Generative priors reconstruct accelerated 3D MRI well but pay heavily at deployment: tens of network evaluations per volume, and protocol-specific hyperparameter tuning. A third hidden cost is the scanner's fixed sampling pattern. We treat the whole operating point as an input. A 3D MeanFlow patch network (a one-step flow model) is fine-tuned end-to-end through a warm-started, five-iteration differentiable conjugate-gradient projection. A small hypernetwork maps the operating point (data-consistency weight, acceleration, and the Cartesian sampling pattern itself) to the network's per-channel modulation. Three findings follow. (i) Learning the acquisition is worth more than any other operating point: on clinical knee data, the learned mask gains up to +2.34 dB over the protocol's variable-density mask. This gain requires the solver: with a feed-forward reconstructor the same learned mask hurts at 4x (-1.7 dB), but with the data-consistency projection it adds +4.6 dB. (ii) One evaluation is highly effective: it beats a 20-step patch-diffusion prior by up to +3.1 dB on brain and +2.9 dB on knee. Three to five evaluations extend the front to +6 dB while using a quarter of the prior's network calls. (iii) Fully sampled targets are optional: trained self-supervised on a split of acquired samples, the reconstructor matches its supervised twin at 4x on real data. Finally, we report what failed and why: subject-adaptive acquisition from measured energy, combining self-supervision with learned acquisition, and amortising the data-consistency weight.
Figures & tables
Figure 1: (a) The measurement-conditioned one-step reconstructor: a 323 patch of the noisy state, the zero-filled condition, pooled thumbnails of both and the voxel coordinates enter a plain 3D U-Net whose blocks are modulated (FiLM) by a hypernetwork of the operating point h=(logλ,log2R) ; one jump x^=xzf−suθ gives the clean estimate. (b) The same h drives a second hypernetwork head that emits logits over the phase-encode plane, renormalised to the budget 1/R : a relaxed mask in training, top- k at test time. (c) Training runs the whole chain (mask, measurement, zero-filled image, one evaluation, warm-started five-iteration CG) and the loss gradient reaches the hypernetwork and the mask logits through the solver. At test time: one evaluation plus CG, or three to five unrolled evaluations.
method
NFE
4×
8×
16×
BraTS 603
CG-SENSE (no prior)
0
34.80
32.04
30.31
one-step MeanFlow prior, plug-and-play
1
35.08
31.92
30.09
one-step MeanFlow prior, plug-and-play
4
38.80
34.36
31.42
patch-diffusion prior, plug-and-play ( Hu et al., 2024 )
20
39.83
34.22
31.04
patch-diffusion prior, plug-and-play
80
39.95
34.20
30.93
ours , one evaluation, hyper (λ,R)
1
41.33
37.31
34.12
Table 3: The cost-quality front. PSNR (dB), 10 volumes, 30 dB, best λ per row; NFE = network evaluations per volume (each diffusion step also runs a 40-iteration CG). All rows share backbone, data, masks, noise, solver and metrics; “unrolled” = our recipe with K iterations of [network → warm CG]. Brain: BraTS 603 stored-measurement split, CG-5; knee: SKM-TEA, CG-20.
Figure 2: Left: quality against network evaluations per volume ( 8× , BraTS 603 ). Right: one hypernetwork model (red) against single-acceleration specialists (dashed; circles at their own rates); 6/12/24× were seen by no model.
Figure 3: Reconstructions and error maps at 8× , SKM-TEA knee, volume 0, two slices. Every column is the same measurement (one mask, one noise draw, best λ of the common grid) except the rightmost method, which acquires with its own learned mask at the same budget; the PSNR/SSIM under each title is that of the displayed volume. Error maps share one colour scale. At 4× the knee is solver-bound and every method is within 1 to 4 dB of the prior-free solver (App. D ); at 8× the prior-based and the measurement-conditioned reconstructions separate. The knee measurement is re-encoded from the reference with the scanner coil maps, as in every knee table.
Appendix figures & tables16 assets
Supplementary material from the paper’s appendix.
Appendix
4×
6×
8×
12×
16×
24×
32×
specialist 4×
41.69
37.82
35.35
33.02
31.86
30.39
29.82
specialist 8×
37.26
38.20
37.51
35.03
33.15
31.09
30.13
specialist 16×
33.93
34.07
34.44
34.79
34.26
32.64
31.30
one hypernetwork (λ,R) , Fourier features
41.33
37.04
37.31
35.40
34.16
32.73
31.83
one hypernetwork (λ,R) , plain MLP
41.33
38.94
37.31
35.40
34.12
32.77
31.79
CG-SENSE
34.80
33.01
32.04
30.77
30.31
29.16
28.90
Appendix
Table 4: One hypernetwork against single-rate specialists (BraTS 603 , PSNR dB, 10 volumes, 30 dB). 6/12/24× were seen by no model.
