# Current challenges of magnetic resonance elastography to quantify in vivo muscle behavior

Sabine Bensamoun, Philippe Pouletaut, Fabrice Charleux

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Sabine Bensamoun, Philippe Pouletaut, Fabrice Charleux. Current challenges of magnetic resonance elastography to quantify in vivo muscle behavior. 20th International Symposium on Computer Methods in Biomechanics and Biomedical Engineering, Universitat Pompeu Fabra Barcelona, Sep 2025, Barcelona, Spain. [hal-05143103](https://hal.science/hal-05143103v1)

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Submitted on 7 Jul 2025

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# CURRENT CHALLENGES OF MAGNETIC RESONANCE ELASTOGRAPHY TO QUANTIFY IN VIVO MUSCLE BEHAVIOR

Sabine Bensamoun (1), Philippe Pouletaut (1), Fabrice Charleux (2)

1. Université de technologie de Compiègne, CNRS, Biomechanics and Bioengineering, France; 2. ACRIM-Polyclinique Saint Côme, Radiology Department, France

## 1. Introduction

Magnetic Resonance Elastography (MRE) was primarily developed as a non-invasive method to quantify liver tissue stiffness using threshold values for assessing fibrosis severity [1]. The main technological and scientific challenges involved the development of efficient wave-generating drivers (mechanical, pneumatic) and the measurement of wavelengths using various methods (manually, inversion algorithms such as LFE, PG, DI, and MMDI [2]). Over time, MRE was applied to multiple organs, including the brain, breast, kidneys, and muscles [3]. However, some tissues are more complex due to their morphological, physiological and mechanical properties. This is particularly true for skeletal muscle, which exhibits:

1. Oriented fibers (parallel, oblique, etc.) resulting in anisotropic behavior,

2. Superficial or deep localization,

3. Different thicknesses (thin facial muscles vs large thigh/calf muscles),

4. Active and passive mechanical conditions,

5. Pathological states (fibrotic alterations). These muscle challenges will be presented, along with potential solutions to address them.

## 2. Materials and Methods

MRE muscle tests use a 1.5T or 3T MRI. An ergometric device can assess muscle contractility, but increases preparation time and requires MRI-compatible materials to avoid artifacts. Waves in skeletal muscles are generated with 90 Hz air pressure through a silicone tube around the target muscle. The pneumatic driver and frequency selection ensure deep wave propagation. A gradient echo sequence with a motion-encoding gradient (Z direction) provides phase images (4 offsets). The scan plane is aligned with muscle fascicles for optimal wave guidance. A Butterworth filter is applied based on fiber orientation. Muscle anisotropy may be assessed with diffusion-weighted sequences and X/Y encoding, though this increases acquisition time. The inversion algorithm must be carefully chosen to enhance

stiffness accuracy, but challenges persist when fibers are damaged or replaced by fibrosis.

## 3. Results

The figure 1 shows the challenge to observe the displacement of the shear wave inside (A) Duchenne muscle, (B) thin facial muscle and (C) neck muscle along with (D) its stiffness.

<figure><img src="image_2.png" /><figcaption>**Figure 1:** Ongoing challenges: phase image acquisitions of fibrotic, thin and neck muscles.</figcaption></figure>

## 4. Discussion and Conclusions

MRE is a non-invasive technique to monitor the functional behaviour of individual muscles. This information will help the clinician to choose and adapt the treatment. The development of MRE protocols will fill the gap of *in vivo* muscle data in the literature.

## 5. References

1. Leclerc GE et al, JMRI; 38(2):422-428 (2013).

2. Chakouch MK et al JMRI 43(6):1423-33 (2016)

3. Bensamoun SF et al, IRBM; 36(1):4-9 (2015).