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Objective

Changes in retinal vascular morphology serve as crucial indicators for diagnosing various diseases, such as diabetic retinopathy, hypertension, and cataracts. Traditional diagnosis of retinal diseases primarily relies on manual assessment by clinicians, typically involving the analysis of retinal vascular curvature, width, and branching patterns based on imaging results from fundus examinations, optical coherence tomography, and fluorescein angiography. However, these imaging outcomes are susceptible to interference from factors such as illumination and noise, which increase the difficulty for clinicians in distinguishing retinal vessels from the background. Furthermore, inherent ocular structures like the optic cup and optic disc regions, as well as pathological alterations such as hard exudates, soft exudates, and the macular area, can also impede clinicians' judgment. Diagnostic results often vary subjectively among different physicians, potentially leading to misdiagnosis due to insufficient experience or fatigue. Automated retinal vessel segmentation technology can not only significantly reduce the time and effort required for manual annotation by clinicians and improve diagnostic efficiency but also minimize the impact of human factors to the greatest extent, providing more objective results to assist physicians in decision-making. Therefore, developing an accurate and automated retinal vessel segmentation technique holds substantial practical significance.

Methods

In the field of retinal vessel segmentation, existing methods can be broadly categorized into unsupervised and supervised approaches. Unsupervised methods do not rely on manually annotated data and primarily achieve segmentation by analyzing the morphological features of vessels. Common techniques include matched filtering-based, edge detection-based, and model-based methods. Matched filtering methods mainly utilize Gaussian kernel functions or their variants, which resemble the cross-sectional shape of blood vessels, to construct two-dimensional linear filter banks. These methods enhance tubular structures in retinal images through multi-scale and multi-directional filter responses, combined with thresholding for preliminary detection of vessel pixels. Edge detection-based methods capture boundary features between vessels and the background by calculating gradient changes in pixel intensity or using differential operators such as Canny and Sobel, often integrated with local or global thresholding strategies to extract vascular contours with continuous topological structures. Model-based methods rely on geometric or statistical models, such as active contour models, level set methods, or vascular tubular models, to mathematically describe vessel structure and distribution. They iteratively optimize energy functionals or probabilistic fitting processes to gradually evolve fine segmentation boundaries that adaptively conform to vessel morphology. However, such methods often depend on manually designed feature extraction pipelines, making it difficult to fully capture the complex topological structures of vessels, thereby resulting in limited segmentation performance. In contrast, supervised methods require expert-annotated data as training samples to achieve higher accuracy in vessel segmentation tasks. These methods can be further divided into traditional machine learning methods and deep learning methods. Traditional machine learning methods typically involve two steps: manual feature extraction and classification. Handcrafted features mainly include edge responses, wavelet responses, principal component information, and color intensity information. Based on the choice of classifier, they can be roughly categorized into k-nearest neighbors, random forests, support vector machines, and Gaussian mixture models. Traditional machine learning methods extract segmentation targets based on vascular features and fundus image characteristics. Compared to manual screening, they offer advantages such as shorter processing time and faster segmentation. However, their feature extraction process still requires manual design and cannot adequately represent the multi-scale structural features of vessels. With the continuous advancement and development of deep learning, it has gradually been adopted across various tasks in computer vision. In the field of medical image analysis, segmentation algorithms have been continuously updated and iterated. The introduction of various deep learning models and modules has further improved the accuracy and efficiency of fundus vessel segmentation algorithms. Compared to traditional machine learning methods, deep learning methods can automatically learn optimal features and achieve predictive modeling without human intervention, offering higher segmentation efficiency. Nevertheless, challenges such as limited representation of fine vessels, interference from complex backgrounds, and discontinuities in vessel structures remain. To address the aforementioned issues, this paper proposes a retinal vessel segmentation algorithm based on Grouped Channel Transformer and Modulated Fusion. First, a dual-dimensional cooperative attention module is designed in the encoder to enhance the distinguishability of vessel features and improve the model's accuracy in segmenting microvessels. Second, a Grouped Channel Transformer module is applied to construct a dual-encoder architecture, establishing global dependencies to effectively capture detailed vessel information. Finally, a Modulated Fusion module is introduced at the decoder to enhance feature fusion between the encoder and decoder, thereby improving the model's robustness against noise interference.

Results and Discussions

Experiments conducted on the DRIVE, CHASE_DB1, and STARE datasets demonstrate that the proposed algorithm achieves accuracy rates of 0.9711, 0.9762, and 0.9758, sensitivities of 0.8026, 0.8219, and 0.8042, and specificities of 0.9873, 0.9866, and 0.9899, respectively. The proposed method outperforms other algorithms in overall segmentation performance, demonstrating superior segmentation capability.

Conclusions

GTMF-Net demonstrates robust vessel segmentation capabilities on the DRIVE, CHASE_DB1, and STARE datasets. It achieves a favorable balance between model complexity and segmentation performance, offering both relatively low computational cost and high segmentation accuracy. However, the algorithm currently exhibits limitations in feature extraction within low-contrast regions, which can lead to mis-segmentation. Future work will focus on optimizing the algorithm's design to improve the accuracy of vessel identification in pathological areas.

, authors=Liming Liang, Lingliang Wang, Jinhui Cai, Chengbin Wang, authorsList=Liming Liang, Lingliang Wang, Jinhui Cai, Chengbin Wang, authorCompany=null, correspAuthors=Lingliang Wang, authorNote=null, correspAuthorsNote=
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针对视网膜血管分割存在微细血管表征能力有限、复杂背景干扰和血管结构断裂等问题,提出一种分组通道Transformer与调制融合的视网膜血管分割算法。首先设计双维协同注意力模块于编码部分,增强微细血管的特征表达,有效提升血管分割能力。其次在编码端构建分组通道Transformer模块,旨在捕获血管之间的长程依赖关系,精确捕捉血管纹理信息。最后在解码端引入调制融合模块,有效融合编解码特征信息,抑制病灶区域噪声干扰。在数据集DRIVE、CHASE_DB1和STARE上进行实验,所提算法准确率分别为0.9711、0.9762和0.9758,灵敏度分别为0.8026、0.8219和0.8042,特异性分别为0.9873、0.9866和0.9899。该方法在整体分割效果方面优于其他算法,展现出更好的分割性能。

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作者贡献

梁礼明:指导论文选题、论文修改;王灵亮:设计并完成实验,论文写作;蔡锦辉:研究资料的收集;王成斌:协助完成论文修改。

梁礼明(1967-),男,硕士,教授,硕士生导师,主要研究方向为机器学习、模式识别与图像处理等。E-mail:

王灵亮(2001-),男,硕士研究生,主要研究方向为医学图像处理。E-mail:

