Magnetic resonance radio frequency coil assembly and head magnetic resonance scanning apparatus

Abstract

The application relates to a magnetic resonance radio frequency coil assembly and a head magnetic resonance scanning device. The magnetic resonance radio frequency coil assembly comprises a support body, a radio frequency coil, a radio frequency shielding layer and a shim coil; the support body is in a cylindrical shape and comprises a first support surface, a second support surface and a third support surface which are arranged in sequence and are sleeved one by one; the radio frequency coil is arranged on the first support surface; the radio frequency shielding layer is arranged on the second support surface; and the shim coil is arranged on the third support surface. The radio frequency coil, the radio frequency shielding layer and the shim coil are respectively arranged on the first support surface, the second support surface and the third support surface of the support body. Since the second support surface is arranged outside the first support surface, the radio frequency shielding layer is arranged outside the radio frequency coil and is arranged outside the second support surface through the third support surface, so that the shim coil can be arranged on the third support surface, the magnetic field uniformity is optimized, and the magnetic field uniformity is improved.

Description

Technical Field

[0001] This application relates to the field of magnetic resonance technology, and in particular to magnetic resonance radio frequency coil assemblies and head magnetic resonance scanning equipment. Background Technology

[0002] Magnetic resonance imaging (MRI) devices use magnetic resonance imaging technology to non-invasively acquire images of any cross-section of the human body. MRI devices receive magnetic resonance signals through radio frequency coils and then generate magnetic resonance images based on these signals.

[0003] In current MRI scans, to prevent patients from feeling cramped or confined during the scan, the aperture size of the MRI scanner is made larger than 70 cm, and in some cases even 80 cm. This type of equipment is particularly suitable for obese patients, improving examination comfort. However, the magnetic field homogeneity of this type of equipment is not as good as that of MRI scanners with smaller apertures, and the excessively large aperture also reduces the penetration depth of the radiofrequency signal. In clinical applications, because the head, chest, upper limbs, and lower limbs of the patient are not uniformly sized, when scanning specific areas such as the head, the housing cavity is relatively large, and the head is relatively small. The center of the head is relatively far from the gradient coil and magnetic field coil, and the linear region of the gradient field or main magnetic field homogeneity in that local area does not meet the requirements. As a result, the reconstructed MRI images of certain areas are unclear, affecting the doctor's diagnosis of the patient's condition.

[0004] To address these issues, some manufacturers have developed MRI equipment specifically designed for scanning key areas. However, for certain specialized areas, such as the head, the uniformity of the B0 (bass overlap) is limited due to the limitations of the mechanical structure of MRI equipment. Previously, MRI equipment required radio frequency (RF) shielding to prevent interference from RF signals to the gradient coils and related components, ensuring that RF coil signal acquisition and subsequent image processing were unaffected. In existing technologies, the shimming coil needs to be installed outside the RF shielding layer, while the RF coil shielding layer is typically fixed inside the gradient coil. This spatial limitation makes it impossible to install the shimming coil and hinders the optimization of image quality for areas of focus. Summary of the Invention

[0005] Therefore, it is necessary to provide a magnetic resonance radio frequency coil assembly to address the technical problem that in related technologies, the shimming coil needs to be installed on the outer layer of the radio frequency shielding layer, while the radio frequency coil shielding layer is usually fixed inside the gradient coil, making it impossible to install the shimming coil in space and thus impossible to optimize the imaging quality of key areas of interest.

[0006] A magnetic resonance radio frequency coil assembly, comprising:

[0007] The support body is arranged in a cylindrical shape. The support body includes a first support surface, a second support surface, and a third support surface arranged around itself in a circumferential direction. The first support surface, the second support surface, and the third support surface are sequentially nested from the inside to the outside.

[0008] The radio frequency coil is disposed on the first support surface;

[0009] An RF shielding layer is disposed on the second support surface; and,

[0010] A shimming coil is disposed on the third support surface.

[0011] In one embodiment, the support body includes at least two support cylinders that are sequentially nested from the inside out, with the first support surface and the third support surface located on the cylinder walls of the two support cylinders respectively.

