Coil element of radio frequency coil using bundles of conductive fibers wound together

Abstract

A radio frequency (RF) receive coil assembly for a magnetic resonance imaging (MRI) system includes a flexible housing. The RF receive coil assembly also includes a flexible anchoring material disposed within the flexible housing. The radio frequency coil assembly further comprises a radio frequency coil arranged in the flexible shell. The radio frequency coil includes a plurality of flexible coil elements coupled to the flexible anchoring material. Each flexible coil element of the plurality of flexible coil elements includes a plurality of conductive fiber bundles wound together. Each bundle of the plurality of bundles includes a plurality of electrically conductive fibers.

Description

Background Art

[0001] The subject matter disclosed herein relates to medical imaging, and more particularly to a radio frequency receive coil assembly that includes a radio frequency coil having a coil element made of a bundle of conductive fibers wound together.

[0002] Non-invasive imaging techniques allow for obtaining images of the internal structures or features of a patient / object without performing an invasive procedure on the patient / object. Specifically, such non-invasive imaging techniques rely on various physical principles (such as differential transmission of X-rays through a target volume, reflection of acoustic waves within a volume, paramagnetism of different tissues and materials within a volume, decay of a target radionuclide within the body, etc.) to acquire data and construct an image or otherwise represent the observed internal features of the patient / object.

[0003] During magnetic resonance imaging, when a substance such as human tissue is subjected to a uniform magnetic field (polarizing field B0), the individual magnetic moments of the spins in the tissue attempt to align with the polarizing field, but precess around the polarizing field in a random order at their characteristic Larmor frequency. If the substance or tissue is subjected to a magnetic field (excitation field B1) in the x-y plane and near the Larmor frequency, then the net alignment torque or "longitudinal magnetization" M z can be rotated or "tilted" into the x-y plane to produce a net transverse magnetic moment M t . After the excitation signal B1 terminates, the signal emitted by the excited spins can be received and processed to form an image.

[0004] When using these signals to generate an image, magnetic field gradients (G x , G y and G z ) are employed. Typically, the region to be imaged is scanned in a series of measurement cycles in which these gradient fields vary according to the particular positioning method used. The resulting set of received nuclear magnetic resonance (NMR) signals is digitized and processed to reconstruct an image using one of the well-known reconstruction techniques.

[0005] Coil arrays typically utilize wire-based or printed circuit board-based coil elements. Thus, the possible configurations of conventional coil elements are limited. In addition, the flexibility (if any) of conventional coil elements is also limited. Additionally, conventional coil arrays are more costly and heavier. Summary of the Invention

[0006] An overview of certain embodiments disclosed herein is presented below. It should be understood that these aspects are provided merely to give the reader a brief overview of these particular embodiments and are not intended to limit the scope of the present disclosure. Indeed, the present disclosure may cover various aspects that may not be shown below.

[0007] In one embodiment, a radio frequency (RF) receive coil assembly for a magnetic resonance imaging (MRI) system is provided. The RF receive coil assembly includes a flexible housing. The RF receive coil assembly also includes a flexible anchoring material disposed within the flexible housing. The RF coil assembly further includes an RF coil disposed within the flexible housing. The RF coil includes a plurality of flexible coil elements coupled to the flexible anchoring material. Each of the plurality of flexible coil elements includes a plurality of bundles of conductive fibers wound together. Each of the plurality of bundles includes a plurality of conductive fibers.

[0008] In another embodiment, a method of manufacturing a radio frequency (RF) receive coil assembly for a magnetic resonance imaging (MRI) system is provided. The method includes providing a flexible anchoring material. The method also includes coupling a plurality of flexible coil elements to the flexible anchoring material to form an RF coil. Each of the plurality of flexible coil elements includes a plurality of bundles of conductive fibers wound together. Each of the plurality of bundles includes a plurality of conductive fibers. The method further includes disposing the flexible anchoring material and the RF coil within a flexible housing.

[0009] In another embodiment, a magnetic resonance imaging (MRI) system is provided. The magnetic resonance imaging system includes an imaging portion having an RF receive coil assembly. The RF receive coil assembly includes a flexible housing. The RF receive coil assembly also includes a flexible anchoring material disposed within the flexible housing. The RF receive coil assembly further includes an RF coil disposed within the flexible housing. The RF coil includes a plurality of flexible coil elements sutured to the flexible anchoring material. Each of the plurality of flexible coil elements includes a plurality of bundles of conductive fibers wound together. Each of the plurality of bundles includes a plurality of conductive fibers. The plurality of bundles of conductive fibers wound together are used as thread for suturing the plurality of flexible coil elements to the flexible anchoring material. BRIEF DESCRIPTION OF THE DRAWINGS

[0010] These and other features, aspects, and advantages of the subject matter of the present invention will be better understood when the following detailed description is read with reference to the accompanying drawings, in which like reference symbols represent like parts throughout the drawings, wherein:

[0011] Figure 1 An embodiment of a magnetic resonance imaging (MRI) system suitable for use with the disclosed technology is illustrated;

[0012] Figure 2 is a schematic diagram of a radio frequency (RF) coil assembly in accordance with aspects of the present disclosure, the RF coil assembly having coil elements formed using a plurality of bundles of conductive fibers wound together;

[0013] Figure 3 is a schematic cross - sectional view of a conductive fiber (e.g., a bare conductive fiber) according to aspects of the present disclosure;

[0014] Figure 4 is a schematic cross - sectional view of a conductive fiber (e.g., having a non - conductive core) according to aspects of the present disclosure;

[0015] Figure 5 is a schematic cross - sectional view of a bundle of conductive fibers (e.g., a bare bundle) according to aspects of the present disclosure;

[0016] Figure 6 is a schematic cross - sectional view of a bundle of conductive fibers (e.g., having an outer covering) according to aspects of the present disclosure;

[0017] Figure 7 is a schematic cross - sectional view of a coil element having multiple wound filaments (e.g., without an outer covering) according to aspects of the present disclosure;

[0018] Figure 8 is a schematic cross - sectional view of a coil element having multiple wound filaments (e.g., having an outer covering) according to aspects of the present disclosure;

[0019] Figure 9 is an image of an example of a bundle of twisted - together conductive fibers according to aspects of the present disclosure;

[0020] Figure 10 is an image of an example of two bundles of conductive fibers wound by twisting according to aspects of the present disclosure;

[0021] Figure 11 is an image of three bundles of conductive fibers wound by weaving according to aspects of the present disclosure;

[0022] Figure 12 is an image of three bundles of conductive fibers wound by twisting according to aspects of the present disclosure;

[0023] Figure 13 is a schematic view of a conductive element of a radio - frequency coil sutured to a flexible anchoring material (e.g., sutured in a zig - zag pattern) according to aspects of the present disclosure;