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Novel extraction of discriminative fine-grained feature to improve retinal vessel segmentation[Z]. arXiv: 2505.03896, 2025. https://doi.org/10.48550/arXiv.2505.03896., articleTitle=null, refAbstract=null)], funds=null, companyList=[AuthorCompany(id=1319955274417427101, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, xref=null, ext=[AuthorCompanyExt(id=1319955274430010014, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, companyId=1319955274417427101, language=EN, country=null, province=null, city=null, postcode=null, companyName=null, departmentName=null, remark=School of Electrical Engineering and Automation, Jiangxi University of Science and Technology, Ganzhou, Jiangxi 341000, China), AuthorCompanyExt(id=1319955274438398623, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, companyId=1319955274417427101, language=CN, country=null, province=null, city=null, postcode=null, companyName=null, departmentName=null, remark=江西理工大学电气工程与自动化学院,江西 赣州 341000)])], figs=[ArticleFig(id=1319955276770431676, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=EN, label=Fig.1, caption=Grouped channel Transformer and modulation fusion retinal vessel segmentation algorithm, figureFileSmall=o93dAF+nsS+VX11n3pbmFw==, figureFileBig=m7v+MKcPvvAuhr+KNYNqow==, tableContent=null), ArticleFig(id=1319955276841734845, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=CN, label=图1, caption=分组通道Transformer与调制融合的视网膜血管分割算法, figureFileSmall=o93dAF+nsS+VX11n3pbmFw==, figureFileBig=m7v+MKcPvvAuhr+KNYNqow==, tableContent=null), ArticleFig(id=1319955277038867134, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=EN, label=Fig.2, caption=Dual-dimensional collaborative attention module, figureFileSmall=v28qxwz998xOY1G35HWPrQ==, figureFileBig=Pb43U+c+A6CLQ9mfbwJBbQ==, tableContent=null), ArticleFig(id=1319955277097587391, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=CN, label=图2, caption=双维协同注意力模块, figureFileSmall=v28qxwz998xOY1G35HWPrQ==, figureFileBig=Pb43U+c+A6CLQ9mfbwJBbQ==, tableContent=null), ArticleFig(id=1319955277173084864, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=EN, label=Fig.3, caption=Grouped channel Transformer module, figureFileSmall=0iSGICI7HgPu5xyfJucTnw==, figureFileBig=tZ7oWwv2PGMe4Rw+L4UP7g==, tableContent=null), ArticleFig(id=1319955277244388033, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=CN, label=图3, caption=分组通道Transformer模块, figureFileSmall=0iSGICI7HgPu5xyfJucTnw==, figureFileBig=tZ7oWwv2PGMe4Rw+L4UP7g==, tableContent=null), ArticleFig(id=1319955277311496898, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=EN, label=Fig.4, caption=Grouped channel-wise self-attention module, figureFileSmall=4oQSdVRKIx+EGbyCpWbbuA==, figureFileBig=Lx8ymXqoS2g58T5AUif05A==, tableContent=null), ArticleFig(id=1319955277378605763, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=CN, label=图4, caption=分组通道自注意力模块, figureFileSmall=4oQSdVRKIx+EGbyCpWbbuA==, figureFileBig=Lx8ymXqoS2g58T5AUif05A==, tableContent=null), ArticleFig(id=1319955277445714628, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=EN, label=Fig.5, caption=Modulation fusion module, figureFileSmall=qQF8LHuyvRGZUOv690MkiQ==, figureFileBig=66RaivZMdwCwTPxU+Aw4BQ==, tableContent=null), ArticleFig(id=1319955277521212101, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=CN, label=图5, caption=调制融合模块, figureFileSmall=qQF8LHuyvRGZUOv690MkiQ==, figureFileBig=66RaivZMdwCwTPxU+Aw4BQ==, tableContent=null), ArticleFig(id=1319955277596709574, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=EN, label=Fig.6, caption=Preprocessed image. 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Comparison of performance metrics of different algorithms

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DatasetMethodAccSenSpeAUCF1
DRIVEU-Net[8]0.97040.79540.98720.98710.8250
Attention U-Net[21]0.97100.79630.98780.98820.8282
FR U-Net[22]0.97050.80130.98670.98760.8264
GT-DLA-dsHFF[23]0.97100.80060.98740.98810.8289
Ours0.97110.80260.98730.98840.8298
CHASE_DB1U-Net[8]0.97470.80850.98590.98850.8015
Attention U-Net[21]0.97600.80370.98760.98990.8091
FR U-Net[22]0.97420.80430.98560.98780.7975
GT-DLA-dsHFF[23]0.97580.80750.98710.98970.8081
Ours0.97620.82190.98660.99010.8136
STAREU-Net[8]0.97530.79240.99030.99030.8305
Attention U-Net[21]0.97560.78800.99100.99050.8312
FR U-Net[22]0.97480.80390.98890.99010.8299
GT-DLA-dsHFF[23]0.97560.79970.99010.99080.8335
Ours0.97580.80420.98990.99110.8350
), ArticleFig(id=1319955278519456465, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=CN, label=表1, caption=

不同算法性能指标对比

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DatasetMethodAccSenSpeAUCF1
DRIVEU-Net[8]0.97040.79540.98720.98710.8250
Attention U-Net[21]0.97100.79630.98780.98820.8282
FR U-Net[22]0.97050.80130.98670.98760.8264
GT-DLA-dsHFF[23]0.97100.80060.98740.98810.8289
Ours0.97110.80260.98730.98840.8298
CHASE_DB1U-Net[8]0.97470.80850.98590.98850.8015
Attention U-Net[21]0.97600.80370.98760.98990.8091
FR U-Net[22]0.97420.80430.98560.98780.7975
GT-DLA-dsHFF[23]0.97580.80750.98710.98970.8081
Ours0.97620.82190.98660.99010.8136
STAREU-Net[8]0.97530.79240.99030.99030.8305
Attention U-Net[21]0.97560.78800.99100.99050.8312
FR U-Net[22]0.97480.80390.98890.99010.8299
GT-DLA-dsHFF[23]0.97560.79970.99010.99080.8335
Ours0.97580.80420.98990.99110.8350
), ArticleFig(id=1319955278611731154, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=EN, label=Tab.2, caption=

Performance comparison results on the DRIVE dataset

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DatasetMethodAccSenSpeAUCF1
DRIVEResDO-UNet[24]0.95610.79850.9791—0.8229
DS2TUNet[25]0.96640.80710.9823—0.8195
ISAM-UNet[26]0.95650.82430.97580.98070.8284
PGU-Net[27]0.95720.79150.98140.98120.8250
GCC-UNet[28]0.95740.80320.98210.98130.8278
RCAR-UNet[29]0.95370.74870.9836—0.8047
RSF-UNet[30]0.95740.79950.98050.98160.8270
AttUKAN[31]0.95490.83930.97210.97950.8250
Ours0.97110.80260.98730.98840.8298
), ArticleFig(id=1319955278691422931, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=CN, label=表2, caption=

DRIVE数据集性能指标对比结果

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DatasetMethodAccSenSpeAUCF1
DRIVEResDO-UNet[24]0.95610.79850.9791—0.8229
DS2TUNet[25]0.96640.80710.9823—0.8195
ISAM-UNet[26]0.95650.82430.97580.98070.8284
PGU-Net[27]0.95720.79150.98140.98120.8250
GCC-UNet[28]0.95740.80320.98210.98130.8278
RCAR-UNet[29]0.95370.74870.9836—0.8047
RSF-UNet[30]0.95740.79950.98050.98160.8270
AttUKAN[31]0.95490.83930.97210.97950.8250
Ours0.97110.80260.98730.98840.8298
), ArticleFig(id=1319955278762726100, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=EN, label=Tab.3, caption=