[0012] In one embodiment, the magnetic resonance radio frequency coil assembly further includes a support block, with the support block provided between any two adjacent support cylinders, and each support cylinder abutting against the corresponding support block.

[0013] In one embodiment, the magnetic resonance radio frequency coil assembly further includes at least one fastener, and any two adjacent support cylinders are connected by the corresponding fastener.

[0014] In one embodiment, in any two adjacent support cylinders, the axial length of the inner support cylinder is greater than or equal to the axial length of the outer support cylinder.

[0015] In one embodiment, the support cylinder having the third support surface is provided with a mounting groove, and the shimming coil is housed in the mounting groove.

[0016] In one embodiment, the number of support cylinders is three, and the first support surface, the second support surface and the third support surface are respectively located on the cylinder walls of the three support cylinders.

[0017] In one embodiment, the magnetic resonance radio frequency coil assembly further includes two protective rings, which are sleeved on the support and located at two ends of the support along its own axial direction.

[0018] This application also provides a magnetic resonance device that can solve at least one of the above-mentioned technical problems.

[0019] A head magnetic resonance imaging (MRI) scanner includes:

[0020] A magnet coil forms a magnet cavity;

[0021] A support body is disposed within the cavity forming the magnet. The support body comprises a first segment and a second segment connected adjacent to each other. The diameter of the first segment is smaller than the diameter of the second segment. The first segment of the support body includes a first support surface, a second support surface, and a third support surface arranged around itself in a circumferential direction. The first support surface, the second support surface, and the third support surface are sequentially nested from the inside out.

[0022] The radio frequency coil is disposed on the first support surface;

[0023] An RF shielding layer is disposed on the second support surface; and,

[0024] A shimming coil is disposed on the third support surface.

[0025] In one embodiment, the first segment includes at least two support cylinders that are sequentially nested from the inside out, with the first support surface and the third support surface located on the cylinder walls of the two support cylinders respectively.

[0026] A gradient coil is provided between the third support surface and the magnet coil.

[0027] In one embodiment, the head magnetic resonance imaging (MRI) scanner further includes:

[0028] The scanning bed is capable of moving within the magnet cavity to the junction area between the first and second segments.

[0029] In one embodiment, the head magnetic resonance imaging device includes a patient end and a service end facing each other.

[0030] The second segment is located at the patient's end;

[0031] The first segment is located on the server side; the second segment has a smaller dimension along the axial direction of the magnet cavity than the first segment along the axial direction of the magnet cavity.

[0032] Beneficial effects:

[0033] The magnetic resonance radio frequency coil assembly provided in this application includes a support body, a radio frequency coil, a radio frequency shielding layer, and a shimming coil. The support body is cylindrical and includes a first support surface, a second support surface, and a third support surface arranged circumferentially around itself, with the first, second, and third support surfaces sequentially nested from the inside out. The radio frequency coil is disposed on the first support surface; the radio frequency shielding layer is disposed on the second support surface; and the shimming coil is disposed on the third support surface. In this application, by providing the first, second, and third support surfaces sequentially nested from the inside out on the support body, the radio frequency coil, the radio frequency shielding layer, and the shimming coil can be respectively mounted on the first, second, and third support surfaces. Since the second support surface is located outside the first support surface, the radio frequency shielding layer is located outside the radio frequency coil, thereby shielding interference signals. Furthermore, by being located outside the second support surface, the shimming coil can be arranged on the third support surface, allowing the shimming coil to be positioned between the gradient coil and the radio frequency shielding layer. This achieves local or global optimization of the magnetic field uniformity, improves magnetic field uniformity, and thus enhances imaging performance.