[0024] Figure 14 is a schematic view of a part of a conductive element of a radio - frequency coil sutured to a flexible anchoring material according to aspects of the present disclosure;

[0025] Figure 15 is a schematic view of a conductive element of a radio - frequency coil sutured to a flexible anchoring material (e.g., sutured in a linear suture pattern) according to aspects of the present disclosure;

[0026] Figure 16Schematic diagram of a conductive element (e.g., having a rectangular shape) of a radio frequency coil sutured to a flexible anchoring material according to aspects of the present disclosure;

[0027] Figure 17 Schematic diagram of a conductive element (e.g., having a triangular shape) of a radio frequency coil sutured to a flexible anchoring material according to aspects of the present disclosure;

[0028] Figure 18 Schematic diagram of a conductive element (e.g., having a rectangular shape) of a radio frequency coil sutured (e.g., in a zigzag pattern) to a flexible anchoring material according to aspects of the present disclosure;

[0029] Figure 19 Schematic diagram of a conductive element (e.g., having a triangular shape) of a radio frequency coil sutured (e.g., in a zigzag pattern) to a flexible anchoring material according to aspects of the present disclosure;

[0030] Figure 20 Schematic diagram of a conductive element of a radio frequency coil having a multi-turn configuration (e.g., having two turns) sutured to a flexible anchoring material according to aspects of the present disclosure;

[0031] Figure 21 Schematic diagram of a conductive element of a radio frequency coil having a multi-coil configuration (e.g., having three turns) sutured to a flexible anchoring material according to aspects of the present disclosure;

[0032] Figure 22 Flowchart of a method for manufacturing a radio frequency receiving coil assembly according to aspects of the present disclosure;

[0033] Figure 23 Schematic diagram of a coil layout (e.g., for a bilateral arrangement) of a radio frequency coil according to aspects of the present disclosure;

[0034] Figure 24 According to aspects of the present disclosure Figure 23 Schematic diagram of the first side of the radio frequency coil in;

[0035] Figure 25 According to aspects of the present disclosure Figure 23 Schematic diagram of the second side of the radio frequency coil in;

[0036] Figure 26 Schematic diagram of a coil layout (e.g., for a hierarchical arrangement) of a radio frequency coil according to aspects of the present disclosure;

[0037] Figure 27 According to aspects of the present disclosure Figure 26 Schematic diagram of the first set of coil elements on the first layer of the radio frequency coil in;

[0038] Figure 28 According to various aspects of the present disclosure Figure 26 A schematic diagram of a second set of coil elements on a second layer of the radio frequency coil;

[0039] Figure 29 According to various aspects of the present disclosure Figure 26 A schematic diagram of a third group of coil elements on a third layer of the radio frequency coil;

[0040] Figure 30 According to various aspects of the present disclosure Figure 26 A schematic diagram of a fourth group of coil elements on a fourth layer of the radio frequency coil;

[0041] Figure 31 is a cross-sectional view of a pair of elasticized or stretchable conductive fiber bundles 378 in a biaxial configuration; and

[0042] Figure 32 is a schematic diagram of the conductive elements of a radio frequency coil in a biaxial configuration sutured to a flexible anchoring material. DETAILED DESCRIPTION

[0043] One or more specific embodiments will be described below. In order to provide a concise description of these embodiments, not all features of an actual implementation are described in the specification. It should be understood that in the development of any such actual implementation, as in any engineering or design project, many implementation-specific decisions must be made to achieve the developer's specific goals, such as complying with system-related and business-related constraints that may vary from implementation to implementation. In addition, it should be understood that such development efforts may be complex and time-consuming, but are still routine tasks for design, fabrication, and manufacturing for ordinary technicians who benefit from this disclosure.

[0044] When introducing the coil elements of various embodiments of the present subject matter, the articles "a", "an", "the", and "said" are intended to indicate that there are one (kind) or more (kinds) of coil elements. The terms "comprising", "including", and "having" are intended to be inclusive and mean that there may be additional coil elements in addition to the listed coil elements. In addition, any numerical examples in the following discussion are intended to be non-limiting, and thus the additional numerical values, ranges, and percentages are within the scope of the disclosed embodiments.

[0045] The present disclosure provides a coil element of a radio frequency coil utilizing a bundle of conductive fibers wound (e.g., braided, stranded, or woven) together. Specifically, the present disclosure provides a radio frequency coil assembly (e.g., a body coil) for a magnetic resonance imaging system, the radio frequency coil assembly having a coil element (e.g., a loop or a coil) coupled (e.g., sutured) to a flexible anchoring material. Although discussed in the context of a body coil, the disclosed embodiments can be used for magnetic resonance compatible sensors. Although discussed in the context of a body coil being used with a magnetic resonance imaging system, the coil can be used in multi-nuclear applications (e.g., used with a positron emission tomography (PET) / magnetic resonance imaging system).

[0046] The disclosed embodiments include a radio frequency (RF) receiving coil assembly for a magnetic resonance imaging (MRI) system, the radio frequency receiving coil assembly including a flexible housing. The radio frequency coil assembly also includes a flexible anchoring material disposed within the flexible housing. The radio frequency coil assembly further includes a radio frequency coil disposed within the flexible housing. The radio frequency coil includes a plurality of flexible coil elements coupled to the flexible anchoring material. Each flexible coil element of the plurality of flexible coil elements includes a plurality of bundles of conductive fibers wound together. Each bundle of the plurality of bundles includes a plurality of conductive fibers.

[0047] In some embodiments, a plurality of flexible coil elements are sutured to the flexible anchoring material using a plurality of bundles of conductive fibers wound together as a thread. In some embodiments, the plurality of flexible coil elements are sutured to the flexible anchoring material as a top thread. In some embodiments, the plurality of flexible coil elements are sutured to the flexible anchoring material as a bobbin thread. In some embodiments, the plurality of flexible coil elements are sutured to the flexible anchoring material as a top thread and a bobbin thread.

[0048] In some embodiments, the plurality of flexible coil elements are sutured to the flexible anchoring material in a zigzag pattern (or a serpentine pattern), wherein the plurality of flexible coil elements are configured to be stretchable due to the zigzag pattern. In some embodiments (e.g., suturing the flexible coil elements in a zigzag pattern), the flexible anchoring material layer is stretchable. In some embodiments, the plurality of flexible coil elements are sutured to the flexible anchoring material in a linear suture pattern.

[0049] In some embodiments, each of the plurality of conductive fibers (of each fiber bundle) includes a non-conductive core and a conductive sheath disposed around the non-conductive core (e.g., plastic or polymer). In some embodiments, each of the plurality of conductive fibers (of a fiber bundle) includes a conductive core, and a plurality of fiber bundles wound together have a non-conductive sheath disposed around the respective bundle. In some embodiments, each of the plurality of conductive fibers (of a fiber bundle) includes a conductive core, and a plurality of fiber bundles wound together have a non-conductive sheath disposed around the respective bundle. In some embodiments, the plurality of bundles wound together are bare (i.e., the wound fiber bundles have no sheath, such as a shield or dielectric layer).

