Patent Description:
Magnetic resonance imaging (MRI) is a medical imaging modality that can create images of the inside of a human body without using x-rays or other ionizing radiation. MRI systems include a superconducting magnet to create a strong, uniform, static magnetic field B<NUM>. When a human body, or part of a human body, is placed in the magnetic field B<NUM>, the nuclear spins associated with the hydrogen nuclei in tissue water become polarized, wherein the magnetic moments associated with these spins become preferentially aligned along the direction of the magnetic field B<NUM>, resulting in a small net tissue magnetization along that axis. MRI systems also include gradient coils that produce smaller amplitude, spatially-varying magnetic fields with orthogonal axes to spatially encode the magnetic resonance (MR) signal by creating a signature resonance frequency at each location in the body. The hydrogen nuclei are excited by a radio frequency signal at or near the resonance frequency of the hydrogen nuclei, which add energy to the nuclear spin system. As the nuclear spins relax back to their rest energy state, they release the absorbed energy in the form of an RF signal. This RF signal (or MR signal) is detected by one or more RF coils and is transformed into the image using reconstruction algorithms.

In <CIT> methods and systems are provided for a flexible, lightweight, low-cost radio frequency (RF) coil array of a magnetic resonance imaging (MRI) system. In one example, a posterior RF coil assembly for a MRI system includes an RF coil array including a plurality of RF coils and a deformable material housing the plurality of RF coils, each RF coil comprising a loop portion of distributed capacitance wire conductors and a coupling electronics unit coupled to each of the plurality of RF coils.

In <CIT> various methods and systems are provided for a flexible, lightweight, low-cost radio frequency (RF) coil array of a magnetic resonance imaging (MRI) system. In one example, a RF coil array for a MRI system includes a plurality of RF coils, each RF coil comprising an integrated capacitor coil loop; a plurality of coupling electronics units each coupled to a respective coil loop; and a plurality of wires coupling each coupling electronics unit to an interface board configured to couple to a cable of the MRI system. The RF coil array is a high density (referring to the number of coil elements) anterior array (HDAA) or a high definition (referring to image resolution) anterior array.

An RF coil assembly for an MRI system according to claim <NUM> includes a central RF coil array including a first plurality of RF coils configured to cover a neck of a subject to be imaged, an upper RF coil array including a second plurality of RF coils extending upward from the central RF coil array and configured to cover a lower head region of the subject, and a lower RF coil array including a third plurality of RF coils extending downward from the central RF coil array and configured to cover an upper shoulder region of the subject, wherein each RF coil of the first, second, and third pluralities of RF coils comprises a loop portion comprising two distributed capacitance parallel wire conductors encapsulated and separated by a dielectric material to form a respective distributed capacitance along the length of the loop portion and wherein each loop portion of the first plurality of RF coils has a first diameter, each loop portion of the second plurality of RF coils has a second diameter, and each loop portion of the third plurality of RF coils has a third diameter, the second diameter and the third diameter being larger than the first diameter.

The following description relates to various embodiments of a radio frequency (RF) coil assembly for an MRI system. An MRI system, such as the MRI system shown by <FIG>, includes a receive RF coil unit that may be comprised of one or more RF coils. For example, the receive RF coil unit may comprise an array of RF coils, as shown in <FIG> and <FIG>. The RF coils are configured with coupling electronics and distributed capacitance wire conductors, as shown in <FIG>, such that each RF coil is lightweight, flexible, and transparent to each other RF coil. In this way, the RF coils may be positioned against a body of a patient and wrapped around the patient in order to image portions of the body that include complicated geometries. Because the RF coils include the coupling electronics and distributed capacitance wire conductors, the RF coils may move and/or overlap relative to each other without degradation of MR signals transmitted to the MRI system by the RF coils.

The receive RF coil unit may be used to image a head, neck, chest, and/or spine region of a patient. However, different patients may have different sized necks, as the neck region exhibits large variation in size across various patient populations. Further, the neck includes complicated geometry (such as a relatively narrow middle portion of the neck flaring upward and outward toward the jaw and also flaring downward and outward toward the chest). This variability in the neck anatomy from patient to patient and also the complicated geometry of the neck results in receive RF coil units that may not conform sufficiently to the patient anatomy to adequately image all areas of the anatomy, such as the cervical spine. Further, when typical RF coil units are made to conform tightly to the patient anatomy, the patient may experience discomfort due to the close proximity of the RF coil unit, which may be comprised of rigid and/or waterproof material that may be uncomfortable when placed tightly around the patient's neck, chest, head, and spine region.

Thus, according to embodiments disclosed herein, a neck RF coil assembly may be configured to tightly conform to the patient anatomy without causing undue discomfort to the patient. The neck RF coil assembly may include a plurality of RF coils as described above and shown in <FIG>. Owing to the lightweight and flexible nature of the conductors and small coupling electronics of the RF coils, the RF coils may be mounted on lightweight and flexible material that may conform tightly to patient anatomy and accommodate a variety of different patient sizes.

For example, a first neck RF coil assembly, as shown in <FIG>, may include three RF coil arrays that are stacked upon each other to form a collar-like structure with a central RF coil array that is configured to wrap around the narrow (e.g., middle) part of a neck of a subject and two peripheral RF coil arrays that, when stacked upon each other and the central RF coil array, form two rows of staggered RF coils. When the first neck RF coil assembly is worn by a subject, one of the two rows of staggered RF coils flares upward and outward from the center to surround a jaw/lower face of the subject and the other of the two rows of staggered RF coils flares downward and outward from the center to surround an upper chest/shoulders of the subject. The RF coils that form the two peripheral RF coil arrays may be attached to a respective substrate in an open loop manner, such that only a relatively small portion of each RF coil is attached to the substrate and the remaining portion of each RF coil is "open" to the environment. This open loop arrangement may allow the RF coils forming the two peripheral RF coil arrays to bend, flex, and otherwise move free from any restrictions that typical substrate/enclosure configurations may impose, thereby allowing the RF coils to conform around the complex geometry of the head, neck, and spine region.

A second neck RF coil assembly which is not covered by the scope of the claimed invention, as shown in <FIG>, may include a semi-rigid substrate shaped to fit over a chest and anterior neck/jaw region of a subject. The substrate may include flaps configured to extend from the subject's cheeks back along the sides of the neck, under the subject's ears, akin to a reverse neck pillow. In some examples, the substrate may include a chin strap configured to cover a chin of the patient. A plurality of RF coils are coupled to inner surfaces the substrate. The substrate may be comprised of foam or other semi-rigid material and various joints, hinges, or flex regions of the second neck RF coil assembly may be provided via the foam substrate rather than traditional coupling/hinging mechanisms. When the second neck RF coil assembly is worn by a patient, the RF coils coupled to the substrate may be brought in close proximity to the chest, anterior neck and chin, and the sides/back of the neck, thereby facilitating high quality imaging of all areas of the neck/spine region.