[0034] This application also provides a head magnetic resonance imaging (MRI) scanner, including a magnet coil, a support body, a radio frequency (RF) coil, an RF shielding layer, and a shimming coil. The magnet coil forms a magnet cavity. The support body is disposed within the magnet cavity and comprises a first segment and a second segment connected adjacent to each other, the diameter of the first segment being smaller than the diameter of the second segment. The first segment of the support body includes a first support surface, a second support surface, and a third support surface arranged circumferentially around itself, the first support surface, the second support surface, and the third support surface being sequentially nested from the inside out. The RF coil is disposed on the first support surface. The RF shielding layer is disposed on the second support surface. The shimming coil is disposed on the third support surface. This MRI scanner can achieve at least one of the above-mentioned technical effects. Attached Figure Description

[0035] Figure 1 This is a schematic diagram of a magnetic resonance radio frequency coil assembly provided in an embodiment of this application, in which the radio frequency coil is mounted on a first support surface.

[0036] Figure 2 This is a schematic diagram of the radio frequency shielding layer being installed on the second support surface in a magnetic resonance radio frequency coil assembly provided in an embodiment of this application.

[0037] Figure 3 This is a schematic diagram of a shimming coil mounted on a third support surface in a magnetic resonance radio frequency coil assembly provided in an embodiment of this application.

[0038] Figure 4 This is a schematic diagram of a head magnetic resonance imaging (MRI) scanner provided in an embodiment of this application.

[0039] Figure 5This is a schematic diagram of a shimming coil in a magnetic resonance radio frequency coil assembly provided in an embodiment of this application.

[0040] Figure 6 A schematic diagram of a shimming coil in a magnetic resonance radio frequency coil assembly provided in another embodiment of this application.

[0041] Figure 7 A simplified diagram illustrating the interaction between a head magnetic resonance imaging (MRI) scanner and the human body, as provided in an embodiment of this application.

[0042] Figure 8 This is a schematic diagram of a partial cross-section of a head magnetic resonance imaging (MRI) scanner provided in an embodiment of this application.

[0043] Figure 9 This is a schematic diagram of a head magnetic resonance scanning device provided in an embodiment of this application, in which the radio frequency coil is mounted on a first support surface.

[0044] Figure 10 This is a schematic diagram of the radio frequency shielding layer installed on the second support surface in a head magnetic resonance scanning device provided in an embodiment of this application.

[0045] Figure 11 This is a schematic diagram of a head magnetic resonance scanning device provided in an embodiment of this application, in which a shimming coil is mounted on a third support surface.

[0046] Icon labels:

[0047] 100-Support body; 110-First support surface; 111-First section; 112-Second section; 120-Second support surface; 130-Third support surface; 140-Support cylinder; 141-First support cylinder; 142-Second support cylinder; 143-Third support cylinder; 150-Fastener; 160-Mounting groove; 170-Protective ring; 200-RF coil; 300-RF shielding layer; 400-Stabilizing coil; 500-Magnet coil; 600-Head magnetic resonance scanning device; 610-Avoidance section; 620-Cavity; 700-Scanning bed. Detailed Implementation

[0048] To make the above-mentioned objectives, features, and advantages of this application more apparent and understandable, the specific embodiments of this application are described in detail below with reference to the accompanying drawings. Many specific details are set forth in the following description to provide a thorough understanding of this application. However, this application can be implemented in many other ways different from those described herein, and those skilled in the art can make similar modifications without departing from the spirit of this application. Therefore, this application is not limited to the specific embodiments disclosed below.

[0049] In the description of this application, it should be understood that the terms "center", "longitudinal", "lateral", "length", "width", "thickness", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "radial", "circumferential", etc., indicating the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this application.

[0050] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include at least one of that feature. In the description of this application, "multiple" means at least two, such as two, three, etc., unless otherwise explicitly specified.

[0051] In this application, unless otherwise expressly specified and limited, the terms "installation," "connection," "joining," and "fixing," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components, unless otherwise expressly limited. Those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances.

[0052] In this application, unless otherwise expressly specified and limited, "above" or "below" the second feature can mean that the first feature is in direct contact with the second feature, or that the first feature is in indirect contact with the second feature through an intermediate medium. Furthermore, "above," "on top of," and "over" the second feature can mean that the first feature is directly above or diagonally above the second feature, or simply that the first feature is at a higher horizontal level than the second feature. "Below," "below," and "under" the second feature can mean that the first feature is directly below or diagonally below the second feature, or simply that the first feature is at a lower horizontal level than the second feature.