Performance comparison results on the CHASE_DB1 dataset

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DatasetMethodAccSenSpeAUCF1
CHASE_DB1ResDO-UNet[24]0.96720.80200.9794—0.8236
DS2TUNet[25]0.97410.81010.9869—0.8362
ISAM-UNet[26]0.96670.77790.99000.98880.8372
PGU-Net[27]0.96580.80510.98170.98570.8099
GCC-UNet[28]0.96590.81230.98150.98500.8086
RCAR-UNet[29]0.95660.74750.9798—0.7470
RSF-UNet[30]0.96720.81260.98260.98740.8179
AttUKAN[31]0.96310.80610.98110.98210.8134
Ours0.97620.82190.98660.99010.8136
), ArticleFig(id=1319955280453030613, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=CN, label=表3, caption=

CHASE_DB1数据集性能指标对比结果

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DatasetMethodAccSenSpeAUCF1
CHASE_DB1ResDO-UNet[24]0.96720.80200.9794—0.8236
DS2TUNet[25]0.97410.81010.9869—0.8362
ISAM-UNet[26]0.96670.77790.99000.98880.8372
PGU-Net[27]0.96580.80510.98170.98570.8099
GCC-UNet[28]0.96590.81230.98150.98500.8086
RCAR-UNet[29]0.95660.74750.9798—0.7470
RSF-UNet[30]0.96720.81260.98260.98740.8179
AttUKAN[31]0.96310.80610.98110.98210.8134
Ours0.97620.82190.98660.99010.8136
), ArticleFig(id=1319955280566276822, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=EN, label=Tab.4, caption=

Performance comparison results on the STARE dataset

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DatasetMethodAccSenSpeAUCF1
STAREResDO-UNet[24]0.95670.79630.9792—0.8172
ISAM-UNet[26]0.96600.78110.98800.98640.8298
PGU-Net[27]0.96540.73680.99010.98620.8062
GCC-UNet[28]0.96580.78060.98770.98560.8282
RCAR-UNet[29]0.95940.69790.9905—0.7850
RSF-UNet[30]0.97190.80020.98820.98990.8318
AttUKAN[31]0.96430.76880.98680.97960.8114
Ours0.97580.80420.98990.99110.8350
), ArticleFig(id=1319955280645968599, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=CN, label=表4, caption=

STARE数据集性能指标对比结果

, figureFileSmall=null, figureFileBig=null, tableContent=
DatasetMethodAccSenSpeAUCF1
STAREResDO-UNet[24]0.95670.79630.9792—0.8172
ISAM-UNet[26]0.96600.78110.98800.98640.8298
PGU-Net[27]0.96540.73680.99010.98620.8062
GCC-UNet[28]0.96580.78060.98770.98560.8282
RCAR-UNet[29]0.95940.69790.9905—0.7850
RSF-UNet[30]0.97190.80020.98820.98990.8318
AttUKAN[31]0.96430.76880.98680.97960.8114
Ours0.97580.80420.98990.99110.8350
), ArticleFig(id=1319955280738243288, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=EN, label=Tab.5, caption=

Comparison of model parameters and floating-point computations

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MethodParams/MFLOGs/G
U-Net[8]34.5264.091
Attention U-Net[21]34.8774.160
FR U-Net[22]7.3753.682
GT-DLA-dsHFF[23]29.8197.407
Ours11.3603.901
), ArticleFig(id=1319955280813740761, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=CN, label=表5, caption=

模型参数量与浮点计算量对比

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MethodParams/MFLOGs/G
U-Net[8]34.5264.091
Attention U-Net[21]34.8774.160
FR U-Net[22]7.3753.682
GT-DLA-dsHFF[23]29.8197.407
Ours11.3603.901
), ArticleFig(id=1319955280889238234, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=EN, label=Tab.6, caption=

Ablation experiment results

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DatasetDCAGCTMFMAccSenSpeAUCF1
DRIVE0.97040.79540.98720.98710.8250
√0.97090.80040.98730.98820.8284
√0.97080.79760.98740.98800.8272
√0.97090.79430.98780.98810.8272
√√0.97100.80180.98720.98810.8289
√√0.97110.79630.98790.98830.8285
√√0.97100.79860.98760.98830.8287
√√√0.97110.80260.98730.98840.8298
CHASE_DB10.97470.80850.98590.98850.8015
√0.97540.80460.98690.98750.8050
√0.97590.82300.98620.99000.8118
√0.97580.80730.98710.98960.8078
√√0.97580.81860.98640.98980.8104
√√0.97600.80940.98720.99000.8096
√√0.97610.81510.98690.98990.8116
√√√0.97620.82190.98660.99010.8136
STARE0.97530.79240.99030.99030.8305
√0.97550.79060.99070.99070.8310
√0.97570.80220.98990.99090.8344
√0.97560.79390.99050.99060.8323
√√0.97550.79650.99020.99060.8324
√√0.97590.79450.99080.99100.8339
√√0.97560.80050.99000.99070.8335
√√√0.97580.80420.98990.99110.8350
), ArticleFig(id=1319955280973124315, tenantId=1146029695717560320, journalId=1278651732997652489, articleId=1319955243589292536, language=CN, label=表6, caption=

消融实验结果

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DatasetDCAGCTMFMAccSenSpeAUCF1
DRIVE0.97040.79540.98720.98710.8250
√0.97090.80040.98730.98820.8284
√0.97080.79760.98740.98800.8272
√0.97090.79430.98780.98810.8272
√√0.97100.80180.98720.98810.8289
√√0.97110.79630.98790.98830.8285
√√0.97100.79860.98760.98830.8287
√√√0.97110.80260.98730.98840.8298
CHASE_DB10.97470.80850.98590.98850.8015
√0.97540.80460.98690.98750.8050
√0.97590.82300.98620.99000.8118
√0.97580.80730.98710.98960.8078
√√0.97580.81860.98640.98980.8104
√√0.97600.80940.98720.99000.8096
√√0.97610.81510.98690.98990.8116
√√√0.97620.82190.98660.99010.8136
STARE0.97530.79240.99030.99030.8305
√0.97550.79060.99070.99070.8310
√0.97570.80220.98990.99090.8344
√0.97560.79390.99050.99060.8323
√√0.97550.79650.99020.99060.8324
√√0.97590.79450.99080.99100.8339
√√0.97560.80050.99000.99070.8335
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分组通道Transformer与调制融合的视网膜血管分割算法
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梁礼明 , 王灵亮 *, * , 蔡锦辉 , 王成斌
光电工程 | 研究论文 2026,53(3): 250264-1
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光电工程 |研究论文 2026 , 53 (3) : 250264 -1
分组通道Transformer与调制融合的视网膜血管分割算法
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梁礼明 , 王灵亮*, * , 蔡锦辉, 王成斌
作者信息
  • 江西理工大学电气工程与自动化学院,江西 赣州 341000
通讯作者:
王灵亮,
作者简介:

