Abstract: Described herein is a lower parasitic multi-turn MRI phased array coil wherein the geometry is substantially identical between the coil turns. The potential of every corresponding point between the turns of the coil is also substantially equal, for example by using capacitors of substantially equal value and/or using substantially equal lengths of copper trace between breaks. As a result of this arrangement, the potential between coil turns is substantially equal, for example, with substantially equal capacitor value and substantially equal break point on conductor trace. This in turn reduces parasitics between turns because the geometry of each turn of the coil is substantially identical. The lower parasitic multi-turn MRI phased array coil is suitable for use with wired or wireless phased array coils, and is particularly well suited for use with lower field MRI systems.

Abstract: Provided is an MR/PET integrated imaging plug-in device that may be inserted into an MM system without requiring modifications to the MRI system, including: a to-be-detected object holder at the magnetic field generated by the magnetic field generation structure, and configured to carry the to-be-detected object; a PET detection component configured to detect a PET image signal from the to-be-detected object; a magnetic resonance receiving coil configured to generate a magnetic resonance image of the to-be-detected object a signal amplification component. The PET detection component is movable relative to the to-be-detected object holder to align or leave the to-be-detected object.

Abstract: The present application relates to a magnetic resonance imaging system comprising: a magnetic resonance imaging device comprising a cylindrical gradient coil apparatus, a radio frequency coil apparatus configured to transmit radio frequency signals at a first frequency, and a first shielding apparatus comprising a first shielding layer arranged radially between the gradient coil apparatus and the radio frequency coil apparatus; and a patient table device comprising a table portion configured for a patient to lie on it, and a second shielding apparatus arranged around at least a portion of the table portion, wherein when the magnetic resonance imaging device is engaged with the patient table device, the first shielding apparatus is in electrical contact with the second shielding apparatus to form a cutoff waveguide which is capable of cutting off radio frequency signals at frequencies below a second frequency, the second frequency being greater than the first frequency.

Abstract: Apparatus for imaging during surgical procedures includes an operating room for the surgical procedure and an MRI for obtaining images periodically through the surgical procedure by moving the magnet up to the table. The magnet wire is formed of a superconducting material such as magnesium di-boride or Niobium-Titanium which is cooled by a vacuum cryocooling system to superconductivity without use of liquid helium. The magnet weighs less than 1 to 2 tonne and has a floor area in the range 15 to 35 sq feet so that it can be carried on the floor by a support system having an air cushion covering the base area of the magnet having side skirts so as to spread the weight over the entire base area. The magnet remains in the room during surgery and is powered off to turn off the magnetic field when in the second position remote from the table.

Abstract: An upper coil assembly for use with a lower RF coil assembly mounted to provide an RF probe arranged to be engaged with a head of a patient in MRI includes a plurality of coil loops arranged in a row defining a phase shift coil array with each coil loop including an independent output conductor for communicating signals to a respective preamplifier for independent amplification and each coil loop including a plurality of capacitors at spaced positions therearound. To decouple the loops each coil loop partly overlaps a next coil loop with a first decoupling capacitor shared on a common portion of each coil loop and each next coil loop. The first and third coil loops are also decoupled by using third decoupling capacitor in a connecting conductor between the first and third coil loops.

Abstract: Embodiments relate to integrated MRI (Magnetic Resonance Imaging) coil arrays that can be stored within a patient table when not in use. One example embodiment comprises a coil array comprising: at least one flat spine-like coil array arranged within a patient table of a MRI system; and flexible coil array(s) configured to be in a stored position within the patient table, wherein, in the stored position, the flexible coil array(s) are one of within or under the at least one flat spine-like rigid coil array, wherein the flexible coil array(s) are further configured to be in an extended position, wherein, in the extended position, the flexible coil array(s) is configured to be extracted from the patient table and to wrap around at least one anatomical region of a patient on the patient table to facilitate MRI of the at least one anatomical region.

Abstract: Embodiments relate to MRI RF multi-tune coil elements, arrays, and MRI systems comprising such elements. One example embodiment comprises: a LC coil comprising one or more matching points; and two or more matching branches, each of which connected to the LC coil at matching point of the one or more matching points that is associated with that matching branch, wherein each matching branch comprises an associated set of one or more RF traps configured to block each frequency of two or more frequencies other than a frequency associated with that matching branch, and wherein each matching branch is configured to match to an associated predetermined impedance at the frequency associated with that matching branch.