[0053] It should be noted that when an element is referred to as being "fixed to" or "set on" another element, it can be directly on the other element or there may be an intervening element. When an element is considered to be "connected to" another element, it can be directly connected to the other element or there may be an intervening element. The terms "vertical," "horizontal," "upper," "lower," "left," "right," and similar expressions used herein are for illustrative purposes only and do not represent the only possible implementation.

[0054] See Figure 1 , Figure 2 , Figure 3 , Figure 4 and Figure 5 , Figure 1 This is a schematic diagram of a magnetic resonance radio frequency coil assembly provided in an embodiment of this application, in which the radio frequency coil is mounted on a first support surface. Figure 2 This is a schematic diagram of the radio frequency shielding layer being installed on the second support surface in a magnetic resonance radio frequency coil assembly provided in an embodiment of this application. Figure 3 This is a schematic diagram of a shimming coil mounted on a third support surface in a magnetic resonance radio frequency coil assembly provided in an embodiment of this application. Figure 4 This is a schematic diagram of a magnetic resonance device provided in an embodiment of this application. Figure 5 This is a schematic diagram of a shimming coil in a magnetic resonance radio frequency coil assembly provided in an embodiment of this application. The magnetic resonance radio frequency coil assembly provided in an embodiment of this application includes a support body 100, a radio frequency coil 200, a radio frequency shielding layer 300, and a shimming coil 400. The support body 100 is cylindrical and includes a first support surface 110, a second support surface 120, and a third support surface 130 arranged circumferentially around itself, with the first support surface 110, the second support surface 120, and the third support surface 130 sequentially nested from the inside out. The radio frequency coil 200 is disposed on the first support surface 110; the radio frequency shielding layer 300 is disposed on the second support surface 120; and the shimming coil 400 is disposed on the third support surface 130.

[0055] Specifically, in this application, a first support surface 110, a second support surface 120, and a third support surface 130 are sequentially arranged from the inside out on the support body 100. This allows the RF coil 200, the RF shielding layer 300, and the shimming coil 400 to be respectively mounted on the first support surface 110, the second support surface 120, and the third support surface 130. Since the second support surface 120 is located outside the first support surface 110, the RF shielding layer 300 is located outside the RF coil 200, thereby shielding interference signals. Furthermore, since the third support surface 130 is located outside the second support surface 120, the shimming coil 400 can be arranged on the third support surface 130. This allows the shimming coil 400 to be positioned between the gradient coil and the RF shielding layer 300, thereby achieving local or global optimization of the magnetic field uniformity, improving magnetic field uniformity, and ultimately enhancing imaging performance. In this embodiment, the RF coil 200 can be a transmitting coil or a combined transmitting / receiving coil.

[0056] It should be noted that in magnetic resonance imaging (MRI) devices, the gradient coil is disposed on the side of the RF shielding layer 300 away from the RF coil 200. In this application, by providing a first support surface 110, a second support surface 120, and a third support surface 130 sequentially arranged from the inside out on the support body 100, the shimming coil 400 can be disposed on the third support surface 130, thereby being located between the gradient coil and the RF shielding layer 300. A magnet coil 500 is also provided on the side of the gradient coil away from the shimming coil 400. The magnet coil 500, the gradient coil, and the RF coil 200 are arranged concentrically to ensure the excitation of imaging protons.

[0057] The radio frequency shielding layer 300 can prevent external radio frequency interference signals from entering, avoid them from interfering with the signals transmitted and received by the radio frequency coil 200, ensure the accuracy and integrity of the magnetic resonance signal received by the radio frequency coil 200, and improve image quality.

[0058] See Figure 1 , Figure 2 and Figure 3 In one embodiment, the support body 100 includes at least two support cylinders 140 that are sequentially nested from the inside out, with the first support surface 110 and the third support surface 130 located on the cylinder walls of the two support cylinders 140 respectively.