[0050] In some embodiments, the plurality of flexible coil elements can be made of litz wire, wire bundles, metal wire bundles, coated filament bundles, woven filament bundles, elastomeric or stretchable filament bundles (e.g., where both the filaments and the conductive coating are stretchable), or wire strand bundles. In some embodiments, the conductive fibers can be inherently stretchable. The conductive fibers within each bundle can be wound in a variety of patterns (e.g., woven, braided, or stranded). The bundles are wound in a variety of patterns (e.g., woven, braided, or stranded). In some embodiments, the shape of the flexible coil element can be changed and can be any shape (e.g., oval, circular, square, rectangular, etc.). In some embodiments, the flexible coil element can follow a straight path along the shape. In some embodiments, the flexible coil element can meander (e.g., zigzag) along the shape. In some embodiments, the meandering enables the flexible coil element to be stretchable. In some embodiments, the flexible coil element can be coupled to the flexible anchoring material in a multi-turn configuration (e.g., the number of turns and / or the gaps are variable). In some embodiments (e.g., where the filaments and the conductive coating are stretchable in an elastomeric or stretchable filament bundle), the elastomeric or stretchable filament bundle can be readily incorporated into the stretchable anchoring material with standard straight stitches.

[0051] In some embodiments, the flexible anchoring material layer is stretchable. In some embodiments, the flexible anchoring material layer is made of a heat-dissipating material. In some embodiments, the flexible anchoring material layer is MRI-compatible and does not generate a proton signal. In some embodiments, the flexible anchoring material layer is made of a film (e.g., plastic film). In some embodiments, the flexible anchoring material layer is made of a fabric.

[0052] In some embodiments, the radio frequency (RF) receive coil assembly includes a single-tuned coil (e.g., a single-proton frequency coil). In some embodiments, the RF receive coil includes a multi-tuned coil (e.g., a multi-nuclear coil), where each frequency is transparent to the other frequencies when there is frequency overlap. For example, a first set of flexible coil elements on the flexible anchoring material can be tuned to a first frequency (e.g., for hydrogen), and a second set of flexible coil elements on the flexible anchoring material can be tuned to a second frequency different from the first frequency (e.g., for carbon-13 or multi-nuclear spectroscopy (MNS)).

[0053] In some embodiments, a method of manufacturing a radio frequency (RF) receive coil assembly for a magnetic resonance imaging (MRI) system includes providing a flexible anchoring material. The method also includes coupling a plurality of flexible coil elements to the flexible anchoring material to form an RF coil. Each of the plurality of flexible coil elements includes a plurality of conductive fiber bundles wound together. Each of the plurality of bundles includes multiple conductive fibers. The method further includes disposing the flexible anchoring material and the RF coil within a flexible housing. In some embodiments, coupling the plurality of flexible coil elements to the flexible anchoring material includes stitching the plurality of flexible coil elements to the flexible anchoring material using the plurality of conductive fiber bundles wound together as a thread. In some embodiments, the plurality of flexible coil elements are stitched to the flexible anchoring material as the top thread. In some embodiments, the plurality of flexible coil elements are stitched to the flexible anchoring material as the bobbin thread. In some embodiments, the plurality of flexible coil elements are stitched to the flexible anchoring material as both the top thread and the bobbin thread. In some embodiments, the plurality of flexible coil elements are stitched to the flexible anchoring material in a zigzag pattern (or a serpentine pattern), where the plurality of flexible coil elements are configured to be stretchable due to the zigzag pattern. In some embodiments (e.g., stitching the flexible coil elements in a zigzag pattern), the flexible anchoring material layer is stretchable. In some embodiments, the plurality of flexible coil elements are stitched to the flexible anchoring material in a linear stitch pattern.

[0054] In some embodiments, a magnetic resonance imaging system includes an imaging portion having an RF receive coil assembly. The RF receive coil assembly includes a flexible housing. The RF receive coil assembly also includes a flexible anchoring material disposed within the flexible housing. The RF receive coil assembly further includes an RF coil disposed within the flexible housing. The RF coil includes a plurality of flexible coil elements stitched to the flexible anchoring material. Each of the plurality of flexible coil elements includes a plurality of conductive fiber bundles wound together. Each of the plurality of bundles includes multiple conductive fibers. The plurality of conductive fiber bundles wound together are used as a thread for stitching the plurality of flexible coil elements to the flexible anchoring material.

[0055] The disclosed embodiments enable the use of bundles of conductive fibers that are wound (e.g., braided, stranded, or woven) together to form coil elements of a radio frequency coil. The disclosed embodiments provide an alternative that is lighter and more flexible than traditional wire-based conductors, while being less expensive but providing similar conductivity and performance. The disclosed embodiments enable a coil assembly that is both lighter and more flexible, thereby enhancing patient comfort and enabling easier positioning of the coil assembly, which can improve processing efficiency when using a magnetic resonance imaging system. The disclosed embodiments enable lower-cost (by reducing conductor costs), faster (e.g., using stitching or embroidery techniques) coil manufacturing. The disclosed embodiments enable the coil elements to be easily stitched to an anchoring fabric or a heat-dissipating fabric to provide a wearable coil array, thereby enabling a high degree of adaptation to the anatomical structure in which it is used. The disclosed embodiments enable the conductive fiber bundles to be woven or braided into a customized configuration to reduce resistance, evenly distribute current, and enhance performance. The disclosed embodiments enable a reduction in reflections in a positron emission tomography scanner (e.g., due to less metal) when the radio frequency coil is used in a PET / MR scanner.

[0056] In view of the foregoing, Figure 1 , a magnetic resonance imaging (MRI) system 100 is schematically illustrated as including a scanner 102, scanner control circuitry 104, and system control circuitry 106. In accordance with the embodiments described herein, the magnetic resonance imaging system 100 is generally configured to perform MR imaging.

[0057] The system 100 also includes: a remote access and storage system or device, such as a picture archiving and communication system (PACS) 108; or other devices, such as remote radiology equipment, that enable on-site or off-site access to data acquired by the system 100. Thus, MR data can be acquired and then processed and evaluated on-site or off-site. Although the magnetic resonance imaging system 100 can include any suitable scanner or detector, in the illustrated embodiment, the system 100 includes a whole-body scanner 102 having a housing 120 through which an aperture 122 is formed. A diagnostic table 124 can be moved into the aperture 122 to allow a patient 126 to be positioned therein for imaging of a selected anatomical structure within the patient.

