4,*, Jordina Torrents-Barrena4, Margarita Gamarra2, Natasha Madera1, Pedro Romero-Aroca3, Aida Valls4 and Domenec Puig4

1Electronic and Telecommunications Engineering Program, Universidad Autónoma del Caribe, Barranquilla, 080001, Colombia
2Department of Computational Science and Electronic, Universidad de la Costa, CUC, Barranquilla, 080001, Colombia
3Ophthalmology Service, Universitari Hospital Sant Joan, Institut de Investigacio Sanitaria Pere Virgili, Reus, 43201, Spain
4Departament d’Enginyeria Informàtica i Matemàtiques, Escola Tècnica Superior d’Enginyeria, Universitat Rovira i Virgili, Tarragona, 43007, Spain
*Corresponding Author: José Escorcia-Gutierrez. Email: jose.escorcia23@gmail.com
Received: 08 May 2021; Accepted: 24 June 2021

Abstract: Diabetic retinopathy (DR) is a complication of diabetes mellitus that appears in the retina. Clinitians use retina images to detect DR pathological signs related to the occlusion of tiny blood vessels. Such occlusion brings a degenerative cycle between the breaking off and the new generation of thinner and weaker blood vessels. This research aims to develop a suitable retinal vasculature segmentation method for improving retinal screening procedures by means of computer-aided diagnosis systems. The blood vessel segmentation methodology relies on an effective feature selection based on Sequential Forward Selection, using the error rate of a decision tree classifier in the evaluation function. Subsequently, the classification process is performed by three alternative approaches: artificial neural networks, decision trees and support vector machines. The proposed methodology is validated on three publicly accessible datasets and a private one provided by Hospital Sant Joan of Reus. In all cases we obtain an average accuracy above 96% with a sensitivity of 72% in the blood vessel segmentation process. Compared with the state-of-the-art, our approach achieves the same performance as other methods that need more computational power. Our method significantly reduces the number of features used in the segmentation process from 20 to 5 dimensions. The implementation of the three classifiers confirmed that the five selected features have a good effectiveness, independently of the classification algorithm.

Keywords: Diabetic retinopathy; artificial neural networks; decision trees; support vector machines; feature selection; retinal vasculature segmentation

1  Introduction

Diabetes Mellitus is a chronic disease. People who suffer diabetes have high blood sugar levels, either due to insufficient insulin in the body or cells’ resistance to this hormone [1]. Diabetes can bring several complications because of the difficulty of maintaining blood pressure at normal levels. Some of the consequences are the increase of cholesterol levels, kidney failure, affectations in the nervous system, or even absolute blindness due to damage to the retinal vessels [2,3].

Diabetic Retinopathy (DR) occurs because a high blood sugar levels damages the retinal vessels [4]. DR causes lesions on the surface of the retina (i.e., microaneurysms, hemorrhages, and exudates). The microaneurysms are pathological signs that appear in the early phase of the disease. They are capillary dilatations produced by the local weakening of the vessels walls [5]. The injuries that appear after microaneurysms are caused by their explosion, known as hemorrhages. Moreover, vessels may start filtering lipids and proteins in addition to blood leakage, causing the appearance of bright spots, which are yellowish and white patches of different sizes, shapes, and locations (i.e., white exudates). In later stages, the yellow-white plasma begins to leak from the blood capillaries, generating hard exudates [6,7].

Blood vessels are responsible for transmitting signals between the retina and the brain [8,9]. Blood vessel features (i.e., length and width variations, tortuosity, and branching pattern) help to identify and diagnose many disorders (e.g., DR, hypertensive retinopathy, retinal artery occlusion) [7]. It is a widely user practice to examine eye fundus images to make diagnosis from the inspection of blood vessels. However, manual segmentation of retinal vessels is time-consuming and can rapidly cause visual fatigue. For assisting ophthalmologists with this complicated and tedious work, there is a demand of rapid and automated methods to analyze this kind of color eye fundus images [10].

