An improved homogeneity design method for fast field-cycling coils in molecular MRI.

PURPOSE: Delta relaxation-enhanced MR (dreMR) is a field-cycling quantitative method for molecular imaging. The dreMR method uses a B0 insert coil to shift the magnitude of the main magnetic field as a magnetization preparation phase of the pulse sequence. Here, an improved coil design method is presented that minimizes field inhomogeneities and allows for explicit control of the ROI. METHODS: A solenoid produces the bulk field shift, and a boundary element method is employed to design in-series shim and shield layers. A design is presented and compared to the current generation dreMR coil design on field inhomogeneity maps, shield performance, and simulated dreMR image. A proof-of-concept design is also presented with an ROI shifted from isocenter. RESULTS: The new design is able to image a sphere of 8.5 cm in diameter with field inhomogeneity of < 1% versus the previous design's 5 cm. The new design presented an increase in shielding capabilities, whereas inductance and resistance increased. For a simulated dreMR image, the new design presented errors < 10% compared to an ideal field simulation, whereas the previous design had errors > 18%. The shifted ROI design produced a region of < 1% inhomogeneity much larger than a design with no shim layer. CONCLUSION: The new design method was found to greatly improve the insert coil field homogeneity and reduce errors in dreMR imaging in simulation without detriment to shielding. This method's capability to increase ROI and control its location will be used to design human dreMR coils going forward.

Design and construction of a gradient coil for high resolution marmoset imaging.

A gradient coil with integrated second and third order shims has been designed and constructed for use inside an actively shielded 310 mm horizontal bore 9.4 T small animal MRI. An extension of the boundary element method, to minimise the power deposited in conducting surfaces, was used to design the gradients, and a boundary element method with a constraint on mutual inductance was used to design the shims. The gradient coil allows for improved imaging performance and was optimized for an imaging region appropriate for marmoset imaging studies. Efficiencies of 1.5 mT m-1 A-1 were achieved in a 15 cm wide bore while maintaining gradient uniformity ≤5% over the 8 cm region of interest. Two new cooling methods were implemented which allowed the gradient coil to operate at 100 A RMS, 25 % of max current with a temperature rise below 30 C.

Nuclear magnetic relaxation dispersion of murine tissue for development of T1 (R1 ) dispersion contrast imaging.

This study quantified the spin-lattice relaxation rate (R1 ) dispersion of murine tissues from 0.24 mT to 3 T. A combination of ex vivo and in vivo spin-lattice relaxation rate measurements were acquired for murine tissue. Selected brain, liver, kidney, muscle, and fat tissues were excised and R1 dispersion profiles were acquired from 0.24 mT to 1.0 T at 37 °C, using a fast field-cycling MR (FFC-MR) relaxometer. In vivo R1 dispersion profiles of mice were acquired from 1.26 T to 1.74 T at 37 °C, using FFC-MRI on a 1.5 T scanner outfitted with a field-cycling insert electromagnet to dynamically control B0 prior to imaging. Images at five field strengths (1.26, 1.39, 1.5, 1.61, 1.74 T) were acquired using a field-cycling pulse sequence, where B0 was modulated for varying relaxation durations prior to imaging. R1 maps and R1 dispersion (ΔR1 /ΔB0 ) were calculated at 1.5 T on a pixel-by-pixel basis. In addition, in vivo R1 maps of mice were acquired at 3 T. At fields less than 1 T, a large R1 magnetic field dependence was observed for tissues. ROI analysis of the tissues showed little relaxation dispersion for magnetic fields from 1.26 T to 3 T. Our tissue measurements show strong R1 dispersion at field strengths less than 1 T and limited R1 dispersion at field strengths greater than 1 T. These findings emphasize the inherent weak R1 magnetic field dependence of healthy tissues at clinical field strengths. This characteristic of tissues can be exploited by a combination of FFC-MRI and T1 contrast agents that exhibit strong relaxivity magnetic field dependences (inherent or by binding to a protein), thereby increasing the agents' specificity and sensitivity. This development can provide potential insights into protein-based biomarkers using FFC-MRI to assess early changes in tumour development, which are not easily measureable with conventional MRI.