[0058] Scanner 102 includes a series of associated coils for generating a controlled magnetic field that is used to excite the magnetic resonance material within the anatomical structure of the subject being imaged. Specifically, a primary magnetic coil 128 is provided for generating a primary magnetic field B0 that is generally aligned with the aperture 122. A series of gradient coils 130, 132, and 134 allow for the generation of a controlled gradient magnetic field during an examination sequence for position encoding certain magnetic resonance nuclei within the patient 126. A radio frequency (RF) coil 136 (e.g., a radio frequency transmit coil) is configured to generate radio frequency pulses for exciting certain magnetic resonance nuclei within the patient. In addition to the coils that may be located local to the scanner 102, the system 100 also includes a set of receive coils or radio frequency receive coils 138 (e.g., a coil array) that are configured to be placed proximal to the patient 126 (e.g., against the patient). For example, the receive coils 138 may include cervical / thoracic / lumbar (CTL) coils, head coils, single-sided spine coils, etc. Generally speaking, the receive coils 138 are placed close to or over the head of the patient 126 in order to receive the weak radio frequency signals (weak relative to the transmit pulses generated by the scanner coils) generated by certain magnetic resonance nuclei within the patient 126 as the patient returns to their relaxed state.

[0059] The various coils of the system 100 are controlled by an external circuitry to generate the desired fields and pulses and to read emissions from the magnetic resonance material in a controlled manner. In the illustrated embodiment, a main power supply 140 supplies power to the primary field coil 128 to generate the main magnetic field B0. The power input (e.g., power from a utility or the power grid), power distribution unit (PDU), power supply (PS), and drive circuit 150 may work together to supply power such that the gradient field coils 130, 132, and 134 generate pulses. The drive circuit 150 may include amplification and control circuitry for supplying current to the coils in accordance with the limitations of the digital pulse sequence output by the scanner control circuitry 104.

[0060] Another control circuit 152 is provided for regulating the operation of the RF coil 136. The circuit 152 includes switching devices for alternating between an active operating mode and a passive operating mode, where the RF coil 136 transmits signals and does not transmit signals, respectively. The circuit 152 also includes amplification circuitry configured to generate radio frequency pulses. Similarly, the receive coils 138 are connected to a switch 154 that is capable of switching the receive coils 138 between a receive mode and a non-receive mode. Thus, in the receive mode, the receive coils 138 resonate with the radio frequency signals generated by the release of magnetic resonance nuclei within the patient 126, and in the non-receive mode, they do not resonate with the radio frequency energy from the transmit coil (i.e., coil 136) in order to prevent unwanted operation. Additionally, a receive circuit 156 is configured to receive the data detected by the receive coils 138 and may include one or more multiplexing and / or amplification circuits.

[0061] It should be noted that although the above scanner 102 and control / amplification circuit system are illustrated as being coupled by a single wire, there may be many such wires in an actual instance. For example, separate wires may be used for control, data communication, power transmission, etc. In addition, appropriate hardware may be provided along each type of wire for correctly processing data and current / voltage. In fact, various filters, digital converters, and processors may be provided between the scanner and either or both of the scanner control circuit 104 and the system control circuit system 106.

[0062] As illustrated, the scanner control circuit system 104 includes an interface circuit 158 that outputs signals for driving the gradient field coil and the radio frequency coil and for receiving data representing the magnetic resonance signals generated in the examination sequence. The interface circuit 158 is coupled to a control and analysis circuit 160. Based on a defined scheme selected via the system control circuit 106, the control and analysis circuit 160 executes commands for driving circuits 150 and 152.

[0063] The control and analysis circuit 160 is also used to receive the magnetic resonance signals and perform subsequent processing before transmitting the data to the system control circuit 106. The scanner control circuit 104 also includes one or more memory circuits 162 that store configuration parameters, pulse sequence descriptions, examination results, etc. during operation.

[0064] An interface circuit 164 is coupled to the control and analysis circuit 160 for exchanging data between the scanner control circuit system 104 and the system control circuit system 106. In some embodiments, although the control and analysis circuit 160 is illustrated as a single unit, it may include one or more hardware devices. The system control circuit 106 includes an interface circuit 166 that receives data from the scanner control circuit system 104 and transmits data and commands back to the scanner control circuit system 104. The control and analysis circuit 168 may include a CPU in a general-purpose or special-purpose computer or workstation. The control and analysis circuit 168 is coupled to a memory circuit 170 to store programming code for operating the magnetic resonance imaging system 100 and to store the processed image data for subsequent reconstruction, display, and transmission. The programming code may execute one or more algorithms that are configured to perform the reconstruction of the acquired data as described below when executed by a processor. In some embodiments, the memory circuit 170 may store one or more neural networks for the reconstruction of the acquired data as described below. In some embodiments, the image reconstruction may occur on a separate computing device having a processing circuit system and a memory circuit system.

[0065] An additional interface circuit 172 may be provided for exchanging image data, configuration parameters, etc. with external system components such as remote access and storage device 108. Finally, the system control and analysis circuit 168 may be communicatively coupled to various peripheral devices for facilitating an operator interface and generating a hard copy of the reconstructed image. In the illustrated embodiment, these peripheral devices include a printer 174, a monitor 176, and a user interface 178, which includes devices such as a keyboard, a mouse, a touch screen (e.g., integrated with the monitor 176), etc.

[0066] Figure 2 is a schematic diagram of a radio frequency coil assembly 180 (e.g., a radio frequency receive coil assembly) having a layered and / or bilateral arrangement of coil elements. The radio frequency coil assembly 180 may be used in a magnetic resonance imaging system (e.g., Figure 1 the magnetic resonance imaging system 100 in). The radio frequency coil assembly 180 includes a radio frequency coil 184 having a plurality of coil elements 186 (e.g., loops or channels). Each element 186 is coupled to an electronic unit 185, which is coupled to a coil interface cable 187. The coil interface cable 187 of each coil element in the coil elements 186 is coupled to an electrical connector interface or interface circuitry 188 (e.g., a balun such as an integrated balun cable harness, which may act as a radio frequency trap). The electrical connector interface 188 (via a cable 190) is coupled to a P connector 192 (e.g., a port connector), which enables the radio frequency coil assembly 180 to be coupled (e.g., via a wired connection) to an interface of the magnetic resonance imaging system that couples the imaging component to the processing component. In some embodiments, the radio frequency coil assembly 180 may have no wired connection and may be configured to be used wirelessly with the magnetic resonance imaging system during a magnetic resonance imaging scan (e.g., for coupling the imaging component to a wireless component).

