CommunicationLow-field MRI can be more sensitive than high-field MRI
Graphical abstract
Introduction
The superlative factor governing MRI image quality is the signal-to-noise ratio (SNR). High-field MRI using superconductive magnets has revolutionized medical diagnostics, with ever-increasing magnetic fields fostering sensitivity improvements via higher SNR. Yet low magnetic field strengths offer many attractive advantages such as reduced magnet size and cost, greater subject safety due to lower absorption of radio-frequency energy, and negligible subject induced magnetic field inhomogeneities [1]. These low-field MRI advantages can potentially be truly transformative, permitting performance of the entire MRI exam in seconds [2] provided sufficient SNR is available. The SNR of conventional, higher field detection is a complex equation of nuclear spin polarization, detection frequency, and other factors [3] arising from Faraday inductive detection. Nuclear spin polarization is a key factor contributing to this SNR. It is a relative measure of nuclear spin alignment with the applied magnetic field B0. Equilibrium nuclear spin polarization, which is only 10−6–10−5 at conditions of human body temperature and B0 of several Tesla, scales linearly with B0 and, therefore, SNR decreases at low field. However, non-equilibrium ‘hyperpolarization’ schemes make polarization independent of the detection field, providing a unique opportunity for high SNR and image quality at low field.
Hyperpolarization techniques temporarily increase polarization by several orders of magnitude to unity, or 100, referred to as the hyperpolarized state. These techniques include dissolution-Dynamic Nuclear Polarization (DNP) [4], Para-Hydrogen and Synthesis Allow Dramatically Enhanced Nuclear Alignment (PASADENA) [5], Spin Exchange Optical Pumping (SEOP) [6] and others. Regardless of the hyperpolarization approach used, the main goal in the context of biomedical applications is preparation of exogenous contrast agents with high polarization to enable molecular imaging of relatively dilute spin systems otherwise not amenable by conventional MRI. Examples of such contrast agents include hyperpolarized noble gases for lung imaging and 13C-labeled metabolites. The latter can be out of balance due to abnormal metabolism, and therefore act as reporters or biomarkers of diseases including those of cancer. 13C-pyruvate contrast agent reporting on elevated rate of glycolysis in cancer is one such example already in clinical trial [7] due to recognized status as a promising molecular imaging agent for prostate cancer.
While low-field MRI has been shown useful for hyperpolarized states of noble gases in lung imaging [8] and much progress has been made for utilizing hyperpolarized contrast agents in molecular imaging [4], [7], the B0 field independent nature of polarization in hyperpolarized contrast agents has not been fully taken advantage of. Maximizing imaging detection sensitivity as a function of both detection field B0 [9] and frequency ω0 still remains a challenge. Prior systematic efforts to develop a theoretical SNR foundation for MRI neglected optimization of the Faraday induction coils to the detection frequency ω0 [3], [9], [10], [11]. We recently demonstrated 13C hyperpolarized signals can be nearly field independent [12]. Here, we present a general theoretical description of hyperpolarized MRI sensitivity in the form of SNR as a function of detection frequency ω0 and experimental validation at four frequencies: 0.5 MHz, 2.0 MHz, 50 MHz, and 200 MHz. It is concluded that low-field MRI can be significantly more sensitive than high-field MRI for detection of hyperpolarized spin states. This is contrary to conventional wisdom that high-field MRI is always more sensitive.
Section snippets
Sample phantoms and preparation of nuclear spin polarizations
1H and 13C spectroscopic and imaging comparisons utilized two spherical phantoms of sodium 1-13C-acetate. The phantom for 1H studies was 1.0 g of sodium 1-13C-acetate (product #279293, Isotec–Sigma–Aldrich) dissolved in 99.8% D2O resulting in 2.8 mL total volume. A larger sample for 13C studies consisted of 5.18 g of sodium 1-13C-acetate dissolved in 99.8% D2O resulting in 17.5 mL total volume. High-field data were acquired on a 4.7 T Varian small animal MRI scanner with a multi-nuclear RF probe
Results and discussion
Seminal work by Hoult et al. [3], [15] described the SNR for Faraday inductive detection of the MRI signal in RF coils as
Eq. (1) relates the magnitude of the electromotive force induced in the RF coil |ε|, noise V, oscillating RF field homogeneity over the subject K, oscillating RF field strength per unit current over the subject B1, subject volume VS, detection frequency ω0, nuclear magnetic moment μN, nuclear spin polarization P, number of spins N
Conclusion
To summarize, a theoretical basis for SNR of hyperpolarized contrast agents as a function of detection frequency is described and validated experimentally. Low-field MRI can indeed be more sensitive for hyperpolarized contrast agents. Moreover, hyperpolarized low-field MRI in combination with cryogenically cooled RF coils [20], [28] can significantly surpass the sensitivity of hyperpolarized high-field MRI, which contradicts the ‘conventional wisdom’ of high-field MRI SNR superiority. In
Acknowledgments
We thank Professor Boyd M. Goodson for his comments on the writing of the manuscript and gratefully acknowledge funding support from NIH R25 CA136440, 3R00 CA134749, DOD CDMRP W81XWH-12-1-0159/BC112431.
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