Abstract: Embodiments relate to cylindrical MRI coils with at least one row as a birdcage row in a transmit mode. One example embodiment is a MRI Radio Frequency (RF) coil array comprising two or more rows of four or more RF coil elements each. Each of the RF coil elements can be configured to resonate at a working frequency of the coil array in a receive mode. At least one of the rows can be configured as a birdcage coil in the transmit mode, and the two or more rows can inductively couple together such that all the two or more rows can resonate together in the transmit mode at the working frequency.

Abstract: Embodiments relate to cylindrical MRI coil arrays with reduced coupling between coil elements. One example embodiment comprises two or more rows, wherein each row comprises at least three RF coil elements of that row enclosing a cylindrical axis; and a ring comprising an associated portion of each RF coil element of a first row and a second row electrically connected together, wherein the associated portion of each RF coil element of the first row and of each RF coil element of the second row comprises an associated capacitor of that RF coil element, and wherein the associated capacitor of that RF coil element is configured to reduce coupling among the RF coil elements of the first row and the RF coil elements of the second row.

Abstract: A single-layer magnetic resonance imaging (MRI) radio frequency (RF) coil element configured to operate in a transmit (Tx) mode and a receive (Rx) mode, the coil element comprising: an LC coil and a failsafe circuit electrically connected with the LC coil, where the LC coil, upon resonating with a primary coil of an MRI system, generates a local amplified Tx field based on an induced current generated in the LC coil by inductive coupling between the LC coil and the primary coil, where the failsafe circuit provides, upon injection of a forward DC bias current into the failsafe circuit, a first impedance, and upon the absence of the forward DC bias current, a second, higher impedance; where the failsafe circuit, upon the single-layer MRI RF coil array element being disconnected from an MRI system, provides the second, higher impedance, and reduces the magnitude of the induced current.

Abstract: A magnetic resonance imaging (MRI) radio frequency (RF) coil array configured to operate in a transmit (Tx) mode or in a receive (Rx) mode, comprising: a plurality of rows configured in an anatomy-specific shape, a row including a plurality of RF coil elements, an RF coil element including an LC coil and a magnitude/phase control component, where the LC coil, upon resonating with a primary coil at the working frequency of the primary coil, generates a local amplified Tx field based on an induced current in the LC coil, where a magnitude or a phase of the induced current is independently adjustable, where the magnitude/phase control component is configured to adjust the magnitude or phase of the induced current, and where the magnitude or phase of the induced current of a first RF coil element is independently adjustable from that of a second, different RF coil element.

Abstract: Embodiments relate to MRI coils and arrays comprising transmission lines to enforce periodic conditions. An example embodiment comprises a MRI RF coil array comprising: a plurality of assemblies, wherein each assembly of the plurality of assemblies comprises: a two-port device of that assembly, wherein the two-port device of that assembly is similar to the two-port device of each other assembly of the plurality of assemblies, and wherein the two-port device of that assembly comprises at least one associated inductor configured to, in a Tx mode, generate at least a portion of a B1 field; and a transmission line of that assembly, wherein a length of the transmission line of that assembly can be similar to a length of the transmission line of each other assembly of the plurality of assemblies, wherein the plurality of assemblies are connected together in a loop.

Abstract: A method for controlling an interventional magnetic resonance imaging (iMRI) system configured to control a heating mode of an iMRI guidewire, the method comprising: controlling, during an iMRI procedure, a magnitude of an induced current in a single-layer MRI radio frequency (RF) coil used in the iMRI procedure, or a phase of the induced current by adjusting at least one of: a difference between a working frequency of a whole body coil (WBC) used in the iMRI procedure and a resonant frequency of the single layer MRI RF coil, a coil loss resistance of the single layer MRI RF coil, or a blocking impedance of an LC circuit connected in parallel with the single-layer MRI RF coil; and controlling a heating mode of the guidewire based, at least in part on the magnitude or phase.