[0067] Each element 186 may be composed of resonator coil elements linked to a printed circuit board module (e.g., the electronic unit 185). Each electronic unit 185 may include various components (e.g., a decoupling circuit, an impedance inverter circuit, and a preamplifier). The radio frequency coil 184 may be designed using AIR TM coil technology from General Electric Healthcare. This enables the radio frequency coil 184 to be lightweight and flexible. Each element 186 is made of a bundle of conductive fibers wound together. In some embodiments, each element 186 may be stretchable (e.g., due to the use of a zigzag or meandering structure). Additionally, the coil elements 186 of the radio frequency coil 184 are transparent, thus contributing to the signal-to-noise ratio.

[0068] The radio frequency coil 184 is disposed within a flexible housing 194 (e.g., a blanket). As depicted, the flexible housing 194 has a rectangular shape. In some embodiments, the flexible housing 194 may have a square shape or other shape. In some embodiments, the flexible housing 194 includes holes or openings to increase the flexibility of the radio frequency coil assembly 180 (and the flexible housing 194). Each hole or opening may be radially located within the element 186. In some embodiments, the flexible housing 194 may contain a deformable material therein. The deformable material may include foam, memory foam, expanded foam, inflatable foam, polyurethane foam, gels such as hydrogels, water balloons, or other suitable deformable materials. When a subject lies on the radio frequency coil assembly 180, the subject will sink into the deformable material, and the radio frequency coil 184 may conform to the unique shape of the subject and thus rest precisely against the patient's body. As depicted, the interface circuitry 188 is disposed within the flexible housing 194. In some embodiments, the interface circuitry 188 may be disposed outside the flexible housing 194.

[0069] As described above, each flexible coil element 186 may be constructed using a plurality of conductive fiber bundles wound together. Each fiber bundle includes a plurality of conductive fibers. Each flexible coil element 186 may be made of Litz wire, a wire bundle, a metal wire bundle, a coated filament bundle, a woven filament bundle, or a conductive fine wire bundle. The conductive fibers within each bundle may be wound in a variety of patterns (e.g., woven, braided, or stranded). The bundles are wound in a variety of patterns (e.g., woven, braided, or stranded).

[0070] Figure 3 is a schematic cross - section of a conductive fiber 200 that can be used to form a coil element. The entire conductive fiber 200 is conductive. In some embodiments, the conductive fiber may be copper (e.g., silver - plated copper). As depicted, the conductive fiber 200 is bare. No covering (dielectric material or shielding layer) is provided around the conductive fiber 200 itself.

[0071] Figure 4 is a schematic cross - section of a conductive fiber 202 (e.g., having a non - conductive core) that can be used to form a coil element. The conductive fiber 202 includes a non - conductive core 204 (e.g., plastic or polymer). A concentric conductive layer 206 (e.g., copper or other conductive metal) is disposed around the non - conductive core 204. The concentric conductive layer 206 may be plated on the non - conductive core 204.

[0072] Figure 5 is a conductive fiber 210 that can be used to form a coil element (e.g., Figure 3 the conductive fiber 200 in Figure 4Schematic cross-section of a bundle 208 (e.g., a bare bundle) of conductive fibers 202). The bundle 208 includes a plurality of conductive fibers 210. The plurality of conductive fibers 210 can be wound in various patterns (e.g., woven, braided, or stranded) within the bundle 208. The number of conductive fibers 210 in the bundle 208 can be varied. No covering (e.g., dielectric material or shielding layer) is provided around the bundle 208 itself.

[0073] Figure 6 is a schematic cross-section of a bundle 212 (e.g., having an outer covering) of conductive fibers 214 (e.g., Figure 3 the conductive fibers 200 in, or Figure 4 the conductive fibers 202 in). The bundle 212 includes a plurality of conductive fibers 214. The plurality of conductive fibers 214 can be wound in various patterns (e.g., woven, braided, or stranded) within the bundle 212. The number of conductive fibers 214 in the bundle 212 can be varied. A concentric outer layer 216 (e.g., dielectric material and / or shielding layer) is provided around the plurality of conductive fibers 214. The dielectric material can be rubber, plastic, or some other dielectric material (e.g., fluorinated ethylene propylene (FEP) or polytetrafluoroethylene (pTFE))).

[0074] Figure 7 is a schematic cross-section of a coil element 186 (e.g., without an outer covering) having a plurality of wound fiber bundles 218 composed of conductive fibers 220 (e.g., Figure 5 the bundle 208 in, or Figure 6 the bundle 212 in). The bundle 218 can be wound in various patterns (e.g., woven, braided, or stranded). No covering (e.g., dielectric material or shielding layer) is provided around the plurality of wound bundles 218. The number of bundles 218 wound together can be varied. In some embodiments, the plurality of wound bundles 218 can be used as fine wires to form the coil element 186 on a flexible anchoring layer. Specifically, the coil element 186 has a cross-section configured to generate an exact capacitance for element tuning at a specific frequency. The coil element 186 has a distributed capacitance configuration. The coil element 186 can be composed of Litz wire, a wire bundle, a metal wire bundle, a coated filament bundle, a woven filament bundle, or a conductive fine wire bundle.

[0075] Figure 8 is a wound bundle 222 having a plurality of conductive fibers 224 (e.g., Figure 5 the bundle 208 in, or Figure 6Schematic diagram of the cross-section of the coil element 186 (e.g., having an outer covering) of the bundle 212). The bundle 222 can be wound in various patterns (e.g., woven, braided, or stranded). A concentric outer layer 226 (e.g., dielectric material and / or shielding layer) is provided around the multiple wound bundles 222. The dielectric material can be rubber, plastic, or some other dielectric material (e.g., perfluoroethylenepropylene (FEP) or polytetrafluoroethylene (PtFe)). The number of bundles 222 wound together can be varied. In certain embodiments, the multiple wound bundles 222 can be used as fine wires to form the coil element 186 on the flexible anchoring layer. Specifically, the coil element 186 has a cross-section configured to generate an exact capacitance for element tuning at a specific frequency. The coil element 186 has a distributed capacitance configuration. The coil element 186 can be composed of Litz wire, wire bundle, metal wire bundle, coated filament bundle, woven filament bundle, or conductive fine wire bundle.

[0076] Figure 9 is an image of an example of a bundle 228 of conductive fibers 230 stranded together. For example, Figure 9 the conductive fibers 230 in have a synthetic polymer core and are coated with copper. The bundle 228 can be used as a fine wire to form a conductive element and couple the conductive element to the flexible fixing material to form a radio frequency coil. Figure 10 is an example of two bundles 228 wound by stranding Figure 9 in. These two bundles 228 wound by stranding can be used as fine wires to form a conductive element and couple the conductive element to the flexible fixing material to form a radio frequency coil. Figure 11 is an example of three bundles 228 wound by braiding Figure 9 in. These three bundles 228 wound by braiding can be used as fine wires to form a conductive element and couple the conductive element to the flexible fixing material to form a radio frequency coil. Figure 12 is an example of three bundles 228 wound by stranding Figure 9 in. These three bundles 228 wound by stranding can be used as fine wires to form a conductive element and couple the conductive element to the flexible fixing material to form a radio frequency coil. A single bundle 228 or two or three wound bundles 228 have a small enough diameter for use in a sewing machine or embroidery machine.

