Glioma Segmentation on 3D MRI Using 2D U-Net: A Study on the BraTS Dataset

1. Introduction

Brain tumors, particularly gliomas, are among the most aggressive and life-threatening cancers affecting the central nervous system [1]. Accurate and early delineation of tumor volumes from magnetic resonance imaging (MRI) scans is essential for effective treatment planning, including radiotherapy, surgical intervention, and prognosis assessment [2,3,4,5]. Manual annotation by radiologists, however, is time-consuming, subject to inter-observer variability, and not scalable for large datasets [6].

Segmentation methods in medical imaging are typically categorized into several classes, such as threshold-based techniques such as Otsu’s method [7], region-based approaches such as region growing [8], edge-based methods such as the Canny edge detector [9], clustering-based techniques such as K-means, Fuzzy C-Means [10], model-based methods such as active contours, level sets [11,12], and machine or deep learning-based approaches such as U-Net, Mask R-CNN, TransUNet [13,14,15]. Each category offers specific advantages depending on the imaging modality, anatomical target, and desired segmentation accuracy.

Although traditional segmentation techniques play a key role in outlining tumor boundaries, their accuracy can be significantly improved by incorporating advanced imaging methods. One such method, Diffusion Tensor Imaging (DTI), offers detailed insights into the brain’s white matter structure, helping to refine segmentation results and support more accurate tumor modeling [16,17].

Diffusion Tensor Imaging (DTI), a specialized MRI technique, is extensively used in neuroimaging to analyze the diffusion of water molecules, particularly for mapping white matter pathways. However, raw DTI images often suffer from low contrast and indistinct tissue boundaries. To enhance image quality, several methods have been employed, including the extraction of scalar indices such as fractional anisotropy (FA) and mean diffusivity (MD), bias field correction, and image fusion techniques. One notable method is the Uni-Stable enhancement technique, which combines clustering maps from various algorithms to produce stable, high-contrast images. Its three-dimensional extension, Uni-Stable-3D, interpolates between anisotropic slices to generate volumetric probability maps that are well-suited for robust tissue segmentation [18,19].

Beyond segmentation, tumor analysis also encompasses detection and prediction. Detection methods range from traditional techniques such as clustering and morphological operations to deep learning-based models, including U-Net, V-Net, and Mask R-CNN, which enable accurate tumor localization and delineation [20,21,22,23,24]. Prediction models aim to simulate tumor growth over time and include reaction-diffusion models, spatio-temporal simulations, and machine learning frameworks such as long short-term memory (LSTM) networks and survival analysis models. For example, an anisotropic reaction-diffusion model based on DTI data was proposed to simulate glioma progression across white and gray matter, demonstrating its effectiveness for treatment planning and prognosis [25].

This study addresses these limitations by proposing a deep learning-based approach for glioma segmentation using a 2D U-Net framework. The model is trained and tested on BraTS 3D multimodal MRI scans with expert-labeled tumor masks. Each scan includes four modalities: FLAIR, T1, T1CE, and T2. Though the data is 3D, our approach processes it as 2D slices to reduce computational demands while preserving relevant features. This allows efficient yet accurate tumor segmentation. Such models hold the potential to enhance diagnostic accuracy, reduce variability in interpretation, and accelerate clinical decision-making. Our solution is reproducible and based on widely available tools and datasets.

2. Dataset Description

In this study, we used the BraTS dataset, available on Synapse repository [26]. This dataset is widely recognized for benchmarking brain tumor segmentation algorithms and is composed of multimodal 3D MRI scans collected from patients diagnosed with glioblastoma multiforme (GBM) and low-grade gliomas (LGG). The dataset reflects clinical heterogeneity and variability in tumor appearance, making it suitable for training and evaluating deep learning models.

Each case in the dataset includes four different MRI scans, with each modality capturing distinct anatomical and pathological features. Together, they provide a comprehensive view of the brain, which helps improve the accuracy of tumor segmentation. An overview of these modalities is provided in Table 1.

Figure 1. Visual comparison of the four MRI modalities.

Figure 1. Visual comparison of the four MRI modalities.

Each imaging modality offers distinct structural and pathological information, and combining them allows for a more precise mapping of tumor subregions. The dataset includes voxel-level annotations with four different classification labels.

3. Data and Image Preprocessing

In the field of medical imaging, especially when dealing with MRI scans, it's common to encounter differences in image intensity, spatial resolution, and anatomical alignment. These inconsistencies can pose significant challenges when training deep learning models, as they introduce noise and reduce data reliability. To address these issues, we implemented a thorough preprocessing pipeline aimed at normalizing the data, enhancing key features, and preparing both images and corresponding labels for segmentation. The process is organized into two main components: image preprocessing and label preprocessing.