作者贡献

梁礼明:指导论文选题、论文修改;王灵亮:设计并完成实验,论文写作;蔡锦辉:研究资料的收集;王成斌:协助完成论文修改。

梁礼明(1967-),男,硕士,教授,硕士生导师,主要研究方向为机器学习、模式识别与图像处理等。E-mail:

王灵亮(2001-),男,硕士研究生,主要研究方向为医学图像处理。E-mail:

Grouped channel Transformer and modulation fusion retinal vessel segmentation algorithm
Liming Liang , Lingliang Wang , Jinhui Cai, Chengbin Wang
Affiliations
  • School of Electrical Engineering and Automation, Jiangxi University of Science and Technology, Ganzhou, Jiangxi 341000, China
  • Corresponding Author:
出版时间: 2026-03-25 doi: 10.12086/oee.2026.250264
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针对视网膜血管分割存在微细血管表征能力有限、复杂背景干扰和血管结构断裂等问题,提出一种分组通道Transformer与调制融合的视网膜血管分割算法。首先设计双维协同注意力模块于编码部分,增强微细血管的特征表达,有效提升血管分割能力。其次在编码端构建分组通道Transformer模块,旨在捕获血管之间的长程依赖关系,精确捕捉血管纹理信息。最后在解码端引入调制融合模块,有效融合编解码特征信息,抑制病灶区域噪声干扰。在数据集DRIVE、CHASE_DB1和STARE上进行实验,所提算法准确率分别为0.9711、0.9762和0.9758,灵敏度分别为0.8026、0.8219和0.8042,特异性分别为0.9873、0.9866和0.9899。该方法在整体分割效果方面优于其他算法,展现出更好的分割性能。

视网膜血管分割  /  分组通道Transformer  /  双维协同注意力  /  调制融合
Objective

Changes in retinal vascular morphology serve as crucial indicators for diagnosing various diseases, such as diabetic retinopathy, hypertension, and cataracts. Traditional diagnosis of retinal diseases primarily relies on manual assessment by clinicians, typically involving the analysis of retinal vascular curvature, width, and branching patterns based on imaging results from fundus examinations, optical coherence tomography, and fluorescein angiography. However, these imaging outcomes are susceptible to interference from factors such as illumination and noise, which increase the difficulty for clinicians in distinguishing retinal vessels from the background. Furthermore, inherent ocular structures like the optic cup and optic disc regions, as well as pathological alterations such as hard exudates, soft exudates, and the macular area, can also impede clinicians' judgment. Diagnostic results often vary subjectively among different physicians, potentially leading to misdiagnosis due to insufficient experience or fatigue. Automated retinal vessel segmentation technology can not only significantly reduce the time and effort required for manual annotation by clinicians and improve diagnostic efficiency but also minimize the impact of human factors to the greatest extent, providing more objective results to assist physicians in decision-making. Therefore, developing an accurate and automated retinal vessel segmentation technique holds substantial practical significance.

Methods

In the field of retinal vessel segmentation, existing methods can be broadly categorized into unsupervised and supervised approaches. Unsupervised methods do not rely on manually annotated data and primarily achieve segmentation by analyzing the morphological features of vessels. Common techniques include matched filtering-based, edge detection-based, and model-based methods. Matched filtering methods mainly utilize Gaussian kernel functions or their variants, which resemble the cross-sectional shape of blood vessels, to construct two-dimensional linear filter banks. These methods enhance tubular structures in retinal images through multi-scale and multi-directional filter responses, combined with thresholding for preliminary detection of vessel pixels. Edge detection-based methods capture boundary features between vessels and the background by calculating gradient changes in pixel intensity or using differential operators such as Canny and Sobel, often integrated with local or global thresholding strategies to extract vascular contours with continuous topological structures. Model-based methods rely on geometric or statistical models, such as active contour models, level set methods, or vascular tubular models, to mathematically describe vessel structure and distribution. They iteratively optimize energy functionals or probabilistic fitting processes to gradually evolve fine segmentation boundaries that adaptively conform to vessel morphology. However, such methods often depend on manually designed feature extraction pipelines, making it difficult to fully capture the complex topological structures of vessels, thereby resulting in limited segmentation performance. In contrast, supervised methods require expert-annotated data as training samples to achieve higher accuracy in vessel segmentation tasks. These methods can be further divided into traditional machine learning methods and deep learning methods. Traditional machine learning methods typically involve two steps: manual feature extraction and classification. Handcrafted features mainly include edge responses, wavelet responses, principal component information, and color intensity information. Based on the choice of classifier, they can be roughly categorized into k-nearest neighbors, random forests, support vector machines, and Gaussian mixture models. Traditional machine learning methods extract segmentation targets based on vascular features and fundus image characteristics. Compared to manual screening, they offer advantages such as shorter processing time and faster segmentation. However, their feature extraction process still requires manual design and cannot adequately represent the multi-scale structural features of vessels. With the continuous advancement and development of deep learning, it has gradually been adopted across various tasks in computer vision. In the field of medical image analysis, segmentation algorithms have been continuously updated and iterated. The introduction of various deep learning models and modules has further improved the accuracy and efficiency of fundus vessel segmentation algorithms. Compared to traditional machine learning methods, deep learning methods can automatically learn optimal features and achieve predictive modeling without human intervention, offering higher segmentation efficiency. Nevertheless, challenges such as limited representation of fine vessels, interference from complex backgrounds, and discontinuities in vessel structures remain. To address the aforementioned issues, this paper proposes a retinal vessel segmentation algorithm based on Grouped Channel Transformer and Modulated Fusion. First, a dual-dimensional cooperative attention module is designed in the encoder to enhance the distinguishability of vessel features and improve the model's accuracy in segmenting microvessels. Second, a Grouped Channel Transformer module is applied to construct a dual-encoder architecture, establishing global dependencies to effectively capture detailed vessel information. Finally, a Modulated Fusion module is introduced at the decoder to enhance feature fusion between the encoder and decoder, thereby improving the model's robustness against noise interference.

Results and Discussions

Experiments conducted on the DRIVE, CHASE_DB1, and STARE datasets demonstrate that the proposed algorithm achieves accuracy rates of 0.9711, 0.9762, and 0.9758, sensitivities of 0.8026, 0.8219, and 0.8042, and specificities of 0.9873, 0.9866, and 0.9899, respectively. The proposed method outperforms other algorithms in overall segmentation performance, demonstrating superior segmentation capability.

