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Myocardial T1 mapping at 5T using multi-inversion recovery real-time spoiled GRE

T0 review · 3 major / 6 minor · reviewed 2026-08-10 · deepseek-v4-flash

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Pith's one-line read A real-time multi-inversion GRE sequence maps myocardial T1 at 5T without the underestimation seen in MOLLI.

desk verdict First 5T myocardial T1 values and a plausible Look-Locker GRE sequence, but the accuracy claims in the abstract outrun the phantom table. read the letter →

arxiv 2501.07081 v3 pith:XQI3SG7M submitted 2025-01-13 physics.med-ph

Linqi Ge , Yihang Zhang , Huibin Zhu , Lang Zhang , Yihang Zhou , Haifeng Wang , Dong Liang , Hairong Zheng
show 1 more author
Yanjie Zhu
This is my paper · ORCID
classification physics.med-ph
keywords myocardialT1mapping5TMRILook-Lockerinversionrecoveryreal-timespoiledGREMOLLImulti-inversionaccuracy
verification ladder T0 review T1 audit T2 compute T3 formal

The pith

A machine-rendered reading of the paper's core claim, the machinery that carries it, and where it could break.

The reading

The paper sets out to establish that a Look-Locker-based sequence called mIR-rt, which samples magnetization recovery with continuous real-time spoiled GRE after multiple inversion pulses, can measure myocardial $T_1$ at 5T accurately. The authors argue that the standard MOLLI sequence systematically underestimates $T_1$ at 5T because it assumes full recovery between inversions and an ideal inversion pulse, assumptions that fail for the longer $T_1$ values found at ultra-high field. If the claim holds, mIR-rt supplies the first accurate myocardial $T_1$ values at 5T, with native myocardium near 1550 ms rather than the roughly 1350 ms reported by MOLLI, and gives clinicians a way to quantify diffuse myocardial disease at a field strength that is only beginning to be used for cardiac imaging.

What carries the argument

The central object is the two-curve Look-Locker fitting model that the sequence builds around. In that model, the signal during a continuous low-flip-angle GRE readout relaxes with an apparent time constant $T_1^*$ rather than $T_1$ itself: $M(t)=M_\infty-(M_\infty-M(0))\exp(-t/T_1^*)$, where $M_\infty$ is the GRE steady-state signal. mIR-rt generates two such curves with two inversion pulses; the second curve is written with the initial condition $M_2(0)=-\delta M_\infty$, which turns the inversion efficiency $\delta$ into a quantity measurable from the images just before and after that pulse. The fit then returns $A$, $B$, and $T_1^*$, and $T_1$ follows from $T_1=T_1^*(B/A-1)/\delta$ with a small dummy-time correction. This second-inversion design is the load-bearing mechanism because it removes the need for an extra calibration scan and converts a four-unknown fit into a three-parameter one.

What would settle it

Run mIR-rt on a phantom or volunteer with the interval between the two inversion pulses shortened in steps, for example 40, 30, and 20 images, while keeping all other settings fixed; if the measured $T_1$ shifts systematically as the interval shrinks, the steady-state assumption behind the second recovery curve is violated. A complementary check is to trigger the second inversion before and after the signal has visibly plateaued and compare the fitted $T_1$ values.

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Extended reading notes

Core claim

The central claim is that mIR-rt measures myocardial $T_1$ at 5T accurately, with errors under 3% in simulation and phantom against reference values, while MOLLI under-reads $T_1$. The sequence applies an inversion pulse, then continuously acquires diastolic real-time spoiled GRE images; after magnetization reaches the steady state of the GRE readout, a second inversion pulse increases the number of fitted samples and also lets the inversion efficiency $\delta$ be estimated from the image pair just before and after that pulse. Fitting follows the Look-Locker model with $M(t)=M_\infty-(M_\infty-M(0))\exp(-t/T_1^*)$, and $T_1$ is recovered as $T_1=T_1^*(B/A-1)/\delta$ with a dummy-time correction. In 16 healthy volunteers the native myocardial $T_1$ values were $1553\pm52$ ms (apex), $1531\pm53$ ms (middle), and $1526\pm60$ ms (base), significantly higher than MOLLI values near 1350 ms, and the paper reports these as the first myocardial $T_1$ values at 5T.