3.1. Image Preprocessing

Intensity Normalization 

MRI images often vary in brightness and contrast depending on the scanner type, imaging protocol, or even the patient being scanned. To reduce this variability and create a more consistent dataset, we applied normalization to each image. This technique standardizes the pixel intensity values so they center around a mean of zero with a standard deviation of one, helping the model better detect relevant structural patterns rather than being distracted by intensity differences [28].

Slice Selection  

Rather than using the entire 3D volume, we focused on axial slices that are most relevant for tumor analysis. Specifically, slices from index 22 to 122 were extracted from each scan. This approach avoids slices that contain little to no brain tissue and ensures that the model concentrates on regions where tumors are typically found [3].

Cropping and Resizing  

To ensure uniform input dimensions suitable for convolutional neural networks, each selected slice was cropped and resized to 128 × 128 pixels. This step helps maintain consistency across samples while also optimizing memory usage and training speed [29].

Data Augmentation  

To make our model more robust and prevent overfitting, we incorporated several data augmentation techniques during training. These included random horizontal and vertical flips, small-angle rotations, and changes in image intensity. By simulating different imaging conditions, these augmentations help the model generalize better to new, unseen data [30].

Input Modalities  

Each input sample was composed of two MRI sequences: FLAIR and T1CE. FLAIR images are particularly sensitive to areas of swelling or edema, while T1CE images are effective at showing regions of contrast uptake, often associated with active tumor tissue. Using both modalities together provided the model with richer and more complementary information for accurate tumor segmentation [25].

3.2. Label Preprocessing

Label Remapping  

The original segmentation masks used four labels: 0, 1, 2, and 4. Since label 4 was not sequential (it represented the enhancing tumor), we remapped it to 3 to produce a clean, continuous label set. The final label scheme used in our study was:

Table 4. Label Remapping.

Label	Description
0	Background
1	Necrotic/Non-enhancing Tumor Core (NCR/NET)
2	Edema (ED)
3	Enhancing Tumor (ET)

Table 4. Label Remapping.

Label	Description
0	Background
1	Necrotic/Non-enhancing Tumor Core (NCR/NET)
2	Edema (ED)
3	Enhancing Tumor (ET)

This adjustment simplified data handling and ensured compatibility with standard categorical loss functions used in deep learning frameworks [32].

3.3. Model Architecture

To perform brain tumor segmentation, we implemented a 2D U-Net architecture using TensorFlow 2.12 and Keras. U-Net is particularly effective for biomedical image segmentation, as it captures both local and global context while preserving spatial detail. Its encoder–decoder structure, enhanced with skip connections, allows for precise reconstruction of tumor boundaries by combining low-level spatial features with high-level semantic information [33].

U-Net Structure  

• Encoder Path:

The encoder comprises four blocks. Each block includes two 2D convolutional layers (3×3 kernels, ReLU activation, 'same' padding), followed by a 2×2 max-pooling operation for downsampling. The number of filters doubles at each level: 32, 64, 128, and 256. This progressive structure enables the network to extract increasingly abstract features [33].

• Bottleneck:

At the network’s deepest layer, two convolutional layers with 512 filters each are followed by a dropout layer (rate = 0.2) to mitigate overfitting.

• Decoder Path:

The decoder mirrors the encoder with upsampling layers (via transposed convolutions), followed by convolutional blocks. Skip connections from corresponding encoder levels are concatenated to preserve spatial resolution. Filter sizes decrease symmetrically: 256, 128, 64, and 32.

• Output Layer:

The final layer is a 1×1 convolution with SoftMax activation, yielding a four-channel output that corresponds to the segmentation classes: background, necrotic core, edema, and enhancing tumor.

Input and Output Specifications  

• Input Shape: Each input consists of two channels—FLAIR and T1CE—resulting in a shape of (128, 128, 2).
• Output Shape: The model produces a segmentation map of shape (128, 128, 4), with class-wise probabilities for each tumor sub-region.

Figure 2. U-NET Structure [34].

Figure 2. U-NET Structure [34].

Training Configuration  

• Frameworks: TensorFlow 2.12 and Keras
• Loss Function: Categorical Crossentropy (suitable for multi-class segmentation)
• Optimizer: Adam optimizer with a learning rate of 0.001
• Regularization: Dropout (rate = 0.2) in the bottleneck layer

Evaluation Metrics  

To comprehensively assess model performance, we used several evaluation metrics, each providing insights into different aspects of segmentation quality [35,36]:

• Mean Intersection over Union (Mean IoU):

Also known as the Jaccard Index, this metric evaluates the overlap between predicted and ground truth regions by computing the ratio of their intersection to their union:

$$IoU={\displaystyle \frac{\left|A\cap B\right|}{\left|A\cup B\right|}}$$

(1)

It offers a strict measure of segmentation accuracy and is computed per class before averaging.