Dual optimization method of radiofrequency and quasistatic field simulations for reduction of eddy currents generated on 7T radiofrequency coil shielding.

PURPOSE: To optimize the design of radiofrequency (RF) shielding of transmit coils at 7T and reduce eddy currents generated on the RF shielding when imaging with rapid gradient waveforms. METHODS: One set of a four-element, 2 × 2 Tic-Tac-Toe head coil structure was selected and constructed to study eddy currents on the RF coil shielding. The generated eddy currents were quantitatively studied in the time and frequency domains. The RF characteristics were studied using the finite difference time domain method. Five different kinds of RF shielding were tested on a 7T MRI scanner with phantoms and in vivo human subjects. RESULTS: The eddy current simulation method was verified by the measurement results. Eddy currents induced by solid/intact and simple-structured slotted RF shielding significantly distorted the gradient fields. Echo-planar images, B1+ maps, and S matrix measurements verified that the proposed slot pattern suppressed the eddy currents while maintaining the RF characteristics of the transmit coil. CONCLUSION: The presented dual-optimization method could be used to design RF shielding and reduce the gradient field-induced eddy currents while maintaining the RF characteristics of the transmit coil.

Development and optimization of hardware for delta relaxation enhanced MRI.

PURPOSE: Delta relaxation enhanced magnetic resonance (dreMR) imaging requires an auxiliary B0 electromagnet capable of shifting the main magnetic field within a clinical 1.5 Tesla (T) MR system. In this work, the main causes of interaction between an actively shielded, insertable resistive B0 electromagnet and a 1.5T superconducting system are systematically identified and mitigated. METHODS: The effects of nonideal fabrication of the field-shifting magnet are taken into consideration through careful measurement during winding and improved accuracy in the design of the associated active shield. The shielding performance of the resultant electromagnet is compared against a previously built system in which the shield design was based on an ideal primary coil model. Hardware and software approaches implemented to eliminate residual image artifacts are presented in detail. RESULTS: The eddy currents produced by the newly constructed dreMR system are shown to have a significantly smaller "long-time-constant" component, consistent with the hypothesis that less energy is deposited into the cryostat of the MR system. CONCLUSION: With active compensation, the dreMR imaging system is capable of 0.22T field shifts within a clinical 1.5T MRI with no significant residual eddy-current fields.

A new approach to shimming: the dynamically controlled adaptive current network.

PURPOSE: Magnetic field homogeneity is important in all aspects of magnetic resonance imaging. A new approach to increase field homogeneity is presented that allows dynamic and adaptive control over the flow of current over a single surface using a network of actively controlled solid-state switches. METHODS: Computer simulations were completed demonstrating the potential of this approach. Wire patterns were produced using the boundary element method to remove magnetic field inhomogeneities over multiple regions of interest. Field maps and regions of interest histograms were compared with and without the shim present. A prototype was constructed confirming the feasibility of this approach within the magnetic resonance environment. Metal-oxide-semiconductor field-effect transistors were used. Two field maps were acquired with the prototype producing gradient and offset field profiles, respectively. The experimental field profiles were compared with simulation. RESULTS: The wire patterns significantly increased field homogeneity over all regions of interest investigated. The field profiles produced by the prototype matched simulation. No imaging artifacts were produced. CONCLUSIONS: An approach to control the shape of a current distribution over a single surface has been described. This method has the potential to improve field homogeneity over any desired region of interest and is particularly well suited for dynamic applications. The method is feasible with current technology and construction techniques.

New head gradient coil design and construction techniques.

PURPOSE: To design and build a head insert gradient coil to use in conjunction with body gradients for superior imaging. MATERIALS AND METHODS: The use of the boundary element method to solve for a gradient coil wire pattern on an arbitrary surface allowed us to incorporate engineering changes into the electromagnetic design of a gradient coil directly. Improved wire pattern design was combined with robust manufacturing techniques and novel cooling methods. RESULTS: The finished coil had an efficiency of 0.15 mT/m/A in all three axes and allowed the imaging region to extend across the entire head and upper part of the neck. CONCLUSION: The ability to adapt an electromagnetic design to necessary changes from an engineering perspective leads to superior coil performance.