<FIG> illustrates a magnetic resonance imaging (MRI) apparatus <NUM> that includes a magnetostatic field magnet unit <NUM>, a gradient coil unit <NUM>, an RF coil unit <NUM>, an RF body or volume coil unit <NUM>, a transmit/receive (T/R) switch <NUM>, an RF driver unit <NUM>, a gradient coil driver unit <NUM>, a data acquisition unit <NUM>, a controller unit <NUM>, a patient table or bed <NUM>, a data processing unit <NUM>, an operating console unit <NUM>, and a display unit <NUM>. In some embodiments, the RF coil unit <NUM> is a surface coil, which is a local coil typically placed proximate to the anatomy of interest of a subject <NUM>. Herein, the RF body coil unit <NUM> is a transmit coil that transmits RF signals, and the local surface RF coil unit <NUM> receives the MR signals. As such, the transmit body coil (e.g., RF body coil unit <NUM>) and the surface receive coil (e.g., RF coil unit <NUM>) are separate but electromagnetically coupled components. The MRI apparatus <NUM> transmits electromagnetic pulse signals to the subject <NUM> placed in an imaging space <NUM> with a static magnetic field formed to perform a scan for obtaining magnetic resonance signals from the subject <NUM>. One or more images of the subject <NUM> can be reconstructed based on the magnetic resonance signals thus obtained by the scan.

The magnetostatic field magnet unit <NUM> includes, for example, an annular superconducting magnet, which is mounted within a toroidal vacuum vessel. The magnet defines a cylindrical space surrounding the subject <NUM> and generates a constant primary magnetostatic field B<NUM>.

The MRI apparatus <NUM> also includes a gradient coil unit <NUM> that forms a gradient magnetic field in the imaging space <NUM> so as to provide the magnetic resonance signals received by the RF coil arrays with three-dimensional positional information. The gradient coil unit <NUM> includes three gradient coil systems, each of which generates a gradient magnetic field along one of three spatial axes perpendicular to each other, and generates a gradient field in each of a frequency encoding direction, a phase encoding direction, and a slice selection direction in accordance with the imaging condition. More specifically, the gradient coil unit <NUM> applies a gradient field in the slice selection direction (or scan direction) of the subject <NUM>, to select the slice; and the RF body coil unit <NUM> or the local RF coil arrays may transmit an RF pulse to a selected slice of the subject <NUM>. The gradient coil unit <NUM> also applies a gradient field in the phase encoding direction of the subject <NUM> to phase encode the magnetic resonance signals from the slice excited by the RF pulse. The gradient coil unit <NUM> then applies a gradient field in the frequency encoding direction of the subject <NUM> to frequency encode the magnetic resonance signals from the slice excited by the RF pulse.

The RF coil unit <NUM> is disposed, for example, to enclose the region to be imaged of the subject <NUM>. In some examples, the RF coil unit <NUM> may be referred to as the surface coil or the receive coil. In the static magnetic field space or imaging space <NUM> where a static magnetic field B<NUM> is formed by the magnetostatic field magnet unit <NUM>, the RF coil unit <NUM> transmits, based on a control signal from the controller unit <NUM>, an RF pulse that is an electromagnet wave to the subject <NUM> and thereby generates a high-frequency magnetic field B<NUM>. This excites a spin of protons in the slice to be imaged of the subject <NUM>. The RF coil unit <NUM> receives, as a magnetic resonance signal, the electromagnetic wave generated when the proton spin thus excited in the slice to be imaged of the subject <NUM> returns into alignment with the initial magnetization vector. In some embodiments, the RF coil unit <NUM> may transmit the RF pulse and receive the MR signal. In other embodiments, the RF coil unit <NUM> may only be used for receiving the MR signals, but not transmitting the RF pulse.

The RF body coil unit <NUM> is disposed, for example, to enclose the imaging space <NUM>, and produces RF magnetic field pulses orthogonal to the main magnetic field B<NUM> produced by the magnetostatic field magnet unit <NUM> within the imaging space <NUM> to excite the nuclei. In contrast to the RF coil unit <NUM>, which may be disconnected from the MRI apparatus <NUM> and replaced with another RF coil unit, the RF body coil unit <NUM> is fixedly attached and connected to the MRI apparatus <NUM>. Furthermore, whereas local coils such as the RF coil unit <NUM> can transmit to or receive signals from only a localized region of the subject <NUM>, the RF body coil unit <NUM> generally has a larger coverage area. The RF body coil unit <NUM> may be used to transmit or receive signals to the whole body of the subject <NUM>, for example. Using receive-only local coils and transmit body coils provides a uniform RF excitation and good image uniformity at the expense of high RF power deposited in the subject. For a transmit-receive local coil, the local coil provides the RF excitation to the region of interest and receives the MR signal, thereby decreasing the RF power deposited in the subject. It should be appreciated that the particular use of the RF coil unit <NUM> and/or the RF body coil unit <NUM> depends on the imaging application.

The T/R switch <NUM> can selectively electrically connect the RF body coil unit <NUM> to the data acquisition unit <NUM> when operating in receive mode, and to the RF driver unit <NUM> when operating in transmit mode. Similarly, the T/R switch <NUM> can selectively electrically connect the RF coil unit <NUM> to the data acquisition unit <NUM> when the RF coil unit <NUM> operates in receive mode, and to the RF driver unit <NUM> when operating in transmit mode. When the RF coil unit <NUM> and the RF body coil unit <NUM> are both used in a single scan, for example if the RF coil unit <NUM> is configured to receive MR signals and the RF body coil unit <NUM> is configured to transmit RF signals, then the T/R switch <NUM> may direct control signals from the RF driver unit <NUM> to the RF body coil unit <NUM> while directing received MR signals from the RF coil unit <NUM> to the data acquisition unit <NUM>. The coils of the RF body coil unit <NUM> may be configured to operate in a transmit-only mode or a transmit-receive mode. The coils of the local RF coil unit <NUM> may be configured to operate in a transmit-receive mode or a receive-only mode.

The RF driver unit <NUM> includes a gate modulator (not shown), an RF power amplifier (not shown), and an RF oscillator (not shown) that are used to drive the RF coils (e.g., RF coil unit <NUM>) and form a high-frequency magnetic field in the imaging space <NUM>. The RF driver unit <NUM> modulates, based on a control signal from the controller unit <NUM> and using the gate modulator, the RF signal received from the RF oscillator into a signal of predetermined timing having a predetermined envelope. The RF signal modulated by the gate modulator is amplified by the RF power amplifier and then output to the RF coil unit <NUM>.

The gradient coil driver unit <NUM> drives the gradient coil unit <NUM> based on a control signal from the controller unit <NUM> and thereby generates a gradient magnetic field in the imaging space <NUM>. The gradient coil driver unit <NUM> includes three systems of driver circuits (not shown) corresponding to the three gradient coil systems included in the gradient coil unit <NUM>.

The data acquisition unit <NUM> includes a pre-amplifier (not shown), a phase detector (not shown), and an analog/digital converter (not shown) used to acquire the magnetic resonance signals received by the RF coil unit <NUM>. In the data acquisition unit <NUM>, the phase detector phase detects, using the output from the RF oscillator of the RF driver unit <NUM> as a reference signal, the magnetic resonance signals received from the RF coil unit <NUM> and amplified by the pre-amplifier, and outputs the phase-detected analog magnetic resonance signals to the analog/digital converter for conversion into digital signals. The digital signals thus obtained are output to the data processing unit <NUM>.