Load-bearing premise

The method depends on the spins actually reaching the steady state of the GRE readout before the second inversion pulse fires; if the fixed interval between inversions is too short for a subject's heart rate, the initial condition for the second recovery curve is wrong and the fitted $T_1$ is biased.

Editorial extensions

If this is right

  • If mIR-rt is accurate at 5T, future 5T cardiac studies can use roughly 1550 ms as the native myocardial $T_1$ reference range for healthy young adults, and departures from it can be tested as markers of disease.
  • MOLLI-based 5T $T_1$ values near 1350 ms would be understood as underestimates rather than true tissue values, so published or clinical 5T MOLLI results would need recalibration.
  • Because the method corrects for inversion efficiency from the second inversion pulse, accurate 5T $T_1$ mapping does not require an additional proton-density or long-delay calibration acquisition.
  • The sequence's fixed 10.2 s acquisition time and heart-rate-independent sample count make it practical for a single breath-hold.
  • The same steady-state-before-second-inversion logic should apply to other long-$T_1$ tissues at ultra-high field, where MOLLI's incomplete-recovery assumption is most damaging.

Reading between the lines

Editorial extensions of the paper, not claims the author makes directly.

  • A natural extension the authors do not pursue is to test whether the same steady-state-before-second-IR logic transfers to 7T cardiac $T_1$ mapping, where recovery times are even longer and the need for inversion-efficiency calibration scans is greater.
  • The reported roughly 200 ms gap between mIR-rt and MOLLI suggests that earlier 5T results obtained with MOLLI-type sequences should be re-examined rather than treated as physiological variation.
  • The method's weaker reproducibility at the apex and base, compared with the middle slice, points to motion and partial-volume effects rather than the fitting model as the current limiting factor, so combining mIR-rt with 3D whole-heart acquisition or learned motion correction could close that gap.
  • A testable clinical extension would be to apply mIR-rt to patients with suspected myocardial amyloidosis or iron overload: if the 5T baseline $T_1$ is longer, disease-related changes may produce a larger dynamic range than at 1.5T or 3T.
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Editorial analysis

A structured set of objections, weighed in public.

Desk editor's note, referee report, and a circularity audit.

Referee Report

3 major / 6 minor

Summary. Ge et al. present a multi-inversion recovery real-time spoiled GRE (mIR-rt) sequence for myocardial T1 mapping at 5T. The sequence applies two inversion pulses in a single breath-hold, acquires real-time GRE images continuously, retrospectively selects diastolic images, and fits a Look-Locker model with an inversion-efficiency parameter to produce T1 maps. The method is evaluated with Bloch simulations, phantom measurements against IR-SE references, and in vivo scans of 16 healthy volunteers, with comparison to MOLLI. The authors report native myocardial T1 values around 1526-1553 ms, significantly higher than MOLLI values around 1350 ms, and claim the technique is more accurate than MOLLI at 5T, representing the first myocardial T1 mapping at 5T.

Significance. The work addresses a real need: at 5T, longer T1 and incomplete magnetization recovery cause MOLLI to underestimate T1, and there is no established myocardial T1 mapping technique at that field strength. The paper's strengths include a physically motivated sequence design, systematic Bloch simulations over T1, flip angle, and inversion efficiency, phantom validation against a spin-echo reference, and reproducibility assessment with ICC. The explicit modeling of inversion efficiency is a useful contribution. However, the quantitative accuracy claim in the abstract is not supported by the phantom data, and the handling of inversion efficiency in vivo may introduce spatial bias. With revisions to the accuracy claims and the inversion-efficiency treatment, the paper would be a valuable contribution to ultra-high-field cardiac MRI.