Figure 4: One volume of the BraTS 603 set at 8× (30 dB), with ∣ error ∣ underneath on a common scale. One measurement-conditioned network evaluation plus a warm CG projection removes residual aliasing that the 20-step diffusion prior leaves behind, at 1/20 of the network cost.
Figure 5: What the model chooses to acquire (BraTS 603 ). Top: the probability the hypernetwork emits for the requested acceleration; middle: the phase-encode locations actually sampled (top- YZ/R ); bottom: the protocol’s variable-density Gaussian mask at the same sampling fraction. At a matched budget the learned pattern concentrates far more strongly on the centre (the fraction of the central 12×12 block it keeps is 0.69/0.59/0.50/0.44 at 4/8/16/32× against 0.59/0.38/0.20/0.07 for the protocol) and its probabilities saturate near 0 and 1 , i.e. it makes decisions rather than jitter.
Figure 6: SKM-TEA knee, 4× , volume 0; error scale 0.1× the reference maximum, half that of the other figures, because at this solver-bound rate the residuals are small for every method.
Figure 7: SKM-TEA knee, 16× , volume 0.
Figure 8: BraTS 603 , 4× , volume 3.
Figure 9: BraTS 603 , 8× , volume 3.
Figure 10: BraTS 603 , 16× , volume 3.
Figure 11: BraTS 603 , 8× , volume 0.
Figure 12: BraTS 1203 , 8× , volume 3 (no unrolled model was trained at this resolution).
Figure 13: BraTS 1203 , 4× , volume 3.
Figure 14: PSNR against network evaluations on one split (BraTS 603 full-k-space split, protocol mask, 30 dB, 10 volumes, best λ per point): the patch-diffusion prior at 2/5/10/20/80 sampler steps (each step also runs a 40-iteration CG), our reconstructor at one and three evaluations (each followed by five warm CG iterations), and the prior-free CG-SENSE.
reconstructor
acquisition
6×
12×
24×
warm CG, 1 evaluation
protocol
38.62
35.52
33.24
learned
41.08
35.48
32.45
gain (won)
+2.46 (150/150)
−0.03 (65/150)
−0.78 (7/150)
warm CG, 3 evaluations
protocol
39.39
35.64
32.95
learned
44.94
38.84
34.25
gain (won)
+5.52 (150/150)
+3.20 (150/150)
+1.28 (150/150)
Appendix
Table 5: The mask head interpolates. BraTS 603 , all 150 validation volumes, 30 dB, PSNR (dB). The hypernetwork was trained on R∈{4,8,16,32} ; here it is asked for 6/12/24× , emitting both the FiLM modulation and the sampling pattern for a rate it never saw. Paired gain of the learned over the protocol mask, with volumes won.
method
NFE
4×
8×
16×
CG-SENSE (no prior)
0
33.26 / 0.586
30.60 / 0.533
28.94 / 0.506
one-step MeanFlow prior, plug-and-play
4
36.32 / 0.652
32.64 / 0.573
30.13 / 0.528
patch-diffusion prior, plug-and-play
20
38.89 / 0.805
33.20 / 0.701
30.04 / 0.659
ours , one evaluation
1
40.91 / 0.863
37.12 / 0.835
34.33 / 0.854
ours , three evaluations
3
42.13 / 0.895
37.45 / 0.832
34.19 / 0.799
ours , one evaluation, learned mask
1
45.54 / 0.934
39.24 / 0.896
33.93 / 0.815
Appendix
Table 6: The cost-quality front on the full-k-space split, all 150 validation volumes (BraTS 603 , 30 dB, best λ per volume and rate, PSNR / SSIM). The same split and models as Tables 1 and 2 . Paired margins of our reconstructor over the 20-step patch-diffusion prior: one evaluation +2.03[2.0,2.1] / +3.93[3.9,4.0] / +4.29[4.2,4.4] dB at 4/8/16× , three evaluations +3.31 / +4.28 / +4.17 dB, each on 150/150 volumes.
method
NFE
4×
8×
16×
CG-SENSE (no prior)
0
37.94 / 0.924
30.09 / 0.721
26.64 / 0.578
patch-diffusion prior, plug-and-play
20
38.83 / 0.939
31.29 / 0.741
27.01 / 0.570
ours , one evaluation
1
39.71 / 0.943
33.50 / 0.851
30.09 / 0.764
ours , three evaluations
3
40.88 / 0.964
35.62 / 0.916
31.86 / 0.850
ours , one evaluation, learned mask
1
41.81 / 0.964
34.80 / 0.892
31.03 / 0.828
Appendix
Table 7: SKM-TEA knee, all 33 validation volumes (quarter resolution, real k-space and scanner coil maps, 30 dB, best λ per volume and rate, PSNR / SSIM, CG-20 for our models). Paired margins over the 20-step patch-diffusion prior: one evaluation +0.82/+2.23/+3.07 dB, three evaluations +1.94/+4.34/+4.89 dB at 4/8/16× , each on 33/33 volumes.