[0059] Specifically, for ease of description, the support body 100 is defined as including a first support cylinder 141 and a third support cylinder 143. The third support cylinder 143 is sleeved on the first support cylinder 141, the first support surface 110 is located on the first support cylinder 141, and the third support surface 130 is located on the third support cylinder 143. Since the second support surface 120 is located between the first support surface 110 and the third support surface 130, when the first support cylinder 141 and the third support cylinder 143 are arranged adjacent to each other, the second support surface 120 can be disposed on the outer cylinder wall of the first support cylinder 141 or the inner cylinder wall of the third support cylinder 143. When other support cylinders 140 are provided between the first support cylinder 141 and the third support cylinder 143, the second support surface 120 can be disposed on the cylinder wall of the support cylinder 140 between the first support cylinder 141 and the third support cylinder 143, or it can be disposed on the outer cylinder wall of the first support cylinder 141 or the inner cylinder wall of the third support cylinder 143.

[0060] By setting up the support cylinders 140 in sequence, the radio frequency coil 200, radio frequency shielding layer 300 and shimming coil 400 can be arranged in a reasonable manner, thereby achieving better magnetic field uniformity and maximizing space utilization.

[0061] It should be noted that when the first support cylinder 141 and the third support cylinder 143 are arranged adjacent to each other, there are two support cylinders 140, which reduces the radial dimension of the support body 100 and the space occupied by the magnetic resonance radio frequency coil assembly. When other support cylinders 140 are provided between the first support cylinder 141 and the third support cylinder 143, there are three support cylinders 140, which further reduces the radial dimension of the support body 100 and the space occupied by the magnetic resonance radio frequency coil assembly. In other embodiments, there may be multiple support cylinders 140.

[0062] See Figure 1 , Figure 2 and Figure 3 In one embodiment, the magnetic resonance radio frequency coil assembly further includes a support block, with a support block provided between any two adjacent support cylinders 140, and each support cylinder 140 abutting against the corresponding support block.

[0063] Specifically, the two ends of the support block abut against the corresponding two support cylinders 140, thereby providing support and stably separating the adjacent support cylinders 140 to facilitate the arrangement of the radio frequency coil 200, the radio frequency shielding layer 300, and the shimming coil 400, etc. At the same time, it can also prevent collisions between adjacent support cylinders 140 when disassembling the support body 100, thereby improving the reliability of the magnetic resonance radio frequency coil assembly.

[0064] The support block can be constructed from the protrusion on the corresponding support cylinder 140 or it can be an isolated component, as long as it can stably separate adjacent support cylinders 140.

[0065] Furthermore, the support block is annular, thereby improving the stability of the connection between the support block and the support cylinder 140, and improving the stability of the support for the corresponding support cylinder 140.

[0066] See Figure 1 , Figure 2 and Figure 3 In one embodiment, the magnetic resonance radio frequency coil assembly further includes at least one fastener 150, and any two adjacent support cylinders 140 are connected by the corresponding fasteners 150, thereby connecting each support cylinder 140 into a whole, which facilitates the installation of the support body 100.

[0067] Furthermore, fasteners 150 are sequentially inserted into at least two adjacent support cylinders 140 and connected to one of the support cylinders 140, thereby connecting the support cylinders 140 together. The arrangement of fasteners 150 inserted into the support cylinders 140 allows for unrestricted placement and number of fasteners 150, enabling multiple fasteners 150 to be installed axially and radially on the support body 100, thus improving the stability of the connection between the support cylinders 140. Preferably, the fasteners 150 are screws.

[0068] Furthermore, the fasteners 150 are arranged at circumferential intervals around the support body 100 to improve the stability of the connection between adjacent support cylinders 140.

[0069] See Figure 1 , Figure 2 and Figure 3 In one embodiment, in any two adjacent support cylinders 140, the axial length of the inner support cylinder 140 is greater than or equal to the axial length of the outer support cylinder 140, thereby facilitating the installation and disassembly of each support cylinder 140, improving the installation and disassembly efficiency of the magnetic resonance radio frequency coil assembly, and enhancing the adaptability of the magnetic resonance radio frequency coil assembly.

[0070] In particular, along the axial direction of the support body 100, the length of the RF shielding layer 300 laid on the second support surface 120 is greater than the length of the RF coil 200 laid on the first support surface 110, thereby providing a better shielding effect for the RF coil 200.