major comments (3)
  1. [Abstract and §4.2/Table 1] The statement that phantom T1 values have 'errors less than 3%' is contradicted by Table 1. The absolute errors of mIR-rt are 66 ms (T1_ref = 950 ms), 76 ms (T1_ref = 1235 ms), 120 ms (T1_ref = 1485 ms), and 125 ms (T1_ref = 1885 ms), corresponding to normalized errors of 6.9%, 6.2%, 8.1%, and 6.6%, respectively. The 'less than 3%' claim is supported only by the simulation results in §4.1. Please revise the abstract and the main text to report the actual phantom accuracy or to explicitly restrict the '<3%' statement to the simulation study.
  2. [§2.2, §3.2, and Fig. 5] The fitting model in Eq. [5] uses the inversion efficiency δ as a known constant. The methods text (§2.2) says δ is 'estimated by the ratio of image intensities immediately before and after the second inversion pulse first,' but the in-vivo analysis (§3.2) fixes δ to the average value 0.85 from five volunteers. This inconsistency matters because Fig. 5 shows marked B1 inhomogeneity in the lateral wall, and the authors attribute the local T1 reduction there to reduced inversion efficiency. A single scalar δ cannot capture such spatial variation; using a global δ will bias T1 estimates in regions where the local inversion efficiency differs from 0.85. Please either estimate δ per-pixel from the images flanking the second IR or provide a sensitivity analysis quantifying how T1 errors scale with δ deviations. This is central to the accuracy and uniformity claims for the proposed method.
  3. [§6 (Conclusion)] The conclusion states that this study reports myocardial T1 values at 5T 'for the first time.' The introduction cites reference [14] on feasibility of cardiovascular MRI at 5T; if that reference or any other prior work has already reported myocardial T1 at 5T, the novelty claim needs qualification. Please verify the first-report claim against the existing literature and adjust the wording if needed.
minor comments (6)
  1. [Abstract vs. Table 2] The abstract reports apex/middle/base T1 values as 1553 ± 52, 1531 ± 53, and 1526 ± 60 ms, whereas Table 2 lists 1553 ± 54, 1530 ± 60, and 1532 ± 62 ms. Please harmonize the numbers.
  2. [§4.2, Figure numbering] The first sentence of §4.2 refers to 'Figure 3' for phantom T1 maps and bar graphs, but Figure 3 is already used in §4.1 for simulation error plots. Please renumber the figures so that each figure number is used only once.
  3. [Discussion, last paragraph] The sentence 'the accuracy of the vertices was somewhat lower' appears to be a typo; it should refer to the apex region, not 'vertices.'
  4. [§2.2, Eq. [7]] The correction T1_corrected = T1 + 2Δt is stated without derivation or reference in the text. A brief explanation or citation would help readers understand the factor of 2.
  5. [§4.3, Table 3] The ICC values are reported for only six subjects, and no confidence intervals are given. Given the small sample size, please report confidence intervals for the ICC estimates to allow assessment of reproducibility precision.
  6. [§4.3, identical p-values] The paragraph explaining why the Wilcoxon p-values are identical across layers is unnecessary in the results section; a brief sentence would suffice, and the explanation interrupts the presentation of the in-vivo results.

Circularity Check

0 steps flagged · score 2.0 of 10

No significant circularity: the T1 estimates are derived from an independent model fit with an externally measured inversion efficiency, and the only author-overlapping citation is a non-load-bearing registration tool.

full rationale

The derivation chain is self-contained. Equations [1]--[6] are the standard Look-Locker model, and T1 is recovered algebraically from the fitted parameters A, B, T1* together with an inversion efficiency delta measured independently from image intensities immediately before and after the second IR pulse (Section 3.2). Delta is not fitted to the same data that generate the reported myocardial T1 values; an average delta of 0.85 from 5 volunteers is fixed for all subjects, so the reported values are not forced by construction. Phantom validation is external: reference T1 values come from a 14-TI IR-SE acquisition and are compared with mIR-rt values obtained from the same sequence used in vivo, so the accuracy comparison is not circular. The steady-state assumption in Eq. [3] is a physical assumption that could be wrong, but it is not a circular reduction. The only author-overlapping citation is [20] (RS-MOCO registration), which is a preprocessing tool and is not load-bearing for the T1 fitting or for the accuracy claim versus MOLLI. I therefore find no self-definitional, fitted-input-called-prediction, self-citation-chain, or uniqueness-imported circularity in the central claim. Note for the reader: the abstract's 'errors less than 3%' statement for phantom studies is internally contradicted by Table 1, which reports 66--125 ms absolute errors on 950--1885 ms references (about 6--8% normalized); this is a consistency/correctness issue, not circularity.