There are several computer vision methods to segment blood vessels automatically. These techniques are divided into different categories such as: pattern recognition, supervised and unsupervised machine learning, mathematical morphology, model tracking, adaptive filtering, and multiscalar approaches [11]. However, there is still a place for improving the accuracy of the current methods. A crucial point to achieve the best image processing tool is the extraction of the best susbset of features from the input image, because many features increase the computational time but not the quality of the results. This paper presents an automatic and efficient segmentation method for blood vessels from eye fundus images. The main contribution of this paper is a method for finding the smallest subset of features to obtain the best results in the segmentation task.

This paper is organized as follows. In Section 2 we expose the contributions of this research. The related work is reviewed in Section 3. Section 4 describes the proposed approach widely. Section 5 presents the used datasets and performance measures. Section 6 reports the main results, comparisons, statistical validations, and discussion. Finally, conclusions and future research lines are listed in Section 7.

2  Contributions

In this work, we propose an automatic vasculature segmentation based on five components: pre-processing, feature extraction, discriminative feature selection, supervised classification, and post-processing. The main contributions are:

1.    The pre-processing stage enhances the blood vessels through a combination of filters, morphological operations, and Contrast Limited Adaptive Histogram Equalization (CLAHE).

2.    The feature extraction computes a wide variety of characteristics to cover the entire feature space and explore diverse segmentation approaches.

3.    The effective feature selection stage guarantees discriminative features in the classification stage. The computational power and resources are drastically reduced using only the optimal characteristics, which consequently increase the overall performance.

4.    Three different supervised classifiers are employed to prove the quality of the selected features: Artificial Neural Networks (ANN), Decision Trees (DT) and Support Vector Machines (SVM).

5.    Four datasets are used to assess our methodology. An ANOVA test is also performed to know statistically the improvement of the method presented in relation to the state-of-the-art.

3  Related Work

Comprehensive reviews of blood vessel segmentation techniques in retinal images were presented by Imran et al. [12] and Fraz et al. [13]. From these reviews and some recent publications, we can observe that some researchers propose supervised methodologies based on a feature extraction, followed by a classifier. For example, Marín et al. [14] implemented a feature vector with gray-level and Hu moment invariant characteristics and an ANN classifier. This method achieved an accuracy of 94.5% using the DRIVE dataset. Similarly, Adapa et al. [15] used ANNs fed with an input vector based on Zernike moments. They obtained an overall accuracy of 94.5%. Although this approach was simpler than Marín et al. [14], the number of parameters and their combination to reach the best performance was extremely challenging. The feature vector extracted by Sathananthavathi et al. [16] was 40D and used the BAT algorithm and random forest to select and classify the optimal 18 features. The final accuracy was 95.3% for the DRIVE dataset. Despite the acceptable accuracy of these methods, the computational resources needed were high as the feature vector was large. Moreover, Kumar et al. [17] applied 2D matched filters to detect vessels enhanced by the CLAHE method. The accuracy reached was 96.2% for the DRIVE dataset. However, the inherent pathologies leaded to miss-classified blood vessels.

Another approach is based on Deep learning architectures, which have been successfully employed for vasculature segmentation with impressive performances by Mansour [18]. Soomro et al. [19] proposed a strided fully CNN for retinal vessel delineation. The synthetic training data was generated through a Principal Component Analysis. This algorithm was assessed on DRIVE, STARE, and HRF datasets, obtaining an overall accuracy of 95.6%, 95.4%, and 96.2%, respectively. In this line, Luo et al. [20] presented a modified U-Net to train a semantic blood vessel segmentation model. Then, a conditional random field integrated the global information. This model produced an average accuracy of 86.5% for the DRIVE dataset. These methods allowed the diagnosis of early pathologies using only the vessels’ state.

The introduction of these automatic methods into daily clinical practice is still challenging due to the required accuracy, the limited computational resources, the processing speed, the image resolution, and the usability [21]. These shortcomings motivated this work to make a new design based on simple and effective processing algorithms and selecting a reduced number of optimal features. We decrease the computational cost and memory resources, while trying to keep the good performance results of the related works.