Conclusions

GTMF-Net demonstrates robust vessel segmentation capabilities on the DRIVE, CHASE_DB1, and STARE datasets. It achieves a favorable balance between model complexity and segmentation performance, offering both relatively low computational cost and high segmentation accuracy. However, the algorithm currently exhibits limitations in feature extraction within low-contrast regions, which can lead to mis-segmentation. Future work will focus on optimizing the algorithm's design to improve the accuracy of vessel identification in pathological areas.

retinal vessel segmentation  /  grouped channel Transformer  /  dual-dimension collaborative attention  /  modulation fusion
梁礼明, 王灵亮, 蔡锦辉, 王成斌. 分组通道Transformer与调制融合的视网膜血管分割算法. 光电工程, 2026 , 53 (3) : 250264 -1 . DOI: 10.12086/oee.2026.250264
Liming Liang, Lingliang Wang, Jinhui Cai, Chengbin Wang. Grouped channel Transformer and modulation fusion retinal vessel segmentation algorithm[J]. Opto-Electronic Engineering, 2026 , 53 (3) : 250264 -1 . DOI: 10.12086/oee.2026.250264
视网膜血管形态变化是多种疾病诊断的重要依据,如糖尿病视网膜病变、高血压及白内障等。在医疗诊断中,医生通常分析眼底图像中血管的直径和弯曲程度来辅助判断病情。然而,视网膜血管结构复杂多变,存在血管细小分支密集、图像对比度低及病变区域干扰等问题,给血管的精确分割带来了较大挑战。因此,研发一种高效、准确的视网膜血管分割技术至关重要[1-2]。
在视网膜血管分割领域,现有方法主要可分为无监督方法和有监督方法两大类。无监督方法不依赖人工标注数据,主要通过分析血管的形态特征实现分割,常见的方法包括基于匹配滤波[3]、基于边缘检测[4]和基于模型[5]等。然而,这类方法往往依赖人工构建的特征提取流程,难以全面捕捉血管复杂的拓扑结构,从而导致分割性能不高。相比之下,有监督方法则需专家提供的标注数据作为训练样本,在血管分割任务上实现更高的精度,此类方法可进一步分为传统机器学习方法与深度学习方法。传统机器学习方法包括支持向量机 (SVM)[6]和集成特征提取[7]等,然而其特征提取过程仍需人工设计,无法充分表征血管的多尺度结构特征。
随着深度学习技术的快速发展,视网膜血管分割领域迎来了较大突破。Ronneberger等[8]提出的U-Net架构通过其独特的编码器-解码器结构和跳跃连接机制,在血管分割中表现出色,但其存在特征层级间的语义差异,难以精确提取血管的细节信息。随后,研究者们对U-Net进行了多种改进。Getahun等[9]构建一种基于编解码架构的全尺度网络,通过结合残差块与自适应阈值算法提升血管分割的精度。Radha等[10]设计一种融合Gabor滤波与深度可分离卷积的U型网络,提升对血管特征的捕获能力。尽管上述算法在分割性能上有所提升,但仍存在特征提取不充分和全局上下文信息捕获能力有限等问题。Transformer[11]模型通过自注意力机制获取序列间的长程依赖性,在自然语言处理任务中取得较大成功。Dosovitskiy等[12]提出视觉Transformer (ViT)模型,通过将图像划分为块序列并应用自注意力机制,增强模型对全局依赖关系的建模能力,为视网膜血管分割任务提供新的解决方案。Wu等[13]构建一种跨尺度级联分层Transformer网络,通过在编码器中构建局部-全局跨尺度Transformer结构,并在解码器中引入位置感知Transformer机制,有效保留血管末端位置信息。Cui等[14]设计一种基于Transformer的联合注意力视网膜血管分割算法,通过多尺度特征融合与注意力机制捕捉上下文信息,增强血管特征权重。上述算法虽在血管分割任务中表现较好,但仍存在微小血管分割不足、血管边缘模糊和易受病变区域干扰等问题。
针对上述问题,本文提出一种分组通道Transformer与调制融合的视网膜血管分割算法 (grouped channel Transformer and modulation fusion network, GTMF-Net),主要工作:1)设计双维协同注意力模块于编码部分,增强血管特征的可辨识度,提升模型对微血管的分割精度;2)应用分组通道Transformer模块构建双编码结构,建立全局信息依赖,有效捕获血管细节信息;3)在解码端引入调制融合模块,增强编码部分和解码部分的特征融合,提升模型抗噪声干扰能力。
本文在U型网络结构的基础上,提出一种分组通道Transformer与调制融合的视网膜血管分割算法,其结构如图1所示。GTMF-Net由特征强化单元、双维协同注意力模块、分组通道Transformer模块和调制融合模块四部分组成。首先特征强化单元采用滑窗裁剪对眼底图像进行扩充,对其应用灰度变换、直方图均衡化等多种预处理方法以增强图像对比度。然后在编码端设计双维协同注意力模块,自适应调整模型对不同血管区域的关注程度,增强微细血管结构信息的权重。再后借助分组通道Transformer模块设计双编码架构,有效捕获上下文信息,实现血管纹理特征的精确提取。最后将调制融合模块置于解码端以充分融合多尺度特征,同时抑制图像中的噪声信息。
在视网膜血管分割任务中,由于眼底图像中血管形态复杂多变,且血管与背景的对比度低,导致微细血管分割较困难。Yu等[15]提出基于离散余弦变换 (DCT)的空间注意力模块,其对通道内各个空间位置分配不同权重,增强血管区域响应,实现模型对微血管信息的充分捕获。本文受文献[15]启发,设计一种双维协同注意力模块 (dual-dimensional collaborative attention module, DCA),旨在捕捉通道间和空间内的相互依赖关系,有效维持血管形态结构的完整性。其结构如图2所示。
DCA包括空间注意力 (spatial attention, SA)分支和通道注意力 (channel attention, CA)分支,其中SA分支通过对各个空间位置进行加权,抑制无关背景区域。CA分支通过调整各个通道的权重,使网络聚焦于血管特征。在SA分支中,首先对输入特征${{\boldsymbol{F}}_{{\text{in}}}}$应用离散余弦变换卷积操作,以提取完整的频率特征D。然后通过7×7卷积层来建模位置间的相互依赖,并使用Sigmoid激活函数得到空间注意力权重${{\boldsymbol{W}}_{\text{s}}}$。最后将权重${{\boldsymbol{W}}_{\text{s}}}$与输入特征图${{\boldsymbol{F}}_{{\text{in}}}}$进行相乘得到空间增强特征${{\boldsymbol{F}}_{\text{s}}}$。其数学表达式分别为
$ {\boldsymbol{D}} = {{Con}}{{{v}}_{{\text{DCT}}}}({{\boldsymbol{F}}_{{\text{in}}}}) \;,$