The MRI apparatus <NUM> includes a table <NUM> for placing the subject <NUM> thereon. The subject <NUM> may be moved inside and outside the imaging space <NUM> by moving the table <NUM> based on control signals from the controller unit <NUM>.

The controller unit <NUM> includes a computer and a recording medium on which a program to be executed by the computer is recorded. The program when executed by the computer causes various parts of the apparatus to carry out operations corresponding to pre-determined scanning. The recording medium may comprise, for example, a ROM, flexible disk, hard disk, optical disk, magneto-optical disk, CD-ROM, or non-volatile memory card. The controller unit <NUM> is connected to the operating console unit <NUM> and processes the operation signals input to the operating console unit <NUM> and furthermore controls the table <NUM>, RF driver unit <NUM>, gradient coil driver unit <NUM>, and data acquisition unit <NUM> by outputting control signals to them. The controller unit <NUM> also controls, to obtain a desired image, the data processing unit <NUM> and the display unit <NUM> based on operation signals received from the operating console unit <NUM>.

The operating console unit <NUM> includes user input devices such as a touchscreen, keyboard and a mouse. The operating console unit <NUM> is used by an operator, for example, to input such data as an imaging protocol and to set a region where an imaging sequence is to be executed. The data about the imaging protocol and the imaging sequence execution region are output to the controller unit <NUM>.

The data processing unit <NUM> includes a computer and a recording medium on which a program to be executed by the computer to perform predetermined data processing is recorded. The data processing unit <NUM> is connected to the controller unit <NUM> and performs data processing based on control signals received from the controller unit <NUM>. The data processing unit <NUM> is also connected to the data acquisition unit <NUM> and generates spectrum data by applying various image processing operations to the magnetic resonance signals output from the data acquisition unit <NUM>.

The display unit <NUM> includes a display device and displays an image on the display screen of the display device based on control signals received from the controller unit <NUM>. The display unit <NUM> displays, for example, an image regarding an input item about which the operator inputs operation data from the operating console unit <NUM>. The display unit <NUM> also displays a two-dimensional (2D) slice image or three-dimensional (3D) image of the subject <NUM> generated by the data processing unit <NUM>.

During a scan, RF coil array interfacing cables (not shown in <FIG>) may be used to transmit signals between the RF coils (e.g., RF coil unit <NUM> and RF body coil unit <NUM>) and other aspects of the processing system (e.g., data acquisition unit <NUM>, controller unit <NUM>, and so on), for example to control the RF coils and/or to receive information from the RF coils. As explained previously, the RF body coil unit <NUM> is a transmit coil that transmits RF signals, and the local surface RF coil unit <NUM> receives the MR signals. More generally, RF coils are used to transmit RF excitation signals ("transmit coil"), and to receive the MR signals emitted by an imaging subject ("receive coil"). In some embodiments, the transmit and receive coils are a single mechanical and electrical structure or array of structures, with transmit/receive mode switchable by auxiliary circuitry. In other examples, the transmit body coil (e.g., RF body coil unit <NUM>) and the surface receive coil (e.g., RF coil unit <NUM>) may be separate components. For enhanced image quality, however, it may be desirable to provide a receive coil that is mechanically and electrically isolated from the transmit coil. In such case it is desirable that the receive coil, in its receive mode, be electromagnetically coupled to and resonant with an RF "echo" that is stimulated by the transmit coil. However, during transmit mode, it may be desirable that the receive coil is electromagnetically decoupled from and therefore not resonant with the transmit coil, during actual transmission of the RF signal. Such decoupling averts a potential problem of noise produced within the auxiliary circuitry when the receive coil couples to the full power of the RF signal. Additional details regarding the uncoupling of the receive RF coil will be described below.

Turning now to <FIG>, a schematic view of an RF coil <NUM> coupled to a controller unit <NUM> is shown according to an exemplary embodiment. The RF coil <NUM> includes a loop portion <NUM> and a coupling electronics portion <NUM> which is coupled to the controller unit <NUM> via a coil-interfacing cable <NUM>. In some embodiments, the RF coil may be a surface receive coil, which may be single- or multi-channel. The RF coil <NUM> may be used in RF coil unit <NUM> of <FIG> and as such may operate at one or more frequencies in the MRI apparatus <NUM>. The coil-interfacing cable <NUM> may extend between the electronics portion <NUM> and an interfacing connector of an RF coil array and/or between the interfacing connector of the RF coil array and the MRI system controller unit <NUM>. The controller unit <NUM> may correspond to and/or be associated with the data processing unit <NUM> and/or controller unit <NUM> in <FIG>.

The loop portion <NUM> may be comprised of at least two parallel conductors that form a distributed capacitance along the length of the loop portion. In the example shown in <FIG>, the loop portion <NUM> includes a first conductor <NUM> and a second conductor <NUM> which exhibit a substantially uniform capacitance along the entire length of the loop portion. Distributed capacitance (DCAP), as used herein, represents a capacitance exhibited between conductors that distributes along the length of the conductors and may be void of discrete or lumped capacitive components and discrete or lumped inductive components. The DCAP can also be called incorporated capacitance. In some embodiments, the capacitance may distribute in a uniform manner along the length of the conductors.

A dielectric material <NUM> encapsulates and separates the first and second conductors <NUM>, <NUM>. The dielectric material <NUM> may be selected to achieve a desired distributive capacitance. For example, the dielectric material <NUM> may be selected based on a desired permittivity ε. In particular, the dielectric material <NUM> may be air, rubber, plastic, or any other appropriate dielectric material. In some embodiments, the dielectric material may be polytetrafluoroethylene (pTFE). The dielectric material <NUM> may surround the parallel conductive elements of the first and second conductors <NUM>, <NUM>. Alternatively, the first and second conductors <NUM>, <NUM> may be twisted upon one another to from a twisted pair cable. As another example, the dielectric material <NUM> may be a plastic material. The first and second conductors <NUM>, <NUM> may form a coaxial structure in which the plastic dielectric material <NUM> separates the first and second conductors. As another example, the first and second conductors may be configured as planar strips.

The coupling electronics portion <NUM> is connected to the loop portion <NUM> of the RF coil <NUM>. Herein, the coupling electronics portion <NUM> may include a decoupling circuit <NUM>, impedance inverter circuit <NUM>, and a pre-amplifier <NUM>. The decoupling circuit <NUM> may effectively decouple the RF coil during a transmit operation. Typically, the RF coil <NUM> in its receive mode may receive MR signals from a body of a subject being imaged by the MR apparatus. If the RF coil <NUM> is not used for transmission, then it may be decoupled from the RF body coil while the RF body coil is transmitting the RF signal.

The impedance inverter circuit <NUM> may include an impedance matching network between the loop portion <NUM> and the pre-amplifier <NUM>. The impedance inverter circuit <NUM> is configured to transform an impedance of the loop portion <NUM> into an optimal source impedance for the pre-amplifier <NUM>. The impedance inverter circuit <NUM> may include an impedance matching network and an input balun. The pre-amplifier <NUM> receives MR signals from the loop portion <NUM> and amplifies the received MR signals. In one example, the pre-amplifier <NUM> may have a low input impedance configured to accommodate a relatively high blocking or source impedance. The coupling electronics portion <NUM> may be packaged in a very small PCB, e.g., approximately <NUM><NUM> in size or smaller. The PCB may be protected with a conformal coating or an encapsulating resin.