[0077] Figure 13 is a schematic diagram of the conductive element 186 of the radio frequency coil stitched on the flexible anchoring material 230. The conductive element 186 and the flexible anchoring material 230 can be provided in a flexible housing (e.g., Figure 2in the flexible housing 194). The conductive element 186 is coupled to (e.g., sutured to) the flexible anchoring material 230 using a bundle of conductive fibers that are wound together as a fine wire. The conductive element 186 is sutured in a zigzag pattern or a serpentine pattern. The zigzag pattern enables the conductive element 186 to stretch. The conductive element 186 has a circular shape. As depicted, the conductive element 186 is coupled to the electronic unit 185, which is coupled to the coil interface cable 187. The flexible anchoring material layer 230 is stretchable. In some embodiments, the flexible anchoring material layer 230 is made of a heat dissipating material. In some embodiments, the flexible anchoring material layer 230 is magnetic resonance compatible and does not produce a proton signal. In some embodiments, the flexible anchoring material layer 230 is made of a film (e.g., a plastic film). In some embodiments, the flexible anchoring material layer 230 is made of a fabric.

[0078] As depicted, in Figure 14 the bundle of conductive fibers that are wound together to form the conductive element 186 (and that serve as the bobbin thread) is secured to the flexible anchoring material 230 via a non-conductive fine wire 232 that serves as the face thread. In some embodiments, the bundle of conductive fibers that are wound together can serve as the face thread, and the non-conductive fine wire can serve as the bobbin thread. In some embodiments, the bundle of conductive fibers that are wound together can serve as both the face thread and the bobbin thread.

[0079] Figure 15 is a schematic view of the conductive element 186 of a radio frequency coil that is sutured to the flexible anchoring material 234 (e.g., in a linear suture pattern). The conductive element 186 and the flexible anchoring material 234 can be disposed in a flexible housing (e.g., Figure 2 the flexible housing 194) in. The conductive element 186 is coupled to (e.g., sutured to) the flexible anchoring material 234 using a bundle of conductive fibers that are wound together as a fine wire. The conductive element 186 is sutured in a linear suture pattern. The conductive element 186 has a circular shape. As depicted, the conductive element 186 is coupled to the electronic unit 185, which is coupled to the coil interface cable 187. The flexible anchoring material layer 234 is non-stretchable. In some embodiments, the flexible anchoring material layer 234 is made of a heat dissipating material. In some embodiments, the flexible anchoring material layer 234 is magnetic resonance compatible and does not produce a proton signal. In some embodiments, the flexible anchoring material layer 234 is made of a film (e.g., a plastic film). In some embodiments, the flexible anchoring material layer 234 is made of a fabric.

[0080] In some embodiments, the shape of the flexible coil element can be changed and can be any shape (e.g., oval, circular, square, rectangular, etc.). For example, Figure 16 and Figure 17Depict respectively the conductive element 186 stitched to the flexible anchoring material 236 in a rectangular shape and a triangular shape. As depicted, in Figure 16 and Figure 17 , the coil element 186 can follow a straight path along the shape profile. In certain embodiments, the coil element 186 can meander (e.g., in a zigzag pattern) along the shape profile as depicted in Figure 18 and Figure 19 . This enables the coil element 186 to stretch when the flexible anchoring material 236 is stretchable. The conductive element 186 and the flexible anchoring material 236 can be disposed in a flexible housing (e.g., the flexible housing 194 in Figure 2 ).

[0081] In certain embodiments, the coil element 186 can have a multi-turn configuration. Figure 20 and Figure 21 are schematic views of the conductive element 186 of a radio frequency coil having a multi-turn configuration stitched to the flexible anchoring material 238. The conductive element 186 and the flexible anchoring material 238 can be disposed in a flexible housing (e.g., the flexible housing 194 in Figure 2 ). As depicted in Figure 20 , the coil element 186 has two turns. As depicted in Figure 21 , the coil element 186 has three turns.

[0082] Figure 22It is a flowchart of a method 240 for manufacturing a radio frequency (RF) receive coil assembly. Method 240 includes providing a flexible anchoring material (block 242). In certain embodiments, the flexible anchoring material layer is stretchable. In certain embodiments, the flexible anchoring material layer is made of a heat dissipating material. In certain embodiments, the flexible anchoring material layer is magnetic resonance compatible and does not generate proton signals. In certain embodiments, the flexible anchoring material layer is made of a film (e.g., a plastic film). In certain embodiments, the flexible anchoring material layer is made of a fabric. Method 240 also includes coupling a plurality of flexible coil elements to the flexible anchoring material to form an RF coil (block 244). Each of the plurality of flexible coil elements includes a plurality of conductive fiber bundles wound together. Each of the plurality of bundles includes multiple conductive fibers. In certain embodiments, the plurality of flexible coil elements can be made of Litz wire, a wire bundle, a metal wire bundle, a plated filament bundle, a woven filament bundle, or a conductive fine wire bundle. In certain embodiments, coupling the plurality of flexible coil elements to the flexible anchoring material includes stitching the plurality of flexible coil elements to the flexible anchoring material using a plurality of conductive fiber bundles wound together as fine wires. In certain embodiments, the flexible coil elements can be stitched using the techniques described in U.S. Application No. 18 / 313,043, filed May 5, 2023, which is hereby incorporated by reference in its entirety for all purposes. In certain embodiments, coupling the plurality of flexible coil elements to the flexible anchoring material includes gluing the plurality of flexible coil elements to the flexible anchoring material. In certain embodiments, a bilateral arrangement structure can be employed to couple a first set of flexible coil elements to one side of the flexible anchoring material and a second set of flexible coil elements to the opposite side of the flexible anchoring material. In certain embodiments, a layered arrangement structure can be employed to couple different groups of flexible coil elements to different individual layers of the flexible anchoring material. In certain embodiments, a combination of the bilateral arrangement structure and the layered arrangement structure can be employed. Method 240 further includes providing a flexible housing (block 246). Method 240 even further includes disposing the flexible anchoring material and the RF coil within the flexible housing (block 248).

