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    PET Reconstruction With an Anatomical MRI Prior Using Parallel Level Sets.

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    The combination of positron emission tomography (PET) and magnetic resonance imaging (MRI) offers unique possibilities. In this paper we aim to exploit the high spatial resolution of MRI to enhance the reconstruction of simultaneously acquired PET data. We propose a new prior to incorporate structural side information into a maximum a posteriori reconstruction. The new prior combines the strengths of previously proposed priors for the same problem: it is very efficient in guiding the reconstruction at edges available from the side information and it reduces locally to edge-preserving total variation in the degenerate case when no structural information is available. In addition, this prior is segmentation-free, convex and no a priori assumptions are made on the correlation of edge directions of the PET and MRI images. We present results for a simulated brain phantom and for real data acquired by the Siemens Biograph mMR for a hardware phantom and a clinical scan. The results from simulations show that the new prior has a better trade-off between enhancing common anatomical boundaries and preserving unique features than several other priors. Moreover, it has a better mean absolute bias-to-mean standard deviation trade-off and yields reconstructions with superior relative l2-error and structural similarity index. These findings are underpinned by the real data results from a hardware phantom and a clinical patient confirming that the new prior is capable of promoting well-defined anatomical boundaries.This research was funded by the EPSRC (EP/K005278/1) and EP/H046410/1 and supported by the National Institute for Health Research University College London Hospitals Biomedical Research Centre. M.J.E was supported by an IMPACT studentship funded jointly by Siemens and the UCL Faculty of Engineering Sciences. K.T. and D.A. are partially supported by the EPSRC grant EP/M022587/1.This is the author accepted manuscript. The final version is available from IEEE via http://dx.doi.org/10.1109/TMI.2016.254960

    ํ•ด๋ถ€ํ•™์  ์œ ๋„ PET ์žฌ๊ตฌ์„ฑ: ๋งค๋„๋Ÿฝ์ง€ ์•Š์€ ์‚ฌ์ „ ํ•จ์ˆ˜๋ถ€ํ„ฐ ๋”ฅ๋Ÿฌ๋‹ ์ ‘๊ทผ๊นŒ์ง€