Shielded resistive electromagnets of arbitrary surface geometry using the boundary element method and a minimum energy constraint.

Eddy currents are generated in MR by the use of rapidly switched electromagnets, resulting in time varying and spatially varying magnetic fields that must be either minimized or corrected. This problem is further complicated when non-cylindrical insert magnets are used for specialized applications. Interruption of the coupling between an insert coil and the MR system is typically accomplished using active magnetic shielding. A new method of actively shielding insert gradient and shim coils of any surface geometry by use of the boundary element method for coil design with a minimum energy constraint is presented. This method was applied to shield x- and z-gradient coils for two separate cases: a traditional cylindrical primary gradient with cylindrical shield and, to demonstrate its versatility in surface geometry, the same cylindrical primary gradients with a rectangular box-shaped shield. For the cylindrical case this method produced shields that agreed with analytic solutions. For the second case, the rectangular box-shaped shields demonstrated very good shielding characteristics despite having a different geometry than the primary coils.

Simulation of head-gradient-coil induced electric fields in a human model.

A finite difference method was used to simulate the electric fields induced in the model by a gradient wire pattern. The pattern simulated corresponded to a design used to perform peripheral nerves stimulation experiments. The size (187.8, 169.02, and 150.24 cm tall) and position (brain and neck mode) of the model, relative to the magnet, as well as the voxel dimensions (3, 6, and 9 mm) of the model were varied to assess the effect on the simulation. The locations of stimulation reported from an experiment were classified according to nerve branch and compared with the peak-simulated electric fields. Model size and location affected the magnitude of the electric field, but not the position. Model resolution affected the location of the peak field. For the smallest resolution investigated, the nerves affected by the locations of peak stimulations in the model correlated to the frequency of stimulation in experiments. Although adequate resolution is required in order to assess the electric fields induced by gradient coil operation, the simulation of electric fields may be useful in evaluating gradient coil design prior to construction.

First image from a combined positron emission tomography and field-cycled MRI system.

Combining positron emission tomography and MRI modalities typically requires using either conventional MRI with a MR-compatible positron emission tomography system or a modified MR system with conventional positron emission tomography. A feature of field-cycled MRI is that all magnetic fields can be turned off rapidly, enabling the use of conventional positron emission tomography detectors based on photomultiplier tubes. In this demonstration, two photomultiplier tube-based positron emission tomography detectors were integrated with a field-cycled MRI system (0.3 T/4 MHz) by placing them into a 9-cm axial gap. A positron emission tomography-MRI phantom consisting of a triangular arrangement of positron-emitting point sources embedded in an onion was imaged in a repeating interleaved sequence of ∼1 sec MRI then 1 sec positron emission tomography. The first multimodality images from the combined positron emission tomography and field-cycled MRI system show no additional artifacts due to interaction between the systems and demonstrate the potential of this approach to combining positron emission tomography and MRI.

Results for diffusion-weighted imaging with a fourth-channel gradient insert.

Diffusion-weighted imaging suffers from motion artifacts and relatively low signal quality due to the long echo times required to permit the diffusion encoding. We investigated the inclusion of a noncylindrical fourth gradient coil, dedicated entirely to diffusion encoding, into the imaging system. Standard three-axis whole body gradients were used during image acquisition, but we designed and constructed an insert coil to perform diffusion encodings. We imaged three phantoms on a 3-T system with a range of diffusion coefficients. Using the insert gradient, we were able to encode b values of greater than 1300 s/mm(2) with an echo time of just 83 ms. Images obtained using the insert gradient had higher signal to noise ratios than those obtained using the whole body gradient: at 500 s/mm(2) there was a 18% improvement in signal to noise ratio, at 1000 s/mm(2) there was a 39% improvement in signal to noise ratio, and at 1350 s/mm(2) there was a 56% improvement in signal to noise ratio. Using the insert gradient, we were capable of doing diffusion encoding at high b values by using relatively short echo times.

Quantitative Comparison of Minimum Inductance and Minimum Power Algorithms for the Design of Shim Coils for Small Animal Imaging.