4  Proposed Methodology

The main challenge associated with retinal vessel segmentation is the false positives detection due to DR lesions (i.e., hemorrhages, microaneurysms, and exudates). The supervised methods used so far require highly discriminative features to reach an accurate delineation of vessels. It is required to find the optimal features in order to speed up the computation and reduce the resources. In this line, the methodology we propose includes a feature selection phase that relies on the Sequential Forward Selection (SFS) algorithm that is widely applied for its simplicity and speed [22,23], with a fitness function based on a Decision Tree (DT) classifier. After the feature selection process, three different classifiers (i.e., ANN, DT, and SVM) are implemented to demonstrate the discriminative power of the selected features. In the end, the best classifier will be selected according to the results obtained in different datasets.

Fig. 1 shows in more detail the first stage of our methodology: feature selection. It has the following steps: 1. image pre-processing to enhance the ocular vasculature, 2. feature extraction for numerical representation, and 3. effective feature selection based on the SFS algorithm. The second stage can be seen in Fig. 2. It is devoted to BV segmentation, with steps: 1) image pre-processing, 2) extraction of the selected features, 3) classification using three different algorithms to label the pixels as vessel or non-vessel, and 4) post-processing to fill holes in detected vessels and remove false positive (isolated) pixels.


Figure 1: Flowchart for selecting discriminative features for blood vessel classification


Figure 2: Flowchart for segmenting the blood vessels from color fundus images (application stage)

4.1 Pre-Processing

We start adjusting the image intensity to increase the contrast between both blood vessel and background pixels. Next, images may be resized. In our case, we work with 4 different datasets (3 of them are public and 1 is private from a local hospital). Images from the DRIVE and STARE datasets are resized to 540 pixels, and images from the Messidor and Sant Joan de Reus datasets are resized to 960 pixels. Afterward, the intensity channel from the HSI color space is selected to highlight the blood vessels.

The retinal blood vessels have a lower reflectance, and they appear to be darker than the background. Some vessels include a light line in the center, which precludes the segmentation. Thus, the images are filtered by applying an opening operation of three pixels in diameter to eliminate the brightest lines, using the disc as a structuring element. Additionally, uneven illumination on retinal images affects the background intensity, making vessels not distinguishable. To solve that issue, we propose to employ a 3×3 disc median filter in order to reduce the occasional salt and pepper noise, and a Gaussian filter to smooth the background (m×m=9×9, mean (μ)=0 and variance (σ2)=1.82, Gμ,σm=G0,1.829).

Regarding the process of acquiring fundus images, various lighting conditions trigger differences in the intensity of the background that are minimized by homogenizing the color information represented in IH (see Fig. 3, second column), we employ the CLAHE algorithm in channel I(HSI). This method is similar to the adaptive histogram equalization, where contrast amplification is limited to reduce the noise amplification problem [24]. Finally, the Top-Hat transformation is applied (see last column of Fig. 3) to estimate the complementary homogenized image IHC using Eq. (1), where γ is a morphological opening operation using an eight-pixel disc. An example of the output image is shown in Fig. 3 (third column).



Figure 3: Pre-processing of an image from Messidor, STARE, DRIVE and Sant Joan datasets

4.2 Feature Extraction

This stage finds the best set of numerical features representing a pixel’s characteristics, focusing on those that enable the distinction between blood vessels and background. Several studies [16,22] have demonstrated that an appropriate selection of features can improve the classification process performance.

In this work, we take a set of 20 features that are used in the literature. In particular, we consider five features that represent the gray level of the pixel, seven features about moment invariants, and eight features about Gabor transform responses over different angles [25].

4.2.1 Gray-Level Features

These features are based on the gray-level intensity and its distribution regarding neighborhood pixels. These features statistically describe the intensity variations, so they could be appropriate to distinguish the blood vessels as they have different intensity of color concerning the background of the eye fundus. A set of gray-level-based descriptors were derived from the homogenized images IH considering a square window with w×w dimension represented by Sx,yw and centered on a particular pixel loc9ated on coordinates (x,y). Several descriptors were formulated using that windows (similar to [14], which correspond to the Eqs. (2)–(6). These gray-level features may indicate the presence of blood vessels, but they do not contain any information about the shape of vessels. Moreover, they are sensitive to the fovea and the optic disc structures, which also are different from the background [15]. Hence, features describing the blood vessel’s shape must provide additional information about the eye vasculature.