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    ํ•™์œ„๋…ผ๋ฌธ (๋ฐ•์‚ฌ) -- ์„œ์šธ๋Œ€ํ•™๊ต ๋Œ€ํ•™์› : ์˜๊ณผ๋Œ€ํ•™ ์˜๊ณผํ•™๊ณผ, 2021. 2. ์ด์žฌ์„ฑ.Advances in simultaneous positron emission tomography/magnetic resonance imaging (PET/MRI) technology have led to an active investigation of the anatomy-guided regularized PET image reconstruction algorithm based on MR images. Among the various priors proposed for anatomy-guided regularized PET image reconstruction, Bowsherโ€™s method based on second-order smoothing priors sometimes suffers from over-smoothing of detailed structures. Therefore, in this study, we propose a Bowsher prior based on the l1 norm and an iteratively reweighting scheme to overcome the limitation of the original Bowsher method. In addition, we have derived a closed solution for iterative image reconstruction based on this non-smooth prior. A comparison study between the original l2 and proposed l1 Bowsher priors were conducted using computer simulation and real human data. In the simulation and real data application, small lesions with abnormal PET uptake were better detected by the proposed l1 Bowsher prior methods than the original Bowsher prior. The original l2 Bowsher leads to a decreased PET intensity in small lesions when there is no clear separation between the lesions and surrounding tissue in the anatomical prior. However, the proposed l1 Bowsher prior methods showed better contrast between the tumors and surrounding tissues owing to the intrinsic edge-preserving property of the prior which is attributed to the sparseness induced by l1 norm, especially in the iterative reweighting scheme. Besides, the proposed methods demonstrated lower bias and less hyper-parameter dependency on PET intensity estimation in the regions with matched anatomical boundaries in PET and MRI. Moreover, based on the formulation of l1 Bowsher prior, the unrolled network containing the conventional maximum-likelihood expectation-maximization (ML-EM) module was also proposed. The convolutional layers successfully learned the distribution of anatomically-guided PET images and the EM module corrected the intermediate outputs by comparing them with sinograms. The proposed unrolled network showed better performance than ordinary U-Net, where the regional uptake is less biased and deviated. Therefore, these methods will help improve the PET image quality based on the anatomical side information.