run
obj
R
λ⋆
NFE
PSNR (dB)
SSIM
s/vol
a_adaptive_60_warm
meanflow
4
0.03
1
34.43 ± 1.25
0.830
0
a_adaptive_60_warm
meanflow
8
0.03
1
31.55 ± 1.12
0.793
0
a_adaptive_60_warm
meanflow
16
0.0001
1
31.06 ± 1.15
0.853
0
a_adaptive_60_warm
meanflow
32
0.0001
1
29.84 ± 1.16
0.822
0
a_fixed_60_std10x7_warm
meanflow
4
0.03
1
38.64 ± 1.40
0.870
0
a_fixed_60_std10x7_warm
meanflow
8
0.03
1
35.01 ± 1.32
0.839
0
Appendix
Table 8: Every evaluated run (best λ per run/rate/NFE; mean ± std over volumes; repaired benchmark, k-space SNR 30 dB). Source: results/*.csv in the released repository.
We present FlowMoDL, an unrolled neural network for highly accelerated 4D flow MRI reconstruction that directly optimizes for both anatomical magnitude and phase-derived velocity accuracy. Building on the MoDL framework, FlowMoDL alternates a learned (3+1)D spatiotemporal denoiser with conjugate-gradient data-consistency updates based on the SENSE forward model. A novel dual-pathway conditioning scheme adapts the denoiser features and data-consistency weighting, enabling a single model to handle varying acceleration factors (10× to 50×). To ensure physiological accuracy, the network is trained using a deep-supervision composite loss that explicitly penalizes velocity magnitude and angular errors, stabilized by a curriculum schedule. We evaluate FlowMoDL on the multi-center CMRx4DFlow dataset against classical and deep-learning baselines (CG-SENSE, MoDL, FlowVN, and FlowMRI-Net). A key advantage of FlowMoDL is its superior gradient step efficiency. When evaluated under an equivalent, limited budget of gradient steps, competing flow-specific networks degrade significantly. In contrast, FlowMoDL robustly converges and strictly outperforms all competitors across all acceleration factors in magnitude SSIM, nRMSE, relative velocity error, and angular error, successfully recovering sharp structural details and temporally coherent velocity fields.
Institute of Information Processing (tnt), Leibniz University Hannover, Germany · L3S, Leibniz University Hannover, Hannover, Germany · Department of Data Science, Friedrich-Alexander-Universität Erlangen-Nürnberg, Germany +2
Zero-shot MRI reconstruction relies on generative priors, but single-modality unconditional priors produce hallucinations under severe ill-posedness. In many clinical workflows, complementary MRI acquisitions (e.g. high-quality structural scans) are routinely available, yet existing reconstruction methods lack mechanisms to leverage this additional information. We propose MPFlow, a zero-shot multi-modal reconstruction framework built on rectified flow that incorporates auxiliary MRI modalities at inference time without retraining the generative prior to improve anatomical fidelity. Cross-modal guidance is enabled by our proposed self-supervised pretraining strategy, Patch-level Multi-modal MR Image Pretraining (PAMRI), which learns shared representations across modalities. Sampling is jointly guided by data consistency and cross-modal feature alignment using pre-trained PAMRI, systematically suppressing intrinsic and extrinsic hallucinations. Extensive experiments on HCP and BraTS show that MPFlow matches diffusion baselines on image quality using only 20% of sampling steps while reducing tumor hallucinations by more than 15% (segmentation dice score). This demonstrates that cross-modal guidance enables more reliable and efficient zero-shot MRI reconstruction.
Seunghoi Kim, Chen Jin, Henry F. J. Tregidgo +2
University College London, UK · Centre for AI, DS&AI, AstraZeneca, UK
4D flow MRI measures time-resolved, three-directional blood velocity but requires long acquisition times, and its diagnostic signal is carried by the phase difference between velocity encodings, not by image magnitude. Recent work has developed a per-encoding variational network to address image reconstruction in this field. In this work, we incorporate a joint supervised and self-supervised training regime and utilize both magnitude and velocity data during supervision. At the same time, we add multiple acquisition-robust and conditioning strategies based on the acceleration factors. On the CMRx4DFlow~2026 aortic dataset (1.5 and 3T), our model lowers RelErr by 38--50% and AngErr by 7.0--8.7∘ against a training-matched baseline across R=10--50, improving on every held-out subject at every acceleration. Our model also shows strong generalization ability to transfer on out-of-distribution data by employing the joint training scheme, with an increase of 7.2% in SSIM and decrease of 38% and 31% in AngErr and RelErr respectively.
Mengyuan Xue, Bochun Mei
Department of Radiology and Biomedical Imaging, University of California, San Francisco, San Francisco, CA, USA