f1(x,y)=IH(x,y)min(s,t)Sx,yw{IH(s,t)} (2)

f2(x,y)=max(s,t)Sx,yw{IH(s,t)IH(x,y)} (3)

f3(x,y)=IH(x,y)mean(s,t)Sx,yw{IH(s,t)} (4)

f5(x,y)=IH(x,y) (5)

f4(x,y)=std(s,t)Sx,yw{IH(s,t)} (6)

4.2.2 Moment Invariants Features

These features are determined by moment invariants, which define small regions in a window centralized in the pixel of interest. They are relevant because the blood vessels in retinal images exhibit variations in shape, size, and geometrical structure. We used some shape descriptors invariant to translation, rotation, and scale to detect these shapes, which are different in shape and angle. The descriptors are known as Hu moments [14,26] and Zernike moments [15], and have effectively been used for representing shape features in other works. In this paper, we have taken the Hu moments, which are described below. From the vessel-enhanced image IVE, described in Eq. (1), a sub-image is generated by taking a region of size fixed to 17×17. This dimension was chosen, guaranteeing that the window may contain a wide vessel. For the sub-image IVESx,y17, the 2-D moment of order is defined in Eq. (7).

mpq=ijipjqIVESx,y17(i,j)p, q=0,1,2, (7)

where summations are over the values of the spatial coordinates i and j spanning the sub-image, and IVESx,y17.

The corresponding central moment is defined in Eq. (8), where i¯ and j¯ are the coordinates of the center of gravity of the sub-image.

μpq=ij(ii¯)p(jj¯)qIVESx,y17(i,j) (8)

where i¯ and j¯ are the coordinates of the center of gravity of the sub-image. i¯=m10m00, j¯=m01m00

The normalized central moment of order (p+q) is defined in Eq. (9).

ηpq=μpqμ00γp, q=0,1,2, (9)

where γ=p+q2+1 p+q=2,3,4,

A set of seven-moment invariants in Eqs. (10)(16) represent undersize, translation, and rotation, can be derived from combinations of regular moments. They are known as Hu moment invariants.

ϕ1=η20+η02 (10)

ϕ2=(η20+η02)2+4η112 (11)

ϕ3=(η303η12)2+(3η21η03)2 (12)

ϕ4=(η30+η12)2+(η21+η03)2 (13)

ϕ5=(η303η12)(η30+η12)[(η30+η12)23(η21+η03)2]+(3η21η03)(η21+η03)[3(η30+η12)2(η21+η03)2] (14)

ϕ6=(η20η02)[(η30+η12)2(η21+η03)2]+4η11(η30+η12)(η21+η03) (15)

ϕ7=(3η21η30)(η30+η12)[(η30+η12)23(η21+η03)2]+(3η21η03)(η21+η03)[3(η30+η12)2(η21+η03)2] (16)

In this study, the logarithm transformation (Eq. (17)) is applied to the absolute value of the Hu moments in order to equalize the moments’ orders magnitudes. The transformed values are included in the feature vector of a pixel located at (x, y):

f6(x,y)=log|ϕ1|,f12(x,y)=log|ϕ7| (17)

4.2.3 Gabor Filter Response Features

The 2D linear Gabor filter is the modulation of the Gaussian kernel function by a sinusoidal plane wave and can be used for edge detection [25]. In the spatial domain, this filter is calculated as the product of Gaussian and an exponential function as given by Eq. (18), where XS=Xcos(θ)+Ysin(θ),YS=Xsin(θ)+Ycos(θ).

g(x.y)=exp[π(XS2σx+YS2σy)]cos(2πfXS) (18)

The parameter θ denotes the filter orientation, f is the frequency of the passband and σ is standard deviations of the filter. The Gabor filter response R(x,y) is computed by convolving the Gabor filter bank g(x,y) with the pre-processed image IH. The maximum filter response over the angle θ spanning [0,π] in steps of π/12 is calculated for each pixel at different scales (σ=2, 3, 4, 5) and frequencies (f=0.125, 0.225). The maximum response obtained for an orientation and a certain frequency is taken as the feature value, as proposed in [25]. So, we obtain eight Gabor-based features for each pixel, denoted f13(x,y)f20(x,y).