์–‘์ „์ž๋ฐฉ์ถœ๋‹จ์ธต์ดฌ์˜ / ์ž๊ธฐ๊ณต๋ช…์˜์ƒ (PET/MRI) ๋™์‹œ ํš๋“ ๊ธฐ์ˆ ์˜ ๋ฐœ์ „์œผ๋กœ MR ์˜์ƒ์„ ๊ธฐ๋ฐ˜์œผ๋กœ ํ•œ ํ•ด๋ถ€ํ•™์  ์‚ฌ์ „ ํ•จ์ˆ˜๋กœ ์ •๊ทœํ™” ๋œ PET ์˜์ƒ ์žฌ๊ตฌ์„ฑ ์•Œ๊ณ ๋ฆฌ์ฆ˜์— ๋Œ€ํ•œ ์‹ฌ๋„์žˆ๋Š” ํ‰๊ฐ€๊ฐ€ ์ด๋ฃจ์–ด์กŒ๋‹ค. ํ•ด๋ถ€ํ•™ ๊ธฐ๋ฐ˜์œผ๋กœ ์ •๊ทœํ™” ๋œ PET ์ด๋ฏธ์ง€ ์žฌ๊ตฌ์„ฑ์„ ์œ„ํ•ด ์ œ์•ˆ ๋œ ๋‹ค์–‘ํ•œ ์‚ฌ์ „ ์ค‘ 2์ฐจ ํ‰ํ™œํ™” ์‚ฌ์ „ํ•จ์ˆ˜์— ๊ธฐ๋ฐ˜ํ•œ Bowsher์˜ ๋ฐฉ๋ฒ•์€ ๋•Œ๋•Œ๋กœ ์„ธ๋ถ€ ๊ตฌ์กฐ์˜ ๊ณผ๋„ํ•œ ํ‰ํ™œํ™”๋กœ ์–ด๋ ค์›€์„ ๊ฒช๋Š”๋‹ค. ๋”ฐ๋ผ์„œ ๋ณธ ์—ฐ๊ตฌ์—์„œ๋Š” ์›๋ž˜ Bowsher ๋ฐฉ๋ฒ•์˜ ํ•œ๊ณ„๋ฅผ ๊ทน๋ณตํ•˜๊ธฐ ์œ„ํ•ด l1 norm์— ๊ธฐ๋ฐ˜ํ•œ Bowsher ์‚ฌ์ „ ํ•จ์ˆ˜์™€ ๋ฐ˜๋ณต์ ์ธ ์žฌ๊ฐ€์ค‘์น˜ ๊ธฐ๋ฒ•์„ ์ œ์•ˆํ•œ๋‹ค. ๋˜ํ•œ, ์šฐ๋ฆฌ๋Š” ์ด ๋งค๋„๋Ÿฝ์ง€ ์•Š์€ ์‚ฌ์ „ ํ•จ์ˆ˜๋ฅผ ์ด์šฉํ•œ ๋ฐ˜๋ณต์  ์ด๋ฏธ์ง€ ์žฌ๊ตฌ์„ฑ์— ๋Œ€ํ•ด ๋‹ซํžŒ ํ•ด๋ฅผ ๋„์ถœํ–ˆ๋‹ค. ์›๋ž˜ l2์™€ ์ œ์•ˆ ๋œ l1 Bowsher ์‚ฌ์ „ ํ•จ์ˆ˜ ๊ฐ„์˜ ๋น„๊ต ์—ฐ๊ตฌ๋Š” ์ปดํ“จํ„ฐ ์‹œ๋ฎฌ๋ ˆ์ด์…˜๊ณผ ์‹ค์ œ ๋ฐ์ดํ„ฐ๋ฅผ ์‚ฌ์šฉํ•˜์—ฌ ์ˆ˜ํ–‰๋˜์—ˆ๋‹ค. ์‹œ๋ฎฌ๋ ˆ์ด์…˜ ๋ฐ ์‹ค์ œ ๋ฐ์ดํ„ฐ์—์„œ ๋น„์ •์ƒ์ ์ธ PET ํก์ˆ˜๋ฅผ ๊ฐ€์ง„ ์ž‘์€ ๋ณ‘๋ณ€์€ ์›๋ž˜ Bowsher ์ด์ „๋ณด๋‹ค ์ œ์•ˆ ๋œ l1 Bowsher ์‚ฌ์ „ ๋ฐฉ๋ฒ•์œผ๋กœ ๋” ์ž˜ ๊ฐ์ง€๋˜์—ˆ๋‹ค. ์›๋ž˜์˜ l2 Bowsher๋Š” ํ•ด๋ถ€ํ•™์  ์˜์ƒ์—์„œ ๋ณ‘๋ณ€๊ณผ ์ฃผ๋ณ€ ์กฐ์ง ์‚ฌ์ด์— ๋ช…ํ™•ํ•œ ๋ถ„๋ฆฌ๊ฐ€ ์—†์„ ๋•Œ ์ž‘์€ ๋ณ‘๋ณ€์—์„œ์˜ PET ๊ฐ•๋„๋ฅผ ๊ฐ์†Œ์‹œํ‚จ๋‹ค. ๊ทธ๋Ÿฌ๋‚˜ ์ œ์•ˆ ๋œ l1 Bowsher ์‚ฌ์ „ ๋ฐฉ๋ฒ•์€ ํŠนํžˆ ๋ฐ˜๋ณต์  ์žฌ๊ฐ€์ค‘์น˜ ๊ธฐ๋ฒ•์—์„œ l1 ๋…ธ๋ฆ„์— ์˜ํ•ด ์œ ๋„๋œ ํฌ์†Œ์„ฑ์— ๊ธฐ์ธํ•œ ํŠน์„ฑ์œผ๋กœ ์ธํ•ด ์ข…์–‘๊ณผ ์ฃผ๋ณ€ ์กฐ์ง ์‚ฌ์ด์— ๋” ๋‚˜์€ ๋Œ€๋น„๋ฅผ ๋ณด์—ฌ์ฃผ์—ˆ๋‹ค. ๋˜ํ•œ ์ œ์•ˆ๋œ ๋ฐฉ๋ฒ•์€ PET๊ณผ MRI์˜ ํ•ด๋ถ€ํ•™์  ๊ฒฝ๊ณ„๊ฐ€ ์ผ์น˜ํ•˜๋Š” ์˜์—ญ์—์„œ PET ๊ฐ•๋„ ์ถ”์ •์— ๋Œ€ํ•œ ํŽธํ–ฅ์ด ๋” ๋‚ฎ๊ณ  ํ•˜์ดํผ ํŒŒ๋ผ๋ฏธํ„ฐ ์ข…์†์„ฑ์ด ์ ์Œ์„ ๋ณด์—ฌ์ฃผ์—ˆ๋‹ค. ๋˜ํ•œ, l1Bowsher ์‚ฌ์ „ ํ•จ์ˆ˜์˜ ๋‹ซํžŒ ํ•ด๋ฅผ ๊ธฐ๋ฐ˜์œผ๋กœ ๊ธฐ์กด์˜ ML-EM (maximum-likelihood expectation-maximization) ๋ชจ๋“ˆ์„ ํฌํ•จํ•˜๋Š” ํŽผ์ณ์ง„ ๋„คํŠธ์›Œํฌ๋„ ์ œ์•ˆ๋˜์—ˆ๋‹ค. ์ปจ๋ณผ๋ฃจ์…˜ ๋ ˆ์ด์–ด๋Š” ํ•ด๋ถ€ํ•™์ ์œผ๋กœ ์œ ๋„ ์žฌ๊ตฌ์„ฑ๋œ PET ์ด๋ฏธ์ง€์˜ ๋ถ„ํฌ๋ฅผ ์„ฑ๊ณต์ ์œผ๋กœ ํ•™์Šตํ–ˆ์œผ๋ฉฐ, EM ๋ชจ๋“ˆ์€ ์ค‘๊ฐ„ ์ถœ๋ ฅ๋“ค์„ ์‚ฌ์ด๋…ธ๊ทธ๋žจ๊ณผ ๋น„๊ตํ•˜์—ฌ ๊ฒฐ๊ณผ ์ด๋ฏธ์ง€๊ฐ€ ์ž˜ ๋“ค์–ด๋งž๊ฒŒ ์ˆ˜์ •ํ–ˆ๋‹ค. ์ œ์•ˆ๋œ ํŽผ์ณ์ง„ ๋„คํŠธ์›Œํฌ๋Š” ์ง€์—ญ์˜ ํก์ˆ˜์„ ๋Ÿ‰์ด ๋œ ํŽธํ–ฅ๋˜๊ณ  ํŽธ์ฐจ๊ฐ€ ์ ์–ด, ์ผ๋ฐ˜ U-Net๋ณด๋‹ค ๋” ๋‚˜์€ ์„ฑ๋Šฅ์„ ๋ณด์—ฌ์ฃผ์—ˆ๋‹ค. ๋”ฐ๋ผ์„œ ์ด๋Ÿฌํ•œ ๋ฐฉ๋ฒ•๋“ค์€ ํ•ด๋ถ€ํ•™์  ์ •๋ณด๋ฅผ ๊ธฐ๋ฐ˜์œผ๋กœ PET ์ด๋ฏธ์ง€ ํ’ˆ์งˆ์„ ํ–ฅ์ƒ์‹œํ‚ค๋Š” ๋ฐ ์œ ์šฉํ•  ๊ฒƒ์ด๋‹ค.Chapter 1. Introduction 1 1.1. Backgrounds 1 1.1.1. Positron Emission Tomography 1 1.1.2. Maximum a Posterior Reconstruction 1 1.1.3. Anatomical Prior 2 1.1.4. Proposed