The coil-interfacing cable <NUM>, such as a RF coil array interfacing cable, may be used to transmit signals between the RF coils and other aspects of the processing system. The RF coil array interfacing cable may be disposed within the bore or imaging space of the MRI apparatus (such as MRI apparatus <NUM> of <FIG>) and subjected to electro-magnetic fields produced and used by the MRI apparatus. In MRI systems, coil-interfacing cables, such as coil-interfacing cable <NUM>, may support transmitter-driven common-mode currents, which may in turn create field distortions and/or unpredictable heating of components. Typically, common-mode currents are blocked by using baluns. Baluns or common-mode traps provide high common-mode impedances, which in turn reduces the effect of transmitter-driven currents. Thus, coil-interfacing cable <NUM> may include one or more baluns. In some embodiments, the one or more baluns may be continuous baluns, such as distributed, flutter, and/or butterfly baluns. The cable <NUM> may be a <NUM>-conductor triaxial cable having a center conductor, an inner shield, and an outer shield. In some embodiments, the center conductor is connected to the RF signal and pre-amp control (RF), the inner shield is connected to ground (GND), and the outer shield is connected to the multi-control bias (diode decoupling control) (MC_BIAS).

The RF coil presented above with respect to <FIG> and <FIG> may be utilized in order to receive MR signals during an MR imaging session. As such, the RF coil of <FIG> may be used in RF coil unit <NUM> of <FIG> and may be coupled to a downstream component of the MRI system, such as the controller unit <NUM>. The RF coil may be placed in the bore of the MRI system in order to receive the MR signals during the imaging session, and thus may be in proximity to the transmit RF coil (e.g., the body RF coil unit <NUM> of <FIG>). The controller unit may store instructions in non-transitory memory that are executable to generate an image from an imaging subject positioned in the bore of the MRI system during an MR imaging session. To generate the image, the controller unit may store instructions to perform a transmit phase of the MR imaging session. During the transmit phase, the controller unit may command (e.g., send signals) to activate the transmit RF coil(s) in order to transmit one or more RF pulses. To prevent interference leading to B<NUM> field distortion during the transmit phase, the receive RF coil(s) may be decoupled during the transmit phase. The controller unit may store instructions executable to perform a subsequent receive phase of the MR imaging session. During the receive phase, the controller unit may obtain MR signals from the receive RF coil(s). The MR signals are usable to reconstruct the image of the imaging subject positioned in the bore of the MRI system.

<FIG> schematically shows a dissembled view <NUM> of a neck RF coil assembly comprising three separate RF coil arrays in accordance with a first exemplary embodiment. In the dissembled view <NUM>, the three RF coil arrays are shown separately and are not overlapped with each other. The RF coil assembly includes two peripheral RF coil arrays and a central RF coil array, each comprising a plurality of RF coils similar to the RF coil <NUM> described above with respect to <FIG>. Each RF coil array includes a substrate to which the RF coils are attached. When the substrates of each of the RF coil arrays are stacked upon each other, an assembled neck RF coil assembly <NUM> is formed, as shown in <FIG>.

The central RF coil array <NUM> includes a plurality of RF coils <NUM> distributed in a partially-overlapping manner along a central longitudinal axis of a first substrate layer <NUM>. For example, the plurality of RF coils <NUM> includes a first RF coil <NUM>. The first RF coil <NUM> is a non-limiting example of the RF coil <NUM> illustrated in <FIG> and described above, and includes a loop portion <NUM> (e.g., comprised of least two parallel, distributed capacitance wire conductors encapsulated and separated by a dielectric material) and a coupling electronics portion <NUM>. The coupling electronics portion <NUM> may include a pre-amplifier, a decoupling circuit, and an impedance inverter circuit, as described above. Each RF coil of the plurality of RF coils <NUM> may be configured similarly to first RF coil <NUM>, e.g., comprised of a loop portion and coupling electronics portion. As shown, the plurality of RF coils <NUM> includes ten RF coils, but other configurations are possible, such as eight RF coils. Each loop portion of each RF coil may have the same diameter. In an example, each diameter may be <NUM>. The loop portions may partially overlap along the first substrate layer <NUM>. For example, a bottom segment of the first RF coil <NUM> (such as the bottom <NUM>% of the loop portion <NUM>) may overlap with a top segment of the RF coil positioned adjacent to the first RF coil <NUM> (e.g., the loop portion <NUM> may overlap the top <NUM>% of the loop portion of the RF coil positioned adjacent to the first RF coil). Each RF coil may overlap with neighboring RF coils of the plurality of RF coils <NUM> by an equal amount. In this way, the RF coils may be distributed equally along the length of the first substrate layer <NUM> in an overlapping manner.

Each RF coil of the plurality of RF coils <NUM> fully overlaps with the first substrate layer <NUM>. For example, the first substrate layer <NUM> may have a width that is wider than the diameter of the RF coils and a length that is longer than a total length of the plurality of RF coils <NUM> (when the RF coils are distributed as described above). Further, each loop portion of each RF coil may at least partially contact the first substrate layer <NUM> along the circumference of the loop portion. Each RF coil may be coupled to the first substrate layer in a suitable manner, such as via stitching. While only one first substrate layer <NUM> is shown (e.g., underneath the plurality of RF coils <NUM>), in some examples, central RF coil array <NUM> may include a second sheet or layer of substrate (e.g., positioned on top of the plurality of RF coils <NUM>). Further, while <FIG> shows the loop portions and coupling electronics portions being coupled to the same side of the first substrate layer <NUM>, in some examples, the coupling electronics portions may be coupled to an opposite side of the first substrate layer <NUM>, and the substrate layer may include holes through which each loop portion may extend in order to facilitate the loop portions being coupled to the respective electronics portions.

Additionally, a coil-interfacing cable <NUM> extends between each coupling electronics portion and an RF coil interfacing connector. Each of the electrical wires coupled to the coupling electronics portions may be housed together (e.g., bundled together) within the coil-interfacing cable <NUM> and electrically coupled to the connector. The connector may interface with the MRI system (e.g., electrically couple with the MRI system by plugging into an input of the MRI system) in order to output signals from the RF coils to the MRI system, and the MRI system may process the signals received from the RF coils via the connector in order to produce images of the body of the patient (e.g., images of the anatomical features of the patient to be imaged by the central RF coil array <NUM>).

The neck RF coil assembly further includes a first peripheral RF coil array <NUM> that includes two rows of RF coils (first row <NUM> and second row <NUM>) distributed along respective axes parallel to the central longitudinal axis at respective edges of a second substrate layer <NUM>. First row <NUM> includes five RF coils and second row <NUM> includes five RF coils for a total of ten RF coils, but other numbers of RF coils are possible. First row <NUM> includes a first RF coil <NUM> that includes a loop portion <NUM> and a coupling electronics portion <NUM>, similar to the RF coil <NUM> described above with respect to <FIG>. Each RF coil of the first peripheral RF coil array <NUM> may be configured similarly (e.g., including a loop portion and a coupling electronics portion). Each loop portion of each RF coil of the first peripheral RF coil array <NUM> may have the same diameter. In an example, each diameter may be larger than the diameter of the RF coils of the central RF coil <NUM>, for example, the diameter may be <NUM>.