[0083] Figure 23 is a schematic diagram of a coil layout 320 (e.g., for a bilateral arrangement structure) of an RF coil 184 (of an RF receive coil assembly). Figure 24 and Figure 25 are respectively Figure 23Schematic diagram of the first side 322 and the second side 324 of the radiofrequency coil 184. The radiofrequency coil 184 includes a first group 326 of coil elements 186 (e.g., flexible coil elements) coupled to the first side 322 of an anchoring material layer 328 (e.g., a flexible anchoring material layer). The radiofrequency coil 184 further includes a second group 330 of coil elements 186 coupled to the second side 324 of the anchoring material layer 328. In some embodiments, the coil elements 186 may be glued to the anchoring material layer 328. In some embodiments, the coil elements 186 may be stitched to the anchoring material layer 328. For example, the conductor of the coil element 186 may be stitched to the anchoring material layer 328 using a bobbin stitching technique. In some embodiments, the conductor of the coil element 186 serves as the bobbin thread, and a non-conductive thread (e.g., a plastic thread) serves as the face thread. In some embodiments, the conductor of the coil element 186 serves as the face thread, and a non-conductive thread (e.g., a plastic thread) serves as the bobbin thread. The corresponding electronic units and coil interface cables for each of the coil elements 186 in the coil elements 186 are not shown. In some embodiments, the anchoring material layer 328 may include slits such that the corresponding electronic units and coil interface cables of a group of coil elements on one side of the anchoring material layer 328 may be disposed on its opposite side, so that all the electronic units and coil interface cables of all the coil elements (the two groups of coil elements) are disposed on a single side of the anchoring material layer 328 to facilitate wiring. The anchoring material layer 328 and the first group 326 and the second group 330 of coil elements 186 are disposed within a flexible housing (e.g., Figure 2 the flexible housing 194 in). The number of coil elements 186 in each of the groups 326, 330 may be varied. The number and arrangement structure of the rows and / or columns of the coil elements 186 in each of the groups 326, 330 may be varied.

[0084] As Figure 23 shown in the coil layout 320, the corresponding coil elements 186 of both the first group 326 of coil elements 186 and the second group 330 of coil elements 186 are alternately disposed between each other along a first direction 332 and a second direction 334 (the two directions being orthogonal to each other) along a horizontal plane 336 defined by the anchoring material layer 328. Each coil element 186 of the first group 326 of coil elements 186 overlaps at least two coil elements 186 of the second group 330 of coil elements 186 (or vice versa).

[0085] Figure 26 is a schematic diagram of the coil layout 340 (e.g., for a layered arrangement structure) of the radiofrequency coil 184 (of a radiofrequency receiving coil assembly). Figures 27 to 30 is Figure 26Schematic diagram of different groups of coil elements 186 on different layers of the radio frequency coil 184. The coil layout 340 depicts the arrangement structure of all coil elements 186 on different layers relative to each other.

[0086] The radio frequency coil 184 includes a first group 342 of coil elements 186 (e.g., flexible coil elements) coupled to the side 344 of an anchoring material layer 346 (e.g., flexible anchoring material layer), and no coil elements are provided on the opposite side 348 of the anchoring material layer 346. The radio frequency coil 184 also includes a second group 350 of coil elements 186 (e.g., flexible coil elements) coupled to the side 352 of an anchoring material layer 354 (e.g., flexible anchoring material layer), and no coil elements are provided on the opposite side 356 of the anchoring material layer 354. The radio frequency coil 184 further includes a third group 358 of coil elements 186 (e.g., flexible coil elements) coupled to the side 360 of an anchoring material layer 362 (e.g., flexible anchoring material layer), and no coil elements are provided on the opposite side 364 of the anchoring material layer 362. The radio frequency coil 184 even further includes a fourth group 366 of coil elements 186 (e.g., flexible coil elements) coupled to the side 368 of an anchoring material layer 370 (e.g., flexible anchoring material layer), and no coil elements are provided on the opposite side 372 of the anchoring material layer 370.

[0087] The anchoring material layer 362 is stacked on the anchoring material layer 370 such that the side 368 (and the coil elements 186 on the side 368) is connected to the side 364 of the anchoring material layer 362. The anchoring material layer 354 is stacked on the anchoring material layer 362 such that the side 360 (and the coil elements 186 on the side 360) is connected to the side 356 of the anchoring material layer 354. The anchoring material layer 346 is stacked on the anchoring material layer 354 such that the side 352 (and the coil elements 186 on the side 352) is connected to the side 348 of the anchoring material layer 346.

[0088] In certain embodiments, the coil element 186 can be glued to the respective anchoring material layers 346, 354, 362, and 370. In certain embodiments, the coil element 186 can be stitched to the respective anchoring material layers 346, 354, 362, and 270. For example, a bobbin stitching technique can be used to stitch the conductors of the coil element 186 to the anchoring material layers 346, 354, 362, and 370. In certain embodiments, the conductors of the coil element 186 serve as the bobbin thread, and a non-conductive thread (e.g., a plastic thread) serves as the face thread. In certain embodiments, the conductors of the coil element 186 serve as the face thread, and a non-conductive thread (e.g., a plastic thread) serves as the bobbin thread. The respective electronic units and coil interface cables for each coil element in the coil element 186 are not shown. In certain embodiments, some of the anchoring material layers 346, 354, 362, and 370 can include slits such that the respective electronic units and coil interface cables of one or more sets of coil elements on one or more of the anchoring material layers 346, 354, 362, and 370 can be disposed on one side of one of the anchoring material layers 346, 354, 362, and 370, such that all of the electronic units and coil interface cables of all of the coil elements (of all sets of coil elements) are disposed on one side of only one of the anchoring material layers 346, 354, 362, and 370 to facilitate wiring. The anchoring material layers 346, 354, 362, and 370 and the sets 342, 350, 358, and 366 of the coil element 186 are disposed within a flexible housing (e.g., Figure 2 the flexible housing 194 in

[0089] ). The number of coil elements 186 in each of the sets 342, 350, 358, and 366 can vary. The number and arrangement structure of the rows and / or columns of the coil elements 186 in each of the sets 342, 350, 358, and 366 can vary. Both the number of sets of the coil elements 186 and the corresponding number of the anchoring material layers can vary.

[0090] AsFigure 26 As shown in the coil layout 340 in, the respective coil elements 186 of different groups 342, 350, 358, and 366 of the coil element 186 are alternately arranged between each other along a horizontal plane 374 defined by the laminated anchoring material layers 346, 354, 362, and 370 in a first direction 332 and a second direction 334 (the two directions are orthogonal to each other). At least one coil element 186 of each group 342, 350, 358, and 366 of the coil element 186 overlaps with at least one coil element 186 of two or more groups among the other groups 342, 350, 358, and 366 of the coil element 186.