[0071] See Figure 1 , Figure 2 and Figure 3In one embodiment, a mounting groove 160 is provided on the support cylinder 140 corresponding to the third support surface 130, and the shimming coil 400 is housed in the mounting groove 160, thereby maximizing space utilization without affecting the strength of the third support cylinder 143.

[0072] See Figure 3 , Figure 5 and Figure 6 , Figure 6 This is a schematic diagram of a shimming coil in a magnetic resonance radio frequency coil assembly provided in another embodiment of this application. In one embodiment, the shimming coil 400 is a mosquito coil type or a spiral type, thereby increasing the local magnetic field and improving the shimming effect. The shimming coil 400 is an array of multiple mosquito coil type or spiral type coils arranged in rows and columns, with each shimming coil 400 recessed in the mounting groove 160. This facilitates optimization by relevant shimming algorithms, achieving better uniformity and resulting in better images.

[0073] The currents of the different shimming coils 400 can be set to be the same or different. In one embodiment, the current of the shimming coil 400 can be determined by the following steps:

[0074] The spherical harmonic decomposition of the magnetic field strength at a point in the scanned field of view yields:

[0075]

[0076] in, spherical coordinate system The target magnetic field below; It is a polynomial; and Let be the expansion coefficient, and The magnetic field contribution of the superconducting coil that forms the superconducting magnet. The magnetic field contribution corresponding to the shim coil 400; Let be the radius of the superconducting coil. The radius of the shim coil is 400.

[0077] Based on the expansion coefficient, the magnitude of the current in the superconducting coil and the shimming coil 400 can be set to achieve shimming optimization.

[0078] In yet another embodiment, the current of the shimming coil 400 can be determined as follows:

[0079] First, the arrangement and relative positional relationship of the multiple shimming coils 400 are determined. In this embodiment, the shimming coils 400 are placed in the mounting slot 160 in an array to form a uniformly distributed shimming array coil.

[0080] Secondly, the magnetic field distribution of the superconducting coil of the superconducting magnet is measured, and the magnetic field distribution is spherically harmonicly expanded to obtain the ununiform field component of the main magnetic field harmonic expansion.

[0081] Finally, based on the arrangement and relative positions of the multiple shimming coils 400, the current of each shimming coil 400 is optimized to ensure that the local field generated by the shimming coil 400 is equivalent to the harmonics of the main magnetic field expanding to the shimming component. The support cylinder 140 corresponding to the first support surface 110 also has a mounting groove 160, in which the radio frequency coil 200 can be installed, thereby maximizing space utilization without affecting the strength of the first support cylinder 141.

[0082] See Figure 1 , Figure 2 and Figure 3 In one embodiment, the bottom wall of the mounting slot 160 has heat dissipation holes, which facilitates heat dissipation of the shimming coil 400 and improves the service life of the magnetic resonance radio frequency coil assembly.

[0083] See Figure 1 , Figure 2 and Figure 3 In one embodiment, there are three support cylinders 140, with the first support surface 110, the second support surface 120 and the third support surface 130 located on the cylinder walls of the three support cylinders 140 respectively.

[0084] Specifically, the support body 100 further includes a second support cylinder 142, which is disposed between the first support cylinder 141 and the third support cylinder 143, and a second support surface 120 is disposed on the second support cylinder 142. By disposing the first support surface 110, the second support surface 120, and the third support surface 130 on the first support cylinder 141, the second support cylinder 142, and the third support cylinder 143, respectively, interference between the RF coil 200, the RF shielding layer 300, and the shimming coil 400 can be reduced, thereby improving the reliability of the magnetic resonance RF coil assembly.

[0085] Furthermore, the support cylinder 140 with a first support surface 110 has a first groove, which is located on the same side of the support cylinder 140 as the first support surface 110. This allows the circuit connected to the RF coil 200 to be placed within the first groove, maximizing space utilization. The support cylinder 140 with a second support surface 120 has a second groove, which is located on the same side of the support cylinder 140 as the second support surface 120. This allows the circuit connected to the RF shielding layer 300 to be placed within the second groove, maximizing space utilization. The support cylinder 140 with a third support surface 130 has a third groove, which is located on the same side of the support cylinder 140 as the third support surface 130. This allows the circuit connected to the shimming coil 400 to be placed within the third groove, maximizing space utilization.