Each of the two rows of RF coils are coupled along a respective edge of the second substrate layer <NUM>. For example, each RF coil of first row <NUM> may be coupled along a first edge of the second substrate layer <NUM> (e.g., a first long edge) and each RF coil of second row <NUM> may be coupled along a second edge of the second substrate layer (e.g., a second long edge). A center strip of the second substrate layer <NUM> may be free from RF coils loop portions. Each RF coil of the two rows may be coupled to the second substrate layer <NUM> only along a relatively small segment of the respective loop portions, thereby forming what is referred to herein as an "open loop" RF coil arrangement. For example, for a given loop portion, a segment that comprises <NUM>-<NUM>% of the circumference of that loop portion may contact and/or be positioned over the second substrate layer <NUM>, while the remaining segment of that loop portion (e.g., the remaining <NUM>-<NUM>% of the loop portion) may be open to ambient, at least in some examples. Further, the RF coils may be distributed along the second substrate layer <NUM> in a non-overlapping manner so that none of the loop portions of the first row overlap with neighboring loop portions of the first row, and none of the loop portions of the second row overlap with neighboring loop portions of the second row. In this way, the loop portions may move independently of each other and partially independently of the second substrate layer <NUM>. For example, each loop portion may flex/bend around a respective contact point where that loop portion contacts the substrate.

Additionally, a coil-interfacing cable <NUM> extends between each coupling electronics portion and an RF coil interfacing connector. Each of the electrical wires coupled to the coupling electronics portions may be housed together (e.g., bundled together) within the coil-interfacing cable <NUM> and electrically coupled to the connector. The connector may interface with the MRI system (e.g., electrically couple with the MRI system by plugging into an input of the MRI system) in order to output signals from the RF coils to the MRI system, and the MRI system may process the signals received from the RF coils via the connector in order to produce images of the body of the patient (e.g., images of the anatomical features of the patient to be imaged by the first peripheral RF coil array <NUM>).

The neck RF coil assembly may further include a second peripheral RF coil array <NUM> that is configured similarly as the first peripheral RF coil array <NUM>, including two rows of RF coils (e.g., first row <NUM> and second row <NUM>) distributed along respective edges of a third substrate layer <NUM> in an open loop RF coil arrangement (e.g., such that only a small segment (e.g., <NUM>% of a circumference) of each loop portion contacts/extends over the third substrate layer and the majority of each loop portion does not contact or extend over the third substrate layer). The second peripheral RF coil array <NUM> may include a greater number of RF coils than the first peripheral RF coil array <NUM> (e.g., <NUM> RF coils versus <NUM> RF coils). Each RF coil of the second peripheral RF coil array <NUM> may be configured similarly to the RF coil described above with respect to <FIG>. For example, first row <NUM> includes an RF coil <NUM> comprised of a loop portion <NUM> and a coupling electronics portion <NUM>. The second peripheral RF coil array <NUM> may include a coil interfacing cable <NUM> coupling each coupling electronics portion of the second peripheral RF coil array <NUM> to a connector, as explained above. In some examples, each coil interfacing cable of the neck RF coil assembly <NUM> may connect to a common connector that is configured to couple to a suitable port (which may be positioned on the table on which the subject to be imaged is positioned, such as table <NUM> of <FIG>). In other examples, each coil-interfacing cable may connect to a separate connector, and each connector may couple to a respective (or the same) port on the MRI system (e.g., on the table).

<FIG> schematically shows the neck RF coil assembly <NUM> when the first peripheral RF coil array <NUM> and the second peripheral RF coil array <NUM> are stacked together and the central RF coil array <NUM> is stacked on top of the first and second peripheral RF coil arrays. The RF coils of the central RF coil array <NUM> may be facing outward, as shown (some detail, such as the coupling electronics parts and coil interfacing cables, have been removed from <FIG> for visual purposes). The center strips of the second and third substrate layers of the peripheral RF coil arrays may align and overlap with the first substrate layer <NUM> and the plurality of RF coils <NUM> of the central RF coil array. Both the first row <NUM> of the first peripheral RF coil array and the first row <NUM> of the second peripheral RF coil array may overlap each other and extend outward in a first direction from the overlapping substrate layers. The RF coils of the first row <NUM> and the first row <NUM> may be staggered relative to each other. For example, loop portion <NUM> and loop portion <NUM> may substantially overlap, with one half of loop portion <NUM> overlapping with one half of loop portion <NUM>; the other half of loop portion <NUM> may overlap with the next loop portion of first row <NUM>. Collectively, first row <NUM> and first row <NUM> may form an upper RF coil array <NUM> that extends outward from central RF coil array <NUM> and, in the example shown, comprises eleven staggered RF coils. The upper RF coil array <NUM> includes a plurality of overlapped RF coils that are coupled along a first (e.g., upper) edge of a substrate section, where the substrate section is comprised of the first substrate layer <NUM>, the second substrate layer <NUM>, and the third substrate layer <NUM>. Each RF coil of the upper RF coil array <NUM> may contact and/or be co-extensive with the substrate section only along a small portion of the loop portion of that RF coil, and the remaining portion of the loop portion may not contact or be co-extensive with the substrate section.

Both the second row <NUM> of the first peripheral RF coil array and the second row <NUM> of the second peripheral RF coil array may overlap each other and extend outward in a second, opposite direction from the overlapping substrate layers. The RF coils of the second row <NUM> and the second row <NUM> may be staggered relative to each other. For example, each loop portion of second row <NUM> may overlap with part (e.g., half) of one loop portion of second row <NUM> and with part (e.g., half) of another loop portion of second row <NUM>. Collectively, second row <NUM> and second row <NUM> may form a lower RF coil array <NUM> that extends outward from central RF coil array <NUM> and, in the example shown, comprises eleven staggered RF coils. The lower RF coil array <NUM> includes a plurality of overlapped RF coils that are coupled along a second (e.g., lower) edge of the substrate section. Each RF coil of the lower RF coil array <NUM> may contact and/or be co-extensive with the substrate section only along a small portion of the loop portion of that RF coil, and the remaining portion of the loop portion may not contact or be co-extensive with the substrate section.

As explained above, the RF coils of the central RF coil array <NUM> fully overlap with the first substrate layer (and hence the substrate section). As a result, the RF coils of the central RF coil array may be configured to bend or flex along with the substrate section at a plurality of axes that are perpendicular to the central longitudinal axis <NUM> of the neck RF coil assembly <NUM>. For example, the central longitudinal axis <NUM> may be parallel to the Y axis of the coordinate system illustrated in <FIG>, and the RF coils of the central RF coil array <NUM> may be configured to bend at a plurality of axes that are each parallel to the X axis of the coordinate system. However, due to the coupling of the RF coils of the central RF coil array <NUM> to the first substrate layer <NUM>, the central RF coil array <NUM> may be constrained and may not bend (or bend less than the bending in the axes perpendicular to the central longitudinal axis) at the central longitudinal axis <NUM> or any other axes parallel to the Y axis. Likewise, the central RF coil array <NUM> may not bend (or bend more than a small amount) at axes parallel to the Z axis.