Assumptions & free parameters 2 free parameters · 5 assumptions · 0 invented entities

The central claim rests on the Look-Locker model with a measured inversion efficiency, a steady-state assumption before the second IR, and an empirical diastolic selection rule. No new physical entities are introduced. The inversion efficiency and the diastolic threshold are the main free parameters.

free parameters (2)
  • Inversion efficiency δ = 0.85
    Measured as the average ratio of signal intensities before and after the second IR in 5 healthy volunteers, then fixed for all subjects and myocardial regions in Eq. [5] and [6].
  • Diastolic selection window = 50% to 95% of RR interval
    An empirical threshold on the RR interval used to classify images for T1 fitting; it affects which and how many data points enter the fit and is not independently validated.
assumptions (5)
  • domain assumption Longitudinal magnetization recovery follows a mono-exponential curve with a single apparent relaxation time T1* (Eq. [1]).
    Used in the Look-Locker fitting model without testing for multi-exponential behavior in myocardium at 5T.
  • standard math The steady-state signal M∞ of the spoiled GRE readout is proportional to T1*/T1 when TR << T1* < T1.
    Standard Look-Locker approximation from Deichmann and Haase [10], invoked to write M0* in Eq. [4].
  • domain assumption Magnetization reaches the GRE steady state before the second inversion pulse, so M2(0) = -δM∞ in Eq. [3].
    Load-bearing premise for the second recovery curve; not verified per subject or heart rate.
  • domain assumption Inversion efficiency δ is spatially uniform and constant across subjects, set to 0.85.
    A single value derived from 5 volunteers is used for all pixels and subjects, despite observed B1 inhomogeneity in the lateral wall.
  • domain assumption Bloch simulations use T2 = 40 ms and a simulated heart rate of 75 bpm as representative cardiac values.
    Used to optimize the IR pulse and to claim accuracy across T1 and flip angle; not tissue-specific for all subjects.

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Cite this review

Pith. "Pith review of Myocardial T1 mapping at 5T using multi-inversion recovery real-time spoiled GRE." pith.science (2026). https://pith.science/paper/XQI3SG7M

@misc{pith2026250107081,
  author       = {Pith},
  title        = {Pith review of: Myocardial T1 mapping at 5T using multi-inversion recovery real-time spoiled GRE},
  year         = {2026},
  howpublished = {\url{https://pith.science/paper/XQI3SG7M}},
  note         = {Machine review of arXiv:2501.07081}
}
read the original abstract

Objective: To develop an accurate myocardial T1 mapping technique at 5T using Look-Locker-based multiple inversion-recovery with the real-time spoiled gradient echo (GRE) acquisition. Approach: The proposed T1 mapping technique (mIR-rt) samples the recovery of inverted magnetization using the real-time GRE and the images captured during diastole are selected for T1 fitting. Multiple-inversion recoveries are employed to increase the sample size for accurate fitting. The T1 mapping method was validated using Bloch simulation, phantom studies, and in 16 healthy volunteers at 5T. Main results: In both simulation and phantom studies, the T1 values measured by mIR-rt closely approximate the reference T1 values, with errors less than 3%, while the conventional MOLLI sequence underestimates T1 values. The myocardial T1 values at 5T are 1553 +/- 52 ms, 1531 +/- 53 ms, and 1526 +/- 60 ms (mean +/- standard deviation) at the apex, middle, and base, respectively. The T1 values measured by MOLLI (1350 +/- 48 ms, 1349 +/- 47 ms, and 1354 +/- 45 ms at the apex, middle, and base) were significantly lower than those of mIR-rt with p<0.001 for all three layers. The mIR-rt sequence method used in our study provides high reproducibility, particularly in the middle slices, supporting its practical relevance for myocardial T1 mapping. Significance: The proposed method is feasible for myocardial T1 mapping at 5T and provides better accuracy than the conventional MOLLI sequence.

Figures

Figures reproduced from arXiv: 2501.07081 by the authors.

Figure 1
Figure 1. The time diagram of the mIR-rt sequence. The sequence has a fixed acquisition time of 10.2 seconds, with the number of cardiac cycles covered depending on heart rate (more cycles for higher heart rates). The top curves show ECG traces for different heart rates, with red arrows indicating inversion pulses (IR). The green trapezoidal blocks represent the spoiler gradient between the IR pulse and the first K-space line… view at source ↗

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Pith tools

Reviewed August 10, 2026 · model on record in the stance chip above.