4.3 Effective Feature Selection

After collecting all the 20 different features F(x,y)=[f1(x,y),f2(x,y),,f20(x,y)], which represent different aspects of the image, we should study if this vector contains non-discriminative features. As a key contribution of this work, we propose to reduce the dimension of this initial feature vector by selecting the set of features that gives the minimal error rate in the classification of vessels.

The discriminative features for vessel segmentation may be found using the SFS algorithm. It is a search algorithm that starts from an empty set and gradually adds features selected by an evaluation function. The method pursues to minimize a goal evaluation function over all possible feature subsets. In our case, this function is the error rate in the blood vessel classification task. Therefore, the classifier needs the ground truth to compare the results and obtain this indicator.

We selected the Decision Trees method to classify the pixels in the SFS algorithm. This classifier has a small memory usage and makes a fast and accurate prediction. A DT is a greedy non-parametric supervised learning method that build a decision tree, where each branch establishes conditions for belonging to one of the classes [27,28]. Decision trees require training data, test data, a heuristic evaluation function, and a stopping criterion function. The partition of the training and test data was made with the hold-out validation, using 70% for training and 30% for testing. The optimization criterion for classification was the Gini’s diversity index. The stopping rules are: 1) the node contains only samples of one class, 2) there are less samples than the threshold defined, 3) any split produces fewer than the number of leaf node samples defined, and 4) there are no more attributes available.

Using SFS, we found that only 5 of the 20 features are needed to make an appropriate segmentation of blood vessels in retinal images. These discriminant features are f1, f2, f3, f4, f5 and f6, corresponding to the four gray-level features and one Moment invariants feature.

Implementing the SFS algorithm in the features selection process minimizes the misclassification rate using a reduced feature vector, which guarantees high performance in the blood vessel segmentation. The obvious computational cost savings can be significant as we reduce the number of features from 20 to 5.

4.4 Classification

The classification stage assigns a label to each pixel, indicating if it corresponds to a vessel or a non-vessel. Thus, it corresponds to a binary classification problem. To validate the performance of the subset of 5 discriminant features identified in the previous stage, we have used three different supervised classifiers: ANN (artificial neural networks), DT (decision trees), and SVM (support vector machines). In that way, we want to prove the effectiveness of the five selected features independently of the classification algorithm.

The DT classifier assigns a class following a set of rules that are constructed from a tree structure, as explained before. Each node contains a feature, and the branches departing from a node correspond to the different possible values of that feature [29]. In our experiments, the DT has been trained using the pixels of two complete images randomly selected from the DRIVE dataset. The DT construction was made with a minimum number of leaf node observations of 300 and using a cross-validation process.

In ANN-based classifiers, the performance is highly influenced by the amount of training data. If data is scarce, the network will not generalize well. However, a large number of samples requires more computational time and resources. On our experiments, we randomly selected 10% of the total number of the DRIVE images pixels, fairly divided into the vessel and non-vessel pixels to train the ANN architecture, which is used in all datasets. This amount was enough to obtain the required performance. The 70% of pixels are employed in the training process, and the rest (30%) for validation, maintaining a constant ratio between the two classes. The ANN input layer has the same number of neurons as the feature vector. Several topologies were tested empirically for the hidden layers. Finally, we set three hidden layers with 15 neurons in each layer, similar to the multi-layer feed-forward network in [14]. The output layer comprises only one neuron associated with a non-linear logistic sigmoid activation function.

SVM classifier is another supervised approach used in the blood vessel segmentation task. An SVM classifier finds the best hyperplane to separate the data points from two different classes. The best hyperplane for an SVM has the most significant margin between the two classes. The data points that are closest to this hyperplane are the support vectors. A drawback of SVM is that it is memory-intensive in the training process, as it works in the dual space. The algorithm needs to store a N×N kernel matrix, where N is the number of training samples. Our training process is performed only with 1% of random pixels collected from one retinal image from Drive due to computational limitations. We employed the sequential minimal optimization and the radial basis function kernel in the configuration.