l_1 Bowsher Prior 3 1.1.5. Deep Learning for MR-less Application 4 1.2. Purpose of the Research 4 Chapter 2. Anatomically-guided PET Reconstruction Using Bowsher Prior 6 2.1. Backgrounds 6 2.1.1. PET Data Model 6 2.1.2. Original Bowsher Prior 7 2.2. Methods and Materials 8 2.2.1. Proposed l_1 Bowsher Prior 8 2.2.2. Iterative Reweighting 13 2.2.3. Computer Simulations 15 2.2.4. Human Data 16 2.2.5. Image Analysis 17 2.3. Results 19 2.3.1. Simulation with Brain Phantom 19 2.3.2.Human Data 20 2.4. Discussions 25 Chapter 3. Deep Learning Approach for Anatomically-guided PET Reconstruction 31 3.1. Backgrounds 31 3.2. Methods and Materials 33 3.2.1. Douglas-Rachford Splitting 33 3.2.2. Network Architecture 34 3.2.3. Dataset and Training Details 35 3.2.4. Image Analysis 36 3.3. Results 37 3.4. Discussions 38 Chapter 4. Conclusions 40 Bibliography 41 Abstract in Korean (๊ตญ๋ฌธ ์ดˆ๋ก) 52Docto

    A function space framework for structural total variation regularization with applications in inverse problems

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    In this work, we introduce a function space setting for a wide class of structural/weighted total variation (TV) regularization methods motivated by their applications in inverse problems. In particular, we consider a regularizer that is the appropriate lower semi-continuous envelope (relaxation) of a suitable total variation type functional initially defined for sufficiently smooth functions. We study examples where this relaxation can be expressed explicitly, and we also provide refinements for weighted total variation for a wide range of weights. Since an integral characterization of the relaxation in function space is, in general, not always available, we show that, for a rather general linear inverse problems setting, instead of the classical Tikhonov regularization problem, one can equivalently solve a saddle-point problem where no a priori knowledge of an explicit formulation of the structural TV functional is needed. In particular, motivated by concrete applications, we deduce corresponding results for linear inverse problems with norm and Poisson log-likelihood data discrepancy terms. Finally, we provide proof-of-concept numerical examples where we solve the saddle-point problem for weighted TV denoising as well as for MR guided PET image reconstruction
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