• Dice Similarity Coefficient (DSC):

The Dice coefficient measures how closely the predicted segmentation matches the ground truth. It is especially useful for imbalanced data such as tumor regions:

• o Overall Dice: Aggregates segmentation performance across all classes.
• o Class-specific Dice: Computed separately for necrotic core, edema, and enhancing tumor regions.

$$DSC={\displaystyle \frac{2\left|A\cap B\right|}{\left(\left|A\right|+\left|B\right|\right)}}$$

(2)

• Precision:

Indicates the proportion of predicted positive pixels that are actually positive.

• Sensitivity (Recall):

Also called the true positive rate, this metric measures the model’s ability to detect all actual tumor pixels:

$$Sensitivity={\displaystyle \frac{TP}{\left(TP+FN\right)}}$$

(3)

• Specificity:

Measures the proportion of correctly identified negative (background) pixels, helping assess false positive rates:

$$Specificity={\displaystyle \frac{TN}{\left(TN+FP\right)}}$$

(4)

These metrics provide a balanced evaluation across detection accuracy, overlap, and class-specific segmentation—key for ensuring clinical reliability in automated tumor delineation systems.

3.4. Training Strategy

• Train/Val/Test split: 70% / 15% / 15%
• Epochs: 30
• Optimizer: Adam (learning rate = 0.001)
• Callbacks: ReduceLROnPlateau, EarlyStopping, CSVLogger
• Batch size: 1 (due to memory constraints)
• Custom DataGenerator for real-time augmentation and loading

4. Results

The U-Net model was trained for 30 epochs using TensorFlow and Keras. The best validation performance was observed at epoch 19, with the following results:

Table 5. Overall Validation Metrics and Additional Performance Measures.

Metric	Value
Validation loss	0.0284
Validation accuracy	98.84%
Global Dice Coefficient	0.5139
Precision	99.08%
Specificity	99.69%

Table 5. Overall Validation Metrics and Additional Performance Measures.

Metric	Value
Validation loss	0.0284
Validation accuracy	98.84%
Global Dice Coefficient	0.5139
Precision	99.08%
Specificity	99.69%

Table 6. Validation per-class Dice (epoch 19).

Tumor Sub-Region	Validation Dice Score
Necrotic Core (NCR/NET)	0.4292
Edema (ED)	0.4644
Enhancing Tumor (ET)	0.5895

Table 6. Validation per-class Dice (epoch 19).

Tumor Sub-Region	Validation Dice Score
Necrotic Core (NCR/NET)	0.4292
Edema (ED)	0.4644
Enhancing Tumor (ET)	0.5895

• Training per-class Dice:

• NCR/NET: 0.4920
• ED: 0.6751
• ET: 0.6251

Table 7. Validation per-class Dice (epoch 19).

Tumor Sub-Region	Training Dice Score
Necrotic Core (NCR/NET)	0.4920
Edema (ED)	0.6751
Enhancing Tumor (ET)	0.6251

Table 7. Validation per-class Dice (epoch 19).

Tumor Sub-Region	Training Dice Score
Necrotic Core (NCR/NET)	0.4920
Edema (ED)	0.6751
Enhancing Tumor (ET)	0.6251

Figure 3. Segmentation: Input MRI, Ground Truth, and Prediction.

Figure 3. Segmentation: Input MRI, Ground Truth, and Prediction.

5. Discussion

The results of this work show that employing a 2D U-Net for brain tumor segmentation—by processing 3D MRI scans slice by slice—is a practical and effective strategy. Although this method doesn't leverage the complete 3D spatial context, it still performed well in identifying critical tumor regions like the Whole Tumor (WT), Tumor Core (TC), and Enhancing Tumor (ET). This aligns with earlier findings from BraTS evaluations that showed 2D models can still provide reliable results when properly trained [37].

6. Conclusion

This thesis supports the effectiveness of a 2D U-Net model for segmenting brain tumors from multimodal MRI data. Even without utilizing full volumetric information, the model successfully distinguished between key tumor components and achieved encouraging segmentation performance.

The main benefit of this approach lies in its simplicity and efficiency. It doesn’t require extensive computational resources, making it accessible for both clinical research settings and practical deployment. The findings reinforce the potential of 2D convolutional models in medical image segmentation, especially when paired with thoughtful preprocessing and training strategies [40].