In contrast, the RF coils of the upper RF coil array <NUM> and the RF coils of the lower RF coil array <NUM> may only overlap with the substrate layers of the substrate section along a small segment of the respective loop portions of the RF coils. The remaining segments of the loop portions may not be constrained by the substrate section. Thus, the RF coils of the upper RF coil array <NUM> and the RF coils of the lower RF coil array <NUM> may bend and flex in multiple planes, and may bend and flex in more planes than the RF coils of the central RF coil array <NUM>. For example, when the neck RF coil assembly is in a flat, first configuration, as shown in <FIG>, the RF coils of the upper and lower RF coil arrays may extend along a first plane with the central RF coil array (such as the x-y plane shown in <FIG>). When the neck RF coil assembly <NUM> is positioned in a second, imaging configuration, such as around a neck of a subject to be imaged (as shown in <FIG> and explained in more detail below), the RF coils of the upper and lower RF coil arrays may bend or flex along with the substrate section to conform to the annular shape formed by the central RF coil array, and also may move out of a respective plane defined by the substrate section to accommodate the anatomical features/geometries of the body of the subject to be imaged. The RF coils may bend at respective contact points where the RF coils couple to a respective substrate layer and may be in a plane that is angled with respect to the respective plane defined by the substrate section. The RF coils may be configured to move into a range of angled planes where the range of angles is -<NUM>° to <NUM>° or other suitable angle ranges. Each RF coil of the upper and lower RF coil arrays move independently of each other.

It should be understood that the first and second peripheral RF coil arrays and the central RF coil array are explained separately for the purpose of clarity. In some embodiments, at least two of the RF coils may be coupled to the same substrate (e.g., made of flexible fabric material). For example, in some embodiments, the first and second peripheral RF coil arrays are coupled to the same substrate, overlapping with each other in the way as discussed above. In some embodiments, the first and second peripheral RF coil arrays are coupled to the same substrate to which the central RF coil array is attached, all coil arrays overlapping in the way as discussed above.

<FIG> show the neck RF coil assembly <NUM> in the imaging configuration (e.g., being worn by a subject to be imaged, such as a patient or other human subject). <FIG> shows a side view <NUM> of a subject <NUM> wearing the neck RF coil assembly <NUM> and <FIG> shows a back view <NUM> of the subject <NUM> wearing the neck RF coil assembly <NUM>. When the neck RF coil assembly <NUM> is wrapped around the subject's neck, the central RF coil array <NUM> may extend around and conform to the subject's neck. The central RF coil array <NUM> may bend along a plurality of axes to conform to an annular shape that matches the shape of the outer surface of the neck.

The upper RF coil array <NUM> may extend upward from the neck and toward the ears of the subject, wrapping around the chin/lower head region of the subject. The lower RF coil array <NUM> may extend downward from the neck and toward the chest/shoulders of the subject, wrapping around the lower neck/upper chest region of the subject. Due to the open loop arrangement of the RF coils of the upper and lower RF coil arrays, the RF coils of the upper and lower RF coil arrays may be bendable and are free to move to conform to the contours of the subject's neck, chin, face, chest, and so forth. The RF coils may include sufficient rigidity, however, to maintain the RF coils in close contact with the subject's body. As exemplified in <FIG>, a tangent plane may be defined by the substrate section (e.g., first substrate layer <NUM>) at an axis <NUM> tangent to the circle formed by the central RF coil array <NUM> and perpendicular to the central longitudinal axis <NUM>. A loop portion of the central RF coil array <NUM> that intersects the axis <NUM> (loop portion <NUM>) extends along with the substrate in the tangent plane. However, a loop portion of the lower RF coil array (loop portion <NUM>) bends out of the tangent plane and is in a plane <NUM> that is angled relative to the tangent plane, such as angled outward in the negative z direction at an angle of <NUM>° relative to the tangent plane. Loop portion <NUM> may bend along a contact point where loop portion <NUM> couples to the substrate section of assembly <NUM>, such as at an edge of the first substrate layer <NUM> and/or where loop portion <NUM> couples to either the second substrate layer or third substrate layer (which may be positioned below first substrate layer <NUM> in <FIG> and thus are not visible).

As appreciated by <FIG>, each RF coil loop portion of the upper and lower RF coil arrays may bend at an appropriate angle to accommodate underlying patient anatomy, and each loop portion of the upper and lower RF coil arrays may move/bend/flex independently of the other loop portions of the upper and lower RF coil arrays. The loop portions of the RF coils of the central RF coil array, however, may be constrained by the substrate section and as such may be more flexible along axes perpendicular to the longitudinal axis (e.g., the short direction) than along axes parallel to the longitudinal axis (e.g., the long direction). For example, along a circumference of the substrate section formed when the neck RF coil assembly <NUM> is wrapped around the subject's neck, the RF coils of the central RF coil array may bend to conform to the annular shape of the substrate section, but at any plane defined by the substrate section, the RF coils of the central RF coil array may not bend out of the plane but may conform to the substrate section, which may not bend significantly in the long direction defined by the central longitudinal axis. The RF coils of the upper and lower RF coil arrays may likewise bend to conform to the annular shape, and may also bend out of any planes defined by the substrate section.

While <FIG> show the plurality of RF coils of the central RF coil array <NUM> as being positioned on an outside of the assembly <NUM> when the assembly is worn by subject <NUM>, in some examples the assembly <NUM> may be flipped so that the plurality of RF coils of the central RF coil assembly <NUM> are positioned on an inside of the assembly <NUM> and thus in contact (whether directly or indirectly via an overlaying substrate layer) with the neck of the subject <NUM>. Further still, while each loop portion of the upper and lower RF coil arrays are shown as being uncovered (e.g., not covered by, coupled to, or in contact with a cover made of, for example, fabric material), in some examples one or more of the loop portions of the RF coils of the upper and/or lower RF coil arrays may be coupled to, covered by, or in contact with a cover, which may help to protect the RF coils and/or the imaging subject. The covers may be comprised of the same or different material than the substrate layers comprising the substrate section. The covers may cover one or both sides of the loop portions.

The substrate layers (e.g., first substrate layer <NUM>, second substrate layer <NUM>, and third substrate layer <NUM>) may be formed of a flexible fabric material that is transparent to RF signals. In one example, the substrate layers of the neck RF coil assembly <NUM> may be formed of one or more layers of Nomex® material.

In this way, the neck RF coil assembly <NUM> may be configured to conform to the neck while also accommodating the flaring out of the subject anatomy away from the neck (e.g., toward the head and toward the chest). This flexible and conformable nature of the RF coil assembly is provided by the central RF coil array, which can be wrapped around the neck and is sized and shaped to match the neck. For example, the central RF coil array may include ten overlapping RF coils each with a diameter of six cm, which may provide for a total RF coil coverage of <NUM>-<NUM> (depending on the level of overlap) along the longitudinal axis, which may correspond to an average neck size. To accommodate subjects with different neck sizes, the ends of the central RF coil array may overlap when wrapped around the neck, and/or more or fewer RF coils may be included or the RF coils may be smaller or larger. The flexible and conformable nature of the assembly is further provided by the upper and lower RF coil arrays, which can bend independently of each other and semi-independently of the substrate section of the assembly. To accommodate the flaring nature of the anatomy, according to the invention, the upper and lower RF coil assemblies are each comprised of RF coils that have a larger diameter than the RF coils of the central RF coil array, and at least in the example shown, may each include more RF coils than the central RF coil array. In this way, the upper and lower RF coil arrays may provide RF coil coverage over the head and chest regions, respectively, which may each have a larger diameter than the more narrow neck region.