4.5 Post-Processing

We consider the premise that pixels belonging to a vessel must have neighbor pixels belonging to vessels, as well. Then, in the first step of our post-processing, we want to fill pixel gaps (holes) in the detected blood vessels (i.e., false negatives). The second stage subsequently removes pixels classified as vessels, but which are isolated (i.e., false positives). Pixels of the vessel class may have neighbor pixels marked as non-vessel. This problem is corrected with an iterative fill operation, considering that pixels with at least six neighbors classified as vessel points must also be vessel pixels. The small-isolated regions, misclassified as blood vessels, are removed.

4.6 Datasets

To evaluate the proposed method, we used three publicly available datasets and one in-house dataset. The DRIVE dataset [30] has 40 color fundus images at 768 × 584 pixels. The STARE dataset [31] has 20 retinal images at 700 × 605 pixels. The Messidor [32] dataset contains 1200 color fundus images at 1440 × 960, 2240 × 1488, and 2304 × 1536 pixels. The local database of the Hospital Sant Joan de Reus consists of 800 RGB color images, 500 of which at 2040 × 1488 pixels, and the remaining 300 at 3008 × 2000.

5  Results and Discussion

This section presents some examples of segmented images and quantitative results obtained with various performance measures. Then, a comparison with other state-of-the-art works is made using statistical tests.

5.1 Experimental Results

An example of segmented images is given in Fig. 4 that shows the phases of our segmentation pipeline. A random sample was picked for each dataset (e.g., Messidor, Sant Joan, DRIVE and STARE). The numerical quality indicators for DRIVE and STARE datasets are presented in Tab. 1.


Figure 4: Results from Messidor, STARE, DRIVE and our in-house (i.e., Sant Joan) datasets


To statistically compare the performance obtained from three different classifiers for all datasets, we computed an ANOVA test. The pattern of differences of means between them was analyzed with a post-hoc test). Specifically, the Games–Howell Post-Hoc test is a non-parametric method to contrast combinations of groups. It does not presume equal variances and sample sizes. In Tab. 2, from the Games-Howell test output we selected the optimal classifier for each indicator and dataset, considering the p-value within a 95% confidence interval. According to these results, the ANN classifier exhibits high Se and Acc for all four datasets. The SVM classifier reached high Sp for all four datasets, but a low Se, because the training process is performed only with 1% of random pixels collected from one retinal image due to computational limitations, as we mentioned in Section 4.4. It can also be seen in Tab. 1 that ANN sacrifices a bit of specificity to obtain a considerably better sensitivity, so in overall it is the best performing method.


Tabs. 1 and 2 indicate good segmentation performances for all classifiers using our effective 5-dim feature vector selected by the SFS algorithm. Nevertheless, the ANN architecture achieved the highest Se and Acc. Therefore, it was used to compare our work’s performance with the state-of-the-art. To validate the selected features again, we changed the DT by the ANN as a classifier within the SFS algorithm and repeated the selection process. Finally, this second test evidenced that the 5-dim feature vector, initially selected, provides the minimum error rate in the blood vessel segmentation process.

5.2 State-of-the-Art Comparison

A robust comparison with past/current works has been done through extensive ANOVA testing for both DRIVE and STARE datasets, considering the performances published in the papers. No results have been published yet with Messidor and Sant Joan de Reus datasets to the best of our knowledge. This statistical analysis uses variances to determine if the mean between two segmentation approaches is different or not [33]. Tab. 3 shows the F statistic with a critical value of 4.0981 and the significance (p-value), which is the probability of obtaining F values under the null hypothesis of mean equality. If the p-value associated with the F statistic is less than 0.05, the null hypothesis is rejected, and the alternative is accepted, which implies that the means of each method are different with a 95% of confidence.