[0091] In some embodiments, the coil element 186 of the radio frequency coil can be made of an elastomeric or stretchable conductive fiber bundle, which is stitched onto a flexible or stretchable anchoring material layer in a biaxial / biaxial line configuration. Figure 31 A cross-sectional view of a pair of elastomeric or stretchable conductive fiber bundles 378 (e.g., of the coil element 186) in a biaxial configuration is depicted; each fiber bundle 378 is disposed or wrapped within a dielectric material 380. In some embodiments, an outer sheath / covering can also be disposed around the fiber bundle 378. The bundle thickness of each fiber bundle 378 (e.g., by adjusting either the fiber thickness or the number of filaments within the fiber bundle 378), the spacing between the fiber bundles 378, and / or the length of each fiber bundle 378 can be varied to change the capacitance per unit length. This enables the coil element 186 to be tuned to a desired frequency. This also eliminates the need for adding capacitance breaks (e.g., as shown by the small rectangles representing printed circuit boards with capacitors in Figure 13 ). Figure 32 A fiber bundle 378 stitched onto a flexible or stretchable anchoring material layer 382 in a biaxial configuration is depicted. As depicted, the fiber bundle 378 is stitched onto the flexible or stretchable anchoring material layer 382 in a straight line manner. In some embodiments, the fiber bundle 378 is stitched onto the flexible or stretchable anchoring material layer 382 in a zigzag manner. As depicted, each fiber bundle 378 is coupled to an electronic unit or module 185. As depicted, each fiber bundle 378 includes a shortened length or notch 384, which is taken out to tune the coil element 186. In some embodiments, the shortened length or notch 384 can be taken out from only one of the fiber bundles 378.

[0092] The technical effects of the disclosed subject matter include enabling the formation of coil elements of a radio frequency coil using bundles of conductive fibers that are wound (e.g., braided, stranded, or woven) together. The technical effects of the disclosed subject matter also include providing an alternative that is lighter and more flexible than conventional wire-based conductors, while being less expensive yet providing similar conductivity and performance. The technical effects of the disclosed subject matter further include enabling a coil assembly that is both lighter and more flexible, thereby enhancing patient comfort, and enabling easier positioning of the coil assembly, which can improve processing efficiency when using a magnetic resonance imaging system. The technical effects of the disclosed subject matter even further include enabling lower-cost (by reducing conductor costs), faster (e.g., using stitching or embroidery techniques) coil manufacturing. The technical effects of the disclosed subject matter additionally include enabling easy stitching of the coil elements to an anchoring fabric or a heat-dissipating fabric to provide a wearable coil array, thereby enabling high adaptation to the anatomical structure in which it is used. The technical effects of the disclosed subject matter also include enabling the conductive fiber bundles to be woven or braided into a customized configuration to reduce resistance, evenly distribute current, and enhance performance. The technical effects of the disclosed subject matter also include enabling reduction of reflections in a positron emission tomography scanner when the radio frequency coil is used in a PET / MR scanner (e.g., due to reduced metal).

[0093] Referring to the technology presented herein and claimed and applying it to physical objects and specific examples having practical characteristics that clearly improve the current art and are thus not abstract, intangible, or purely theoretical. Additionally, if any of the claims appended to the end of this specification contain one or more coil elements designated as "means for [performing]... function" or "steps for [performing]... function," such coil elements are intended to be construed in accordance with 35 U.S.C. 112(f). However, for any claims containing coil elements designated in any other way, such coil elements are not intended to be construed in accordance with 35 U.S.C. 112(f).

[0094] This written description uses examples to disclose the subject matter, including the best mode, and also enables those skilled in the art to practice the subject matter, including manufacturing and using any device or system and performing any included method. The patent scope of the subject matter is defined by the claims and may include other examples that occur to those skilled in the art. If such other examples have structural coil elements that do not differ from the literal language of the claims, or if they include equivalent structural coil elements that differ from the literal language of the claims in minor respects, such other examples are intended to fall within the scope of the claims.

Claims

1. A radio frequency (RF) receive coil assembly for a magnetic resonance imaging (MRI) system, the RF receive coil assembly comprising: A flexible housing; Flexible anchoring material disposed within the flexible housing; And An RF coil disposed within the flexible housing, wherein the RF coil includes a plurality of flexible coil elements coupled to the flexible anchoring material, and wherein each flexible coil element of the plurality of flexible coil elements includes a plurality of conductive fiber bundles wound together, and each of the plurality of bundles includes a plurality of conductive fibers.

2. The RF receive coil assembly of claim 1, wherein the plurality of flexible coil elements are stitched to the flexible anchoring material using the plurality of conductive fiber bundles wound together as thread.

3. The RF receive coil assembly of claim 2, wherein the plurality of flexible coil elements are stitched to the flexible anchoring material as the top thread.

4. The RF receive coil assembly of claim 2, wherein the plurality of flexible coil elements are stitched to the flexible anchoring material as the bobbin thread.

5. The RF receive coil assembly of claim 2, wherein the plurality of flexible coil elements are stitched to the flexible anchoring material in a zigzag pattern, and wherein the plurality of flexible coil elements are configured to be stretchable due to the zigzag pattern.

6. The RF receive coil assembly of claim 5, wherein the flexible anchoring material is stretchable.

7. The RF receive coil assembly of claim 2, wherein the plurality of flexible coil elements are stitched to the flexible anchoring material via a linear stitch pattern.

8. The RF receive coil assembly of claim 1, wherein each of the plurality of conductive fibers includes a non-conductive core and a conductive covering disposed around the non-conductive core.

9. The RF receive coil assembly of claim 1, wherein each of the plurality of conductive fibers includes a conductive core, and each of the plurality of bundles has a non-conductive covering disposed around the respective bundle.

10. The RF receive coil assembly of claim 1, wherein each of the plurality of conductive fibers includes a conductive core, and the plurality of bundles wound together have a non-conductive covering disposed around the respective bundle.

11. The RF receive coil assembly of claim 1, wherein the plurality of bundles wound together are bare.

12. The RF receive coil assembly of claim 1, wherein each flexible coil element of the plurality of flexible coil elements is coupled to the flexible anchoring material in a multi-turn configuration.

13. A method of manufacturing an RF receive coil assembly for an MRI system, the method comprising: Providing flexible anchoring material; Coupling a plurality of flexible coil elements to the flexible anchoring material to form an RF coil, wherein each flexible coil element of the plurality of flexible coil elements includes a plurality of conductive fiber bundles wound together, and each of the plurality of bundles includes a plurality of conductive fibers; And The flexible anchoring material and the RF coil are disposed within a flexible housing.

14. The method according to claim 13, wherein coupling the plurality of flexible coil elements to the flexible anchoring material comprises suturing the plurality of flexible coil elements to the flexible anchoring material using the plurality of conductive fiber bundles wound together as fine wires.

15. A magnetic resonance imaging system, the magnetic resonance imaging system comprising: An imaging section having an RF receiving coil assembly according to any one of claims 1 to 13.

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