$ {{\boldsymbol{W}}_{\text{s}}} = \sigma ({{Con}}{{{v}}_{7 \times 7}}({\boldsymbol{D}}))\;, $
$ {{\boldsymbol{F}}_{\text{s}}} = {{\boldsymbol{F}}_{{\text{in}}}} \odot {{\boldsymbol{W}}_{\text{s}}} \;,$
式中:${{Con}}{{{v}}_{{\text{DCT}}}}$表示离散余弦变换卷积操作;${{Con}}{{{v}}_{7 \times 7}}$表示7×7卷积层;$\sigma $表示Sigmoid函数;$ \odot $表示相乘。在CA分支中,首先对输入特征${{\boldsymbol{F}}_{{\text{in}}}}$应用平均池化操作和1×1卷积操作,并通过Sigmoid函数得到通道注意力权重。然后将通道注意力权重${{\boldsymbol{W}}_{\text{c}}}$与特征${{\boldsymbol{F}}_{\text{s}}}$进行相乘,以突出血管区域。最后将上述结果与输入特征${{\boldsymbol{F}}_{{\text{in}}}}$相加,得到输出特征${{\boldsymbol{F}}_{{\text{out}}}}$。其数学表达式分别为
$ {{\boldsymbol{W}}_{\text{c}}} = \sigma ({{Con}}{{{v}}_{1 \times 1}}({{AVGPool}}({{\boldsymbol{F}}_{{\text{in}}}}))) \;,$
$ {{\boldsymbol{F}}_{{\text{out}}}} = ({{\boldsymbol{F}}_{\text{s}}} \odot {{\boldsymbol{W}}_{\text{c}}}) + {{\boldsymbol{F}}_{{\text{in}}}}\;, $
式中:AVGPool表示平均池化操作;${{Con}}{{{v}}_{1 \times 1}}$表示1×1卷积操作。
由于传统卷积网络侧重于局部区域特征的提取,难以捕捉长程依赖关系。Li等[16]提出分组通道自注意力模块,其将输入特征图按通道维度划分为若干组,在各组内进行通道注意力计算,有效捕获全局上下文信息,增强模型对血管语义信息的表征能力。本文受文献[16]启发,并结合ViT,提出分组通道Transformer模块 (grouped channel Transformer module, GCT),其结构如图3所示。
GCT模块由分组通道自注意力模块 (grouped channel-wise self-attention module, GCSA)、层归一化 (layer norm, LN)和多层感知机 (multilayer perceptron, MLP)组成。其过程分别表示如下:
$ {{\boldsymbol{I}}_{{\text{mid}}}} = {{GCSA}}({{LN}}({{\boldsymbol{I}}_{{\text{in}}}})) + {{\boldsymbol{I}}_{{\text{in}}}}\;, $
$ {{\boldsymbol{I}}_{{\text{out}}}} = {{MLP}}({{LN}}({{\boldsymbol{I}}_{{\text{mid}}}})) + {{\boldsymbol{I}}_{{\text{mid}}}} \;,$
式中:${{\boldsymbol{I}}_{{\text{in}}}}$表示输入;${{\boldsymbol{I}}_{{\text{out}}}}$表示输出。
GCSA能实现对全局信息的有效建模,增强模型对微血管的识别能力,其结构如图4所示。首先给定输入特征${\boldsymbol{X}} \in {R^{C \times H{{ \times }}W}}$,应用线性投影操作和深度卷积操作,得到查询矩阵Q、键矩阵K和值矩阵V。然后将上述特征沿通道维度划分为G个子组并重塑为${{\boldsymbol{Q}}_{\text{g}}}$、${{\boldsymbol{K}}_{\text{g}}}$和${{\boldsymbol{V}}_{\text{g}}}$。其次将${{\boldsymbol{Q}}_{\text{g}}}$和${{\boldsymbol{K}}_{\text{g}}}$进行点乘和缩放,并经过Softmax函数归一化后得到注意力矩阵${{\boldsymbol{A}}_{\text{g}}}$。最后利用矩阵${{\boldsymbol{A}}_{\text{g}}}$对${{\boldsymbol{V}}_{\text{g}}}$进行加权求和,将加权结果进行拼接及线性投影操作得到输出特征Y。其在数学上分别表示如下:
$ ({\boldsymbol{Q}},{\boldsymbol{K}},{\boldsymbol{V}}) = {{DCon}}{{{v}}_{{{{{d}}=2}}}}(\varOmega ({\boldsymbol{X}}))\;, $
$ ({{\boldsymbol{Q}}_{\text{g}}},{{\boldsymbol{K}}_{\text{g}}},{{\boldsymbol{V}}_{\text{g}}}) = {{GroupReshape}}_{\text{g}}({\boldsymbol{Q}},{\boldsymbol{K}},{\boldsymbol{V}})\;, $
$ {{\boldsymbol{A}}_{\text{g}}} = {{Softmax}}\left( {\dfrac{{{{\boldsymbol{Q}}_{\text{g}}}{{\boldsymbol{K}}_{\text{g}}}}}{t}} \right)\;, $
$ {\boldsymbol{Y}} = \varOmega ({{Concat}}({{\boldsymbol{A}}_1}{{\boldsymbol{V}}_1},{{\boldsymbol{A}}_2}{{\boldsymbol{V}}_2}, \cdots ,{{\boldsymbol{A}}_{\text{g}}}{{\boldsymbol{V}}_{\text{g}}})) \;,$
式中:${{\boldsymbol{Q}}_{\text{g}}} \in {{\bf{R}}^{\tfrac{C}{G} \times HW}}$、${{\boldsymbol{K}}_{\text{g}}} \in {{\bf{R}}^{HW \times \tfrac{C}{G}}}$、${{\boldsymbol{V}}_{\text{g}}} \in {{\bf{R}}^{HW \times \tfrac{C}{G}}}$;$\varOmega $表示线性投影操作;${{DCon}}{{{v}}_{{{{{d}}=2}}}}$表示膨胀率为2的深度卷积;$ {{GroupReshap}}{{{e}}_{\text{g}}} $表示分组与形状变换;t表示可学习的参数。
在原始U-Net架构中,编码路径与解码路径通过跳跃连接直接耦合,这种方式虽能传递空间细节信息,但编码端提取的低级特征与解码端提取的高级特征在语义上存在差异。为了将编解码特征充分融合,提高模型对血管信息的捕获能力并抑制背景噪声干扰,本文引入调制融合模块 (modulation fusion module, MFM)[17],如图5所示。