For the DRIVE and STARE dataset, we obtained a higher Acc than the other authors indicated in Tab. 3. Our proposal achieved similar Se values compared with the references in Tab. 3, except for Roy et al. [35] which we overcame. Regard to Sp, Marín et al. [14], Adapa et al. [15], Zhao et al. [34], and Farokhian et al. [37] obtained higher values but quite close to our approach. Next, Tab. 4 presents the performance results achieved by different state-of-the-art methods (i.e., feature extraction, miscellaneous, and deep learning) using both DRIVE and STARE datasets.


Our method performed slightly worse than other complex classifiers such as convolutional neural networks. However, these methodologies require extensive training datasets, and the available datasets contain a small number of annotated images, having a high risk of overfitting [37]. Additionally, they spend large computational resources in the training process. Furthermore, our work was validated with four datasets, including images with different resolutions and constraints, unlike other proposals validated only with DRIVE and STARE datasets.

Similar methodologies such as Marín et al. [14], Adapa et al. [15], and Thangaraj et al. [25] also used ANNs and feature extraction techniques. They obtained very similar Acc and Se values than ours. Nevertheless, the works by Marín et al. [14] and Adapa et al. [15] omitted the feature selection phase, thus some features could be redundant. Furthermore, the authors used a larger feature vector and, consequently, more computational memory and resources. This can be seen in Tab. 5. We used a minimal number of features and the computational time was reduced notably, despite using a workstation with less processing capacity than Adapa et al. [15] and Sathananthavathi et al. [16]. If we compare the computational time using our workstation and varying the number of features, we can state that using the selected 5-dim vector, the time is reduced to 50% of the 7-dim vector proposed in Marín et al. [14] and up to 85% in comparison with the initial 20-dim vector.


6  Conclusions

In summary, in this work, we developed a vasculature segmentation methodology for retinal color fundus images. Firstly, morphological operations, bank filters, and the CLAHE algorithm were used to enhance blood vessels and remove artifacts and lighting effects. The feature extraction procedure computed an initial 20-dim vector build upon gray-level, moment invariant and Gabor features. A feature selection based on the SFS algorithm and DT classifier was added to uncover the most discriminative features. The input vector to the classifiers was efficiently reduced from 20 to 5 dimensions. Post-processing was finally designed with morphological operations to fill holes in detected vessels and eliminate isolated pixels. Our methodology was evaluated on three publicly accessible datasets (i.e., Messidor, DRIVE, and STARE) and one private dataset provided by Hospital Universitari Sant Joan de Reus (in Catalonia, Spain).

The overall performance was evaluated using sensitivity (Se), specificity (Sp), and accuracy (Acc) measures. The obtained Se, Sp, and Acc from the ANN classifier using the public datasets were for DRIVE 70.5%, 97.2%, and 96.3%, and STARE 73.3%, 97.9%, and 96.5%, respectively. Regarding the in-house dataset, the Se, Sp and Acc were 71.5%, 97.0% and 95.6%, respectively. Additionally, we calculated an ANOVA test to validate our results and compare the ANN classifier with state-of-the-art results. From these results, we can say that the goal of the work has been achieved. The first test revealed that the five selected features are suitable for all classifiers. Therefore, we have reduced the number of features needed to identify blood vessels in eye fundus images properly. Consequently, the effective feature selection drastically minimized the algorithm complexity and resources. The second test demonstrated that our method has similar performances to the literature in both DRIVE and STARE images using this 5-dim feature vector. Further research focuses on implementing a fast, accurate, and straightforward ANN-based architecture fed with the optimized feature vector to reach the optimal accuracy for clinical productization. Additionally, the feature extraction time can be considerably reduced by using parallel computation. Finally, the proposed methodology could be applied for finding the appropriate features needed to detect other pathologies or structures such as the optic disc and macula in digital fundus images.

Acknowledgement: The first author has been endorsed by Fundación Carolina with a predoctoral grant. The Ministry of Science, Technology, and Innovation of Colombia supported the fourth author’s research training process as a young researcher and innovator.

Funding Statement: This work has been funded by the research project PI18/00169 from Instituto de Salud Carlos III & FEDER funds. University Rovira i. Virgili also provided funds with Project 2019PFR-B2-61.

Conflicts of Interest: The authors declare no conflicts of interest to report regarding the present study.


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