Abstract: Embodiments relate to multi-turn magnetic resonance imaging (MRI) radio frequency (RF) coil arrays employing ring decoupling, and MRI apparatuses employing such coil arrays. One example embodiment comprises: four or more RF coil elements that enclose a cylindrical axis, wherein each RF coil element comprises a first capacitor of that RF coil element and a loop comprising at least two turns; and a ring structure that facilitates decoupling of the RF coil elements, wherein each RF coil element is adjacent to two neighboring RF coil elements and is non-adjacent to one or more other coil elements, wherein each RF coil element has a shared side in common with the ring structure, wherein the shared side comprises a second capacitor of that RF coil element with a capacitance selected to mitigate inductive coupling between that RF coil element and non-adjacent RF coil elements.

Abstract: Embodiments relate to birdcage coils with in-plane open RF shielding capable of operating at 7T and higher field strength. One example embodiment comprises a first birdcage circuit and second birdcage circuit, each comprising two rings, N rungs that electrically connect the two rings of that circuit, a plurality of capacitors in the first birdcage circuit to form a first birdcage coil, and an optional plurality of capacitors in the second birdcage circuit to form a second birdcage coil when included or a non-resonant RF shield when omitted, wherein the first birdcage circuit is electrically isolated from the second birdcage circuit, wherein the first birdcage circuit and the second birdcage circuit have a common cylindrical axis, and wherein the N rungs of the second birdcage circuit are azimuthally rotated through a first angle relative to the N rungs of the first birdcage circuit.

Abstract: An example magnetic resonance imaging (MRI) radio frequency (RF) coil array comprises: at least one row of RF coil elements arranged radially around a cylindrical axis, wherein each row comprises: at least four RF coil elements circumferentially enclosing the cylindrical axis, wherein each RF coil element of that row is configured to operate in a Tx mode and in a Rx mode, wherein, in the Rx mode, each RF coil element of that row is tuned to a working frequency of the MRI RF coil array, and wherein, in the Tx mode, each RF coil element of that row is tuned to an additional frequency that is different than the working frequency, wherein the additional frequency is such that, a mode frequency of a selected mode resulting from coupling among the RF coil elements of that row is at the working frequency.

Abstract: Methods and other embodiments control a member of a plurality of MRI transmit (Tx)/receive (Rx) coil array elements to operate in a resonant Tx mode or in a non-resonant Tx mode. The member of the plurality of MRI Tx/Rx coil array elements, upon resonating with a primary coil at a working frequency, generates a local amplified Tx field based on an induced current in the member of the plurality of MRI Tx/Rx coil array elements. The member of the plurality of MRI Tx/Rx coil array elements includes at least one magnitude/phase control circuit connected in parallel. Upon detecting that the member of the plurality of MRI Tx/Rx coil array elements is operating in resonant Tx mode, embodiments randomly control a member of the at least one magnitude/phase control circuit to vary the magnitude or phase of the local amplified Tx field over a range of magnitudes or phases.

Abstract: An MRI RF coil array for use in a multi-channel MRI system, comprising a plurality of coils arranged in a M by N array, the number of columns corresponding with the number of channels in the MRI system. Columns are aligned with the B0 field. The plurality of coils are configured as a plurality of combined coils, corresponding with the number of columns, comprising a coil in a first row of the array connected with a coil in each of the remaining rows. The column position of each coil of a combined coil is distinct from the column position of each other coil of the combined coil. Coils of a combined coil are disjoint from the coils of each, other, combined coil. A combined coil is configured to connect with a corresponding member of the plurality of Rx channels, and is decoupled from each, other combined coil.

Abstract: Embodiments relate to cylindrical MRI coil arrays with reduced coupling between coil elements. One example embodiment comprises two or more rows, wherein each row comprises at least three RF coil elements of that row enclosing a cylindrical axis; and a ring comprising an associated portion of each RF coil element of a first row and a second row electrically connected together, wherein the associated portion of each RF coil element of the first row and of each RF coil element of the second row comprises an associated capacitor of that RF coil element, and wherein the associated capacitor of that RF coil element is configured to reduce coupling among the RF coil elements of the first row and the RF coil elements of the second row.

Abstract: Embodiments relate to cylindrical MRI coils with at least one row as a birdcage row in a transmit mode. One example embodiment is a MRI Radio Frequency (RF) coil array comprising two or more rows of four or more RF coil elements each. Each of the RF coil elements can be configured to resonate at a working frequency of the coil array in a receive mode. At least one of the rows can be configured as a birdcage coil in the transmit mode, and the two or more rows can inductively couple together such that all the two or more rows can resonate together in the transmit mode at the working frequency.