首先将编码器特征${{\boldsymbol{F}}_{{\text{enc}}}}$与解码器特征${{\boldsymbol{F}}_{{\text{dec}}}}{\text{ }}$进行相加,得到融合特征${{\boldsymbol{F}}_{{\text{sum}}}}{\text{ }}$。然后将特征${{\boldsymbol{F}}_{{\text{sum}}}}{\text{ }}$通过全局平均池化操作、多层感知机 (MLP)和Softmax归一化运算,以生成通道注意力权重${{\boldsymbol{A}}_{{\text{attn}}}}{\text{ }}$。再后将权重${{\boldsymbol{A}}_{{\text{attn}}}}{\text{ }}$按通道维度分别与特征${{\boldsymbol{F}}_{{\text{enc}}}}$和特征${{\boldsymbol{F}}_{{\text{dec}}}}{\text{ }}$相乘,并将上述结果相加得到特征${{\boldsymbol{F}}_{{\text{fus}}}}{\text{ }}$,以增强血管特征的语义表达。最后将特征${{\boldsymbol{F}}_{{\text{fus}}}}{\text{ }}$与特征${{\boldsymbol{F}}_{{\text{enc}}}}$进行拼接,对拼接结果应用卷积操作得到输出特征${{\boldsymbol{F}}_{{\text{out}}}}{\text{ }}$。其在数学上分别表示为
$ {{\boldsymbol{F}}_{{\text{sum}}}} = {{\boldsymbol{F}}_{{\text{enc}}}} \oplus {{\boldsymbol{F}}_{{\text{dec}}}} \;,$
$ {{\boldsymbol{A}}_{{\text{attn}}}} = {{Softmax}}\left( {{{MLP}}\left( {{{GAP}}({{\boldsymbol{F}}_{{\text{sum}}}})} \right)} \right)\;, $
$ {{\boldsymbol{F}}_{{\text{fus}}}} = ({{\boldsymbol{A}}_{{\text{attn}}}} \otimes {{\boldsymbol{F}}_{{\text{enc}}}}) \oplus ({{\boldsymbol{A}}_{{\text{attn}}}} \otimes {{\boldsymbol{F}}_{{\text{dec}}}})\;, $
$ {{\boldsymbol{F}}_{{\text{out}}}} = {{Conv}}\left( {{{Concat}}({{\boldsymbol{F}}_{{\text{fus}}}},{{\boldsymbol{F}}_{{\text{enc}}}})} \right) \;,$
式中:GAP表示全局平均池化操作;Conv表示卷积操作;$ \oplus $表示相加;$ \otimes $表示相乘。
本文实验在64位Windows 11操作系统环境下进行,硬件配置为CPU Intel (R) Core (TM) i7-14650HX,运行内存16 GB,GPU NVIDIA GeForce RTX 4060,显存8 GB。算法基于PyTorch框架搭建,采用Python编程语言实现。在训练阶段,模型通过Adam优化器更新参数,使用交叉熵损失函数对训练过程进行监督。学习率设为0.0005,总训练轮次为20,批次大小固定为6。为平衡模型收敛效率与过拟合风险,引入余弦退火策略动态调整学习率,并设置早停机制,若连续10个训练周期未产生更优权重则自动终止训练。
本文采用 DRIVE[18]、CHASE_DB1[19]和STARE[20]三个公开视网膜图像数据集进行算法验证。DRIVE数据集包含40幅彩色眼底图像,每幅图像的分辨率为565 pixel×584 pixel,其中20幅用于训练,另外20幅用于测试。CHASE_DB1数据集采集自14名学龄儿童的双眼,共28幅分辨率为999 pixel×960 pixel的彩色视网膜图像,实验中选取前20幅作为训练集,其余8幅作为测试集。STARE数据集包含20幅605 pixel×700 pixel的彩色眼底图像,因官方未提供训练集和测试集划分,故采用五折交叉验证法进行实验评估。上述3个数据集中,每幅视网膜图像均附有两位专家独立标注的金标准,本文选取第一位专家的标注结果作为基准参考。
由于原始眼底图像普遍存在亮度不均、对比度低及噪声干扰等问题,上述因素会影响模型的分割性能,故对数据集进行预处理。如图6所示,首先对原始图像进行灰度转换,降低计算冗余并突出血管形态结构。然后通过标准化操作调整像素分布范围,缓解亮度分布不均对图像质量的影响。再后应用限制对比度直方图均衡化,增强血管纹理与背景之间的局部对比度。最后采用伽马校正对整体亮度分布进行非线性调整,优化微细血管在较暗区域的显现效果。考虑到公开数据集样本量有限,为缓解训练过程中的过拟合风险,对数据集进行扩充处理。具体来说,采用64×64大小的滑动窗口从预处理后的原始图像及对应的金标准图像中提取10000个图像块。
为了客观评估模型的性能,本文选取准确率 (Acc)、灵敏度 (Sen)、特异性 (Spe)、F1分数 (F1)和ROC曲线下面积 (AUC)作为评价指标。其中,准确率表示正确分割的血管与背景像素之和占总像素的比例;灵敏度表示正确分割的血管像素占实际血管像数的比例;特异性表示正确分割的非血管像素占实际背景像素的比例;F1分数综合评估模型对血管结构的捕获能力。其计算公式分别为
$ {{Acc}} = \dfrac{{TP + TN}}{{TP + TN + FP + FN}}\;, $
$ {{S en}} = \dfrac{{TP}}{{TP + FN}} \;,$
$ {{S pe}} = \dfrac{{TN}}{{TN + FP}} \;,$
$ {{F_1}} = \dfrac{{2TP}}{{2TP + FP + FN}} \;,$
式中:TP为真阳性;TN为真阴性;FP为假阳性;FN为假阴性。
为了验证本文算法的性能优势,在相同实验环境下,将GTMF-Net分割结果和其余四种算法分割结果进行比较,包括U-Net[8]、Attention U-Net[21]、FR U-Net[22]和GT-DLA-dsHFF[23]。U-Net是基准模型,Attention U-Net是在U-Net基础上引入注意力机制的经典改进模型,FR U-Net是近年来分割性能较好的模型,GT-DLA-dsHFF是近年来将Transformer结构与U-Net框架相结合的先进模型。如图7所示,其中第一、二行为DRIVE数据集中眼底图像,第三、四行为CHASE_DB1数据集中眼底图像,第五、六行为STARE数据集中眼底图像。
观察DRIVE数据集第一行分割结果可知,U-Net无法有效提取交叉处微细血管的形态特征,导致其丢失较多的血管信息,Attention U-Net分割细小血管时出现血管分割不足问题,FR U-Net和GT-DLA-dsHFF在分支血管末端处存在血管断裂现象,而GTMF-Net在微细血管的分割上取得良好的效果。观察DRIVE数据集第二行分割结果可知,由于视网膜边界区域的背景与前景对比度低,U-Net和Attention U-Net出现血管识别不充分问题,FR U-Net、GT-DLA-dsHFF和GTMF-Net相对较好地保留血管信息,但FR U-Net和GT-DLA-dsHFF存在主血管轮廓不清晰现象。观察CHASE_DB1数据集第三和第四行分割结果可知,U-Net、FR U-Net和GT-DLA-dsHFF将病灶区域错误分类为血管,Attention U-Net出现主血管像素缺失问题,而GTMF-Net能够准确区分背景与血管,较完整地分割出主血管。观察STARE数据集第五行分割结果可知,由于视盘区域周围光照不均匀,U-Net、Attention U-Net和FR U-Net出现微血管不连续问题,GT-DLA-dsHFF和GTMF-Net存在问题相对较小。观察STARE数据集第六行分割结果可知,受中央视网膜动脉阻塞病变影响,U-Net、Attention U-Net和FR U-Net存在血管分割模糊现象,GT-DLA-dsHFF出现血管末梢断连问题,GTMF-Net分割出的血管结构更加清晰,表明GTMF-Net在视网膜图像分割中具有更优的鲁棒性。
为了更深入地体现所提算法的优势,图8展示了不同算法在DRIVE、CHASE_DB1和STARE数据集上的局部放大细节,其中图8第一、第二和第三行细节分别源自图7第一、第四和第六行的标注区域。
