Image denoising method in low-dose CT projection domain based on improved U-net
A CT image, low-dose technology, applied in the field of image processing, can solve problems such as inaccurate noise recognition and loss of image details, and achieve the effects of improving image quality, improving structure, and preventing important structural information from being saved.
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Embodiment 1
[0036] An embodiment of the present invention provides an improved U-net-based image denoising method in the low-dose CT projection domain, including:
[0037] S101: Based on the noise characteristics of the CT image projection domain, create matched normal dose and low dose projection image datasets;
[0038] S102: Use the inception module to replace the convolutional layer part of the U-net network encoder;
[0039] S103: further optimize, train and test the U-net network structure;
[0040] S104: Input the low-dose CT projection data that needs to be de-noised into the trained U-net network, obtain the de-noised projection data, and perform filter back-projection reconstruction on the de-noised projection data.
[0041] Considering that the source of noise is located in the projection domain, it may be easier to study low-dose CT in the region closest to the noise, and the streak artifact appears as scattered noise in the projection domain. The low-dose CT image denoising...
Embodiment 2
[0044]On the basis of the above embodiment, the embodiment of the present invention provides another method for image denoising in the low-dose CT projection domain based on the improved U-net, including the following steps:
[0045] S201 : generating fan beam geometric projection data by using the Siddon ray driving method from the CT image of normal dose;
[0046] S202: When the light source is a monochromatic X-ray, approximate the noise in the low-dose CT projection by the Poisson noise shown in formula (1):
[0047] Z i ~Poisson{Z 0i exp(-s i )+r i}i=1,2...I(1)
[0048] Among them, Z i is the number of incident photons along the i-th X-ray path, Z 0i is the initial incident intensity of X-ray, r i is the background electronic noise along the i-th X-ray path, s i is the line integral of the attenuation coefficient;
[0049] As an implementation, Z 0i is evenly set to 10 5 .
[0050] S203: Add the noise obtained by the simulation in step S202 to the projection d...
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