<FIG> schematically shows an RF coil array <NUM> that may be included as part of a neck RF coil assembly in accordance with a second exemplary embodiment that is not claimed. RF coil array <NUM> includes a plurality of RF coils, and each RF coil is similar to RF coil <NUM> described above with respect to <FIG> (e.g., includes a loop portion and coupling electronics portion). The RF coil array <NUM> includes three sections: a head section (or upper section), a neck section (or central section), and a chest section (or lower section). Each section includes a plurality of RF coils arranged in a row, and each section partially overlaps with at least one other section. The head section is configured to wrap around a jaw/lower head region of a subject to be imaged (e.g., a patient or other human subject), the neck section is configured to wrap around a neck of the subject, and the chest region is configured to be positioned on an anterior upper chest region of the subject. Further, the RF coil array <NUM> optionally includes a chin coil configured to be positioned over a chin of the subject.

The head section of the RF coil array includes a first plurality of RF coils arranged in a row. As shown in <FIG>, the head section includes four head RF coils and one chin RF coil, although the chin RF coil is optional. When included, the chin RF coil includes a loop portion <NUM> and coupling electronics portion <NUM>. A first head RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, a second head RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, a third head RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, and a fourth head RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>. The RF coils of the head section partially overlap with one another. For example, loop portion <NUM> partially overlaps with loop portion <NUM>. When the chin RF coil is omitted, a gap without any RF coils may be present between loop portion <NUM> and loop portion <NUM>. When included, loop portion <NUM> partially overlaps with loop portion <NUM> and loop portion <NUM>. Loop portion <NUM> may have a larger diameter than the other loop portions in the head section, and the other loop portions in the head section may all have the same diameter.

The neck section of the RF coil array includes a second plurality of RF coils arranged in a row. As shown in <FIG>, the neck section includes six neck RF coils. A first neck RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, a second neck RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, a third neck RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, a fourth neck RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, a fifth neck RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, and a sixth neck RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>. The RF coils of the neck section partially overlap with one another. For example, loop portion <NUM> partially overlaps with loop portion <NUM>. Further, each loop portion of the neck section overlaps with at least one loop portion of the head section. For example, loop portion <NUM> partially overlaps with loop portion <NUM>, loop portion <NUM> partially overlaps with loop portion <NUM> and loop portion <NUM>, and so forth. Each loop portion in the neck section may have the same diameter as the other loop portions in the neck section.

The chest section of the RF coil array includes a third plurality of RF coils arranged in a row. As shown in <FIG>, the chest section includes five chest RF coils. A first chest RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, a second chest RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, a third chest RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, a fourth chest RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>, and a fifth neck RF coil includes a loop portion <NUM> and a coupling electronics portion <NUM>. The RF coils of the chest section partially overlap with one another. For example, loop portion <NUM> partially overlaps with loop portion <NUM>. Further, each loop portion of the chest section overlaps with at least one loop portion of the neck section. For example, loop portion <NUM> partially overlaps with loop portion <NUM>. Each loop portion in the chest section may have the same diameter as the other loop portions in the chest section.

Thus, the RF coil array <NUM> is arranged into three rows of RF coils in an overlapping manner (e.g., where the RF coils of a given row partially overlap with each other along the row, and where the RF coils of two adjacent rows partially overlap with each along an interface between the rows). Other than the chin RF coil, each other RF coil of the RF coil array <NUM> may be equal in size and may be spaced apart from neighboring RF coils by an equal amount. In this way, an equal and uniform amount of decoupling may be present between each RF coil. However, in other examples, different RF coils may have different sizes and/or may be spaced apart by different amounts. While not shown in <FIG>, each RF coil of the RF coil array <NUM> is coupled to a coil interfacing cable that couples each coupling electronics portion to a connector, as explained above with respect to <FIG>.

To facilitate close coupling of each RF coil of the RF coil array <NUM> around the complicated geometry of the head, neck, and chest region, the RF coil array <NUM> may be coupled to inner surfaces of a semi-rigid pillow. The semi-rigid pillow may be shaped similar to a neck pillow, and may include a chest region configured to cover an anterior region of a chest, a first side flap configured to extend from a lower face region (e.g., a cheek) around a first side of a neck, and a second side flap configured to extend from the lower face region (e.g., the other check) around a second side of the neck. The semi-rigid pillow may further include a neck region coupling the chest region to the first side flap and the second side flap, and in some examples, a chin flap. Each region/flap of the semi-rigid pillow may include at least one RF coil of the RF coil array <NUM>. During imaging, the semi-rigid pillow may be placed over the anterior chest and neck of the subject, in a manner similar to a reverse neck pillow.

<FIG> show various views of a neck RF coil assembly <NUM> that includes the RF coil array <NUM> coupled to a semi-rigid pillow. <FIG> is a back view <NUM> of the pillow, where inner surfaces of the chest region and neck region are visible. The semi-rigid pillow incudes a chin flap <NUM>, a first side flap <NUM>, a second side flap <NUM>, a neck region <NUM>, and a chest region <NUM>. Each region and flap of the semi-rigid pillow may be made of a conformable/flexible material such as foam. RF coil array <NUM> is distributed across inner surfaces of the semi-rigid pillow. For example, as shown in <FIG>, the RF coils of the chest section are distributed across the chest region <NUM>, such that loop portion <NUM>, loop portion <NUM>, loop portion <NUM>, loop portion <NUM>, and loop portion <NUM> are coupled to chest region <NUM>. At least a portion of the RF coils of the neck section are coupled to neck region <NUM>, such as loop portion <NUM> and loop portion <NUM>, as shown in <FIG>. The RF coils of the head portion are coupled across the two side flaps. For example, in <FIG>, loop portion <NUM> is coupled to first side flap <NUM> and loop portion <NUM> is coupled to second side flap <NUM>. Loop portion <NUM> is coupled to chin flap <NUM>.

<FIG> shows a top isometric view <NUM> of the neck RF coil assembly <NUM>. As illustrated in <FIG>, each side flap includes RF coils of the head section and of the neck section of the RF coil array <NUM>. For example, the second side flap <NUM> is coupled to loop portion <NUM> and loop portion <NUM> of the head section, and to loop portion <NUM> and loop portion <NUM> of the neck section. As shown in the top view <NUM> of the neck RF coil assembly <NUM> shown in <FIG>, the first side flap <NUM> is likewise be coupled to two RF coils of the head section (loop portion <NUM> and loop portion <NUM>) and two RF coils of the neck section of the RF coil array <NUM> (loop portion <NUM> and loop portion <NUM>). Further, <FIG> show that two RF coils of the neck section (e.g., loop portion <NUM> and loop portion <NUM>) are coupled to the neck region and extend/bend over onto the chin flap <NUM>.