由第一行的分割细节图可知,U-Net出现分支处细小血管信息缺失问题较为严重,Attention U-Net、FR U-Net和GT-DLA-dsHFF存在血管结构断连现象,GTMF-Net则较好地保持血管结构的完整性。由第二行的分割细节图可知,U-Net、FR U-Net和GT-DLA-dsHFF受病灶区域影响,将病理信息分割为血管,Attention U-Net出现主血管分割不完全问题,而GTMF-Net能较清晰地分割出主血管结构。由第三行的分割细节图可知,U-Net、Attention U-Net和FR U-Net在血管交叉区域存在分割断裂及微细血管像素缺失问题,GT-DLA-dsHFF和GTMF-Net相对较好地保留交叉处的血管信息,但GT-DLA-dsHFF存在微细血管分割不足现象,相比之下,GTMF-Net能够更准确地分割出血管轮廓,分割结果与金标准基本吻合。实验表明,GTMF-Net在DRIVE、CHASE_DB1和STARE数据集上实现对血管的准确识别,相较其余对比算法具有更优的分割性能。
为了定量评估所提算法的性能,在相同实验环境下,将GTMF-Net与文献[8]及文献[21-23]在DRIVE、CHASE_DB1和STARE这3个数据集上进行比较,性能指标对比结果如表1所示。
观察表1可知,在DRIVE数据集上,Attention U-Net利用注意力门机制动态调整特征响应,其特异性达到最优值,但GTMF-Net的准确率、灵敏度、AUC值和F1分数均比其高,表明Attention U-Net虽然能有效识别非血管区域,但其对血管和背景的整体判别效果有待提高。在CHASE_DB1数据集上,GT-DLA-dsHFF利用全局Transformer建模像素间长距离依赖关系,其在特异性上高于GTMF-Net,但GTMF-Net其余指标均为最优,其中灵敏度较GT-DLA-dsHFF提升1.44%,表明GTMF-Net捕获微细血管的能力较强。在STARE数据集上,除FR U-Net算法外,其余算法的特异性较GTMF-Net均有提升,原因是GTMF-Net利用分组通道自注意力机制有效提升微血管分割能力,但会导致模型将一些背景区域识别为血管,进而影响特异性的表现;但GTMF-Net在准确率、灵敏度、AUC值和F1分数等指标上均取得最优值,表明GTMF-Net在血管分割的综合表现上更为出色。
为了直观体现所提算法的性能,图9和图10展示了上述5个模型在DRIVE和CHASE_DB1数据集上的ROC曲线和PR曲线对比图。由图9和图10可知,GTMF-Net的ROC曲线更接近坐标系的左上区域,PR曲线更接近坐标系的右上区域,AUC (ROC)值和AUC (PR)值均为最高,表明GTMF-Net能够更全面地识别血管结构,较其余对比算法分割性能更优。
为了进一步验证所提算法的先进性,将GTMF-Net与近年其他先进算法[24-31]在Acc、Sen、Spe、AUC和F1这5个指标上进行对比,如表2~表4所示,其数据均引自原文献。
由表2可知,在DRIVE数据集上,DS2TUNet通过Transformer整合局部和全局特征,并结合深度监督机制实现多层级监督,其灵敏度高于GTMF-Net,但其余指标均低于GTMF-Net。AttUKAN利用注意力门机制选择性增强血管区域特征,并结合标签引导的像素级对比损失函数强化前景血管像素的判别能力,其灵敏度达到最优值,但GTMF-Net其余指标均比其高。此外,GTMF-Net的准确率和AUC值均优于其余对比算法,表明GTMF-Net在辨别血管像素和背景像素方面具有更好的性能。由表3可知,在CHASE_DB1数据集上,ISAM-UNet通过深度融合多尺度上下文信息和优化特征提取过程,有效减少血管特征损失,其特异性和F1分数高于GTMF-Net,但GTMF-Net的准确率、灵敏度和AUC值分别比ISAM-UNet提升0.95%、4.4%和0.13%,表明GTMF-Net能够增强复杂背景区域中血管的识别能力,精确提取血管细节特征。由表4可知,在STARE数据集上,RCAR-UNet提出一种粗糙通道注意力机制,自适应校准特征通道,有效抑制无关区域的特征响应,其特异性最高,较GTMF-Net提升0.06%,但GTMF-Net除特异性外,其余指标均为各项的最优值,表明GTMF-Net在血管分割任务上实现了更高的精度,综合性能优于其余先进算法。综合表2~表4可知,GTMF-Net泛化能力强,分割性能优越。
表5展示了GTMF-Net与其他几种模型在参数量和浮点计算量方面的对比。结果表明,与U-Net、Attention U-Net和GT-DLA-dsHFF相比,GTMF-Net在保持相近浮点计算量的同时,其参数量仅为11.360 M,显著低于上述模型。尽管FR U-Net的参数量略低于GTMF-Net,但其性能指标和分割效果均不及GTMF-Net。综上所述,GTMF-Net在模型复杂度与分割性能之间取得较好平衡,是一种具备较低计算开销与较高精度的分割模型。
为证明本文算法各模块的有效性,在DRIVE、CHASE_DB1和STARE数据集上进行消融实验,其结果如表6所示。其中,每个数据集的首行对应原始U-Net模型的实验结果。
观察表6可知,当DCA单独加入或与其他模块组合加入时,三个数据集中准确率和F1分数均有一定的提升,表明DCA能够引导网络聚焦于血管相关区域,有效提升分割精度。当GCT单独加入时,CHASE_DB1数据集中灵敏度达到最优;当GCT与DCA组合加入时,DRIVE和STARE数据集中灵敏度较仅加入DCA时进一步提升,表明GCT能够有效增强模型对微细血管的捕获能力。当MFM单独加入时,三个数据集中准确率、特异性和AUC值均有所提升;当MFM与DCA组合加入时,三个数据集中特异性均达到最优,且在DRIVE和STARE数据集中准确率达到最高,表明MFM能够抑制背景噪声干扰,提高模型对血管信息的捕获能力。完整的GTMF-Net模型在三个数据集中特异性均未达到最高,其原因在于,GCT利用了分组通道自注意力机制,该机制通过在通道维度上对权重进行重分配,强化局部血管特征响应。虽其有助于提升模型对微细血管特征的提取能力,但当特征分布中存在噪声或背景纹理与血管特征较为相似时,模型可能会错误地放大这些无关区域的响应,将一些背景区域识别为血管,进而影响特异性的表现。但完整的GTMF-Net模型除特异性外其余指标均表现较好,整体性能最优。综上所述,GTMF-Net有效且合理。
针对视网膜血管分割存在复杂背景干扰、微细血管分割不足和血管结构断裂等问题,本文提出分组通道Transformer与调制融合的视网膜血管分割算法。首先,在算法的编码端设计双维协同注意力模块,建立通道间和空间位置上的依赖关系,有效保留血管形态结构信息;其次,应用分组通道Transformer模块构建双编码结构,建立血管像素间的全局语义关联,促进微细血管局部信息的充分捕获;最后,在算法的解码端引入调制融合模块,保证血管结构的连续性,降低无关背景区域噪声的影响。实验结果表明,GTMF-Net在DRIVE、CHASE_DB1和STARE数据集上展现出良好的血管分割能力,但算法在低对比度区域的特征提取能力有限,导致其仍存在误分割现象,后续研究将优化算法设计,提升病变区域的血管识别精度。

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doi: 10.12086/oee.2026.250264
  • 接收时间:2025-09-04
  • 首发时间:2026-10-22
  • 出版时间:2026-03-25
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  • 收稿日期:2025-09-04
  • 修回日期:2025-11-12
  • 录用日期:2025-11-14
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    江西理工大学电气工程与自动化学院,江西 赣州 341000

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