High-performance shim coils are required for high-field magnetic resonance imaging and spectroscopy. Complete sets of high-power and high-performance shim coils were designed using two different methods: the minimum inductance and the minimum power target field methods. A quantitative comparison of shim performance in terms of merit of inductance (ML) and merit of resistance (MR) was made for shim coils designed using the minimum inductance and the minimum power design algorithms. In each design case, the difference in ML and the difference in MR given by the two design methods was <15%. Comparison of wire patterns obtained using the two design algorithms show that minimum inductance designs tend to feature oscillations within the current density; while minimum power designs tend to feature less rapidly varying current densities and lower power dissipation. Overall, the differences in coil performance obtained by the two methods are relatively small. For the specific case of shim systems customized for small animal imaging, the reduced power dissipation obtained when using the minimum power method is judged to be more significant than the improvements in switching speed obtained from the minimum inductance method.

Evaluation of a positron emission tomography (PET)-compatible field-cycled MRI (FCMRI) scanner.

Field-cycled MRI (FCMRI) uses two independent, actively controlled resistive magnets to polarize a sample and to provide the magnetic field environment during data acquisition. This separation of tasks allows for novel forms of contrast, reduction of susceptibility artifacts, and a versatility in design that facilitates the integration of a second imaging modality. A 0.3T/4-MHz FCMRI scanner was constructed with a 9-cm-wide opening through the side for the inclusion of a photomultiplier-tube-based positron emission tomography (PET) system. The performance of the FCMRI scanner was evaluated prior to integrating PET detectors. Quantitative measurements of the system's signal, phase, and temperature were recorded. The polarizing and readout magnets could be operated continuously at 100 A without risk of damage to the system. Transient instabilities in the readout magnet, caused by the pulsing of the polarizing magnet, dissipated in 50 ms; this resulted in a steady-state homogeneity of 32 Hz over a 7-cm-diameter volume. The short- and long-term phase behaviors of the readout field were sufficiently stable to prevent visible readout or phase-encode artifacts during imaging. Preliminary MR images demonstrated the potential of the FCMRI scanner and the efficacy of integrating a PET system.

Delta relaxation enhanced MR: improving activation-specificity of molecular probes through R1 dispersion imaging.

MR molecular imaging enables high-resolution, in vivo study of molecular processes frequently utilizing gadolinium-based probes that specifically bind to a particular biological molecule or tissue. While some MR probes are inactive when unbound and produce enhancement only after binding, the majority are less specific and cause enhancement in either state. Accumulation processes are then required to increase probe concentration in regions of the target molecule/tissue. Herein, a method is described for creating specificity for traditionally nonspecific probes. This method utilizes MR field-cycling methods to produce MRI contrast related to the dependence of R(1) upon magnetic field. It is shown that the partial derivative of R(1) with respect to magnetic field strength, R(1)', can be used as an unambiguous measure of probe binding. T(1)-weighted images and R(1)' images were produced for samples of albumin and buffer both enhanced with the albumin-binding agent Vasovist. For T(1) images, samples with low concentrations of Vasovist in an albumin solution could not be differentiated from samples with higher concentrations of Vasovist in buffer. Conversely, the R(1)' images showed high specificity to albumin. Albumin samples with a 10-microM concentration of Vasovist were enhanced over buffer samples containing up to 16 times more Vasovist.

Simulation of scattering and attenuation of 511 keV photons in a combined PET/field-cycled MRI system.

Mixing the imaging modalities of positron emission tomography (PET) and magnetic resonance imaging (MRI) will offer the best soft tissue contrast (MRI) with information about metabolic function (PET). The high magnetic field environment of an MRI system makes the detection of annihilation photons difficult, as the response of standard photo-multiplier tubes is compromised. An approach using field-cycled MRI is discussed here, as field-cycled MRI makes it possible to have long periods of time available for nuclear imaging when there is no magnetic field present. This work focuses upon the effect of the field-cycled MRI upon the nuclear image due to the added material providing additional attenuation of the PET signal, and additional nuclei for scatter. These effects are studied using a Monte Carlo simulation based upon the GEANT libraries. Attenuation effects are shown to be significant, approximately 6% for the RF shield and coil and approximately 24% for the gradients. No significant effect is seen in image quality due to the scattering of the gammas. With these levels of attenuation it is concluded that open gradient coils and shim coils are required around the imaging volume.