As shown in <FIG>, the semi-rigid pillow includes a plurality of protrusions which may accommodate internal electronics of the RF coil array. For example, first side flap <NUM> includes a first protrusion <NUM> and a second protrusion <NUM>. Chest region <NUM> includes a third protrusion <NUM>, which may extend across an entirety of the chest region <NUM>. While not shown in <FIG>, the second side flap <NUM> may also include two protrusions similar to the first side flap <NUM>. Additionally, some areas of the semi-rigid pillow may be angled relative to other regions in order to conform to underlying patient anatomy. For example, first side flap <NUM> includes a flex region <NUM> where the first side flap bends inward such that the flex region <NUM> is angled (e.g., at an angle of <NUM>-<NUM>°) relative to the remaining portion of the first side flap <NUM>. The second side flap <NUM> likewise includes a flex region <NUM> that bends inward relative to the rest of the second side flap. Loop portion <NUM> may bend to conform to the shape of the second side flap, such that loop portion <NUM> includes a first portion that is flat and aligned with a plane defined by the inner surface of the second side flap (e.g., a z-y plane) and a second portion that is angled inward relative to the first portion. Chin flap <NUM> may also bend inward, and loop portion <NUM> may bend to conform to the shape of the chin flap.

<FIG> shows another top isometric view <NUM> of the neck RF coil assembly <NUM>. In the view <NUM>, the semi-rigid pillow is made partially transparent so that inner electronics of the RF coil array <NUM> are visible. As shown, coupling electronics portion <NUM> and coupling electronics portion <NUM> of the head section of the RF coil array <NUM> are included in the first protrusion of the first side flap <NUM>; the coupling electronics portions of the other RF coils of the head section are likewise included in the second side flap. A coupling electronics portion <NUM> of the neck section is also shown in the second protrusion of the first side flap <NUM>. A coupling electronics portion of the neck section (coupling electronics portion <NUM>) is shown as being included in the neck region <NUM> and/or chin flap <NUM>, as well as coupling electronics portion <NUM>. The coupling electronics portions of the chest section are included in the third protrusion of the chest region <NUM>, including coupling electronics portion <NUM>, coupling electronics portion <NUM>, coupling electronics portion <NUM>, coupling electronics portion <NUM>, and coupling electronics portion <NUM>. Further, coupling electronics portion <NUM> (which is part of an RF coil of the neck section) is also positioned in the chest region <NUM>. Also included in the inner electronics is a plurality of baluns, such as balun <NUM>. Neck RF coil assembly <NUM> further includes a coil interfacing cable <NUM> coupled to a connector <NUM>, similar to the coil interfacing cable and connector described above with respect to <FIG> (e.g., the coil interfacing cable may be coupled to each coupling electronics portion, and each balun shown in <FIG> may be included as part of the coil interfacing cable). The coil interfacing cable <NUM> may exit the semi-rigid pillow at one of two possible locations. In a first embodiment, the coil interfacing cable <NUM> may exit the semi-rigid pillow on a bottom of the first side flap <NUM> and connect to connector <NUM>, which may be configured to couple to a port on the table on which the subject to be imaged may be positioned (such as table <NUM> of <FIG>). In some examples, as shown in <FIG> and explained below, the neck RF coil assembly <NUM> may be used in concert with a head RF coil configured to be placed around the head of the imaging subject. The head RF coil may be configured to connect to two ports on the table, and due to the number of channels in the head RF coil (e.g., <NUM>), a plurality of channels (e.g., <NUM>) of one of the ports on the table may be available. In such examples, connector <NUM> may be configured to connect to the port on the table that may also be coupled to a portion of the channels of the head RF coil. In a second embodiment, the coil interfacing cable <NUM> may exit the semi-rigid pillow near the top, on one (or in some examples, both) of the sides of the semi-rigid pillow, and couple to connector <NUM>. In the second embodiment, connector <NUM> may be configured to couple to a port positioned in the head RF coil (shown in <FIG>).

The semi-rigid pillow may be comprised of a suitable material that is transparent to RF signals and maintains desired rigidity while allowing some flexibility and conformability, such as polyurethane foam, polystyrene, nylon, or other suitable material. In some examples, the different regions and flaps described herein may be comprised of different pieces of material that are coupled together to form the semi-rigid pillow. When separate pieces of material are coupled together, they pieces may be coupled together using adhesive, thermal welding, or other non-rigid coupling mechanism, thereby avoiding the use of rigid joints, hinges, or other mechanisms. In other examples, two or more of the regions and/or flaps described herein may be comprised of a single piece of material. For example, the entire pillow may be made from one piece of material that is cut/shaped to form the final pillow. The internal electronics (e.g., coupling electronics portions, baluns, coil-interfacing cable) may be embedded within the material (e.g., embedded within the foam) and the loop portions may be coupled on surfaces of the material. The semi-rigid pillow may be covered in an outer cover to protect the internal components and maintain sterility, where the cover is thin and flexible (e.g., formed of a flexible material that is transparent to RF signals, such as one or more layers of Nomex® material or Nomex Nano® material). In still other examples, the semi-rigid pillow may be comprised of an outer substrate that is shaped as shown herein once filled with a filler material, where the filler material is comprised of discrete particles.

<FIG> show the neck RF coil assembly <NUM> positioned over a subject to be imaged. In a first view <NUM> of <FIG>, the neck RF coil assembly <NUM> is positioned over a subject <NUM> that is lying on a table (in some examples, the table may include additional RF coils to image a posterior of the subject). The chest region <NUM> is positioned over an anterior upper chest of the subject, the first side flap <NUM> extends from a cheek of the patient around a side of the neck of the subject, the second side flap <NUM> extends from the other cheek of the patient around the other side of the neck of the subject, and the neck region <NUM> is positioned over the anterior part of the neck. The chin flap <NUM> extends upward from the neck region <NUM> and over the chin of the subject. As appreciated by second view <NUM> of <FIG>, the neck RF coil assembly <NUM> may be used together with a traditional head coil assembly, such as head coil assembly <NUM>, in order to image the entirety of the subject's head, neck, and cervical spine region.

A technical effect of the neck RF coil assemblies described herein is increased depth of imaging of the head, neck, and spine region.

Claim 1:
A radio frequency, RF, coil assembly for a magnetic resonance imaging, MRI, system, comprising:
a central RF coil array (<NUM>) including a first plurality of RF coils configured to cover a neck of a subject to be imaged;
an upper RF coil array (<NUM>) including a second plurality of RF coils extending upward from the central RF coil array (<NUM>) and configured to cover a lower head region of the subject; and
a lower RF coil array (<NUM>) including a third plurality of RF coils extending downward from the central RF coil array (<NUM>) and configured to cover an upper shoulder region of the subject,
wherein each RF coil of the first, second, and third pluralities of RF coils comprises a loop portion comprising two distributed capacitance parallel wire conductors encapsulated and separated by a dielectric material to form a respective distributed capacitance along the length of the loop portion and wherein each loop portion of the first plurality of RF coils has a first diameter, each loop portion of the second plurality of RF coils has a second diameter, and each loop portion of the third plurality of RF coils has a third diameter, the second diameter and the third diameter being larger than the first diameter.