[0086] See Figure 1 , Figure 2 and Figure 3 In one embodiment, the magnetic resonance radio frequency coil assembly further includes two protective rings 170, which are sleeved on the support 100 and located at two ends of the support 100 along its own axial direction.

[0087] Specifically, the first support cylinder 141 has the longest length in the axial direction of the support body 100, and both ends of the first support cylinder 141 extend beyond the second support cylinder 142. Two protective rings 170 are respectively disposed at both ends of the first support cylinder 141, so that when installing or disassembling the magnetic resonance radio frequency coil assembly, the magnetic resonance radio frequency coil assembly can be prevented from rubbing against the gradient coil, thereby improving the reliability of the magnetic resonance radio frequency coil assembly.

[0088] This invention also provides a head magnetic resonance imaging (MRI) scanner, which can be used as a dedicated head scanner, capable of creating a dedicated space to accommodate the head and meeting the requirements for high-precision head imaging. (See also...) Figures 7-11 , Figure 7 A simplified diagram illustrating the interaction between a head magnetic resonance imaging (MRI) scanner and the human body, as provided in an embodiment of this application. Figure 8 This is a schematic diagram of a partial cross-section of a head magnetic resonance imaging (MRI) scanner provided in an embodiment of this application. Figure 9 This is a schematic diagram of a head magnetic resonance scanning device provided in an embodiment of this application, in which the radio frequency coil is mounted on a first support surface. Figure 10 This is a schematic diagram of the radio frequency shielding layer installed on the second support surface in a head magnetic resonance scanning device provided in an embodiment of this application. Figure 11This is a schematic diagram of a head magnetic resonance imaging (MRI) scanner according to an embodiment of this application, showing a shimming coil mounted on a third support surface. The head MRI scanner includes a magnet coil 500, a support body 100, a radio frequency (RF) coil 200, an RF shielding layer 300, and a shimming coil 400. The magnet coil 500 forms a magnet cavity. The support body 100 is disposed within the magnet cavity and includes a first segment 111 and a second segment 112 connected adjacent to each other. The diameter of the first segment 111 is smaller than the diameter of the second segment 112. The first segment 111 of the support body 100 includes a first support surface 110, a second support surface 120, and a third support surface 130 arranged circumferentially around itself, with the first support surface 110, the second support surface 120, and the third support surface 130 sequentially nested from the inside out. The RF coil 200 is disposed on the first support surface 110. The RF shielding layer 300 is disposed on the second support surface 120. The shimming coil 400 is disposed on the third support surface 130.

[0089] Specifically, in this application, by providing a first support surface 110, a second support surface 120, and a third support surface 130 sequentially nested on the support body 100, the radio frequency coil 200, the radio frequency shielding layer 300, and the shimming coil 400 can be respectively installed on the first support surface 110, the second support surface 120, and the third support surface 130. Since the second support surface 120 is located outside the first support surface 110, the radio frequency shielding layer 300 is located outside the radio frequency coil 200, thereby shielding interference signals. And by providing the third support surface 130 outside the second support surface 120, the shimming coil 400 can be arranged on the third support surface 130, thereby achieving local or global optimization of magnetic field uniformity, improving magnetic field uniformity, and thus improving imaging effect.

[0090] See Figures 8-11 In one embodiment, the first segment 111 includes at least two support cylinders 140 arranged sequentially from the inside to the outside, with the first support surface 110 and the third support surface 130 located on the cylinder walls of the two support cylinders 140 respectively; a gradient coil is provided between the third support surface 130 and the magnet coil 500.

[0091] Specifically, in this application, by setting a first support surface 110, a second support surface 120, and a third support surface 130 sequentially nested from the inside out on the support body 100, the radio frequency coil 200, the radio frequency shielding layer 300, and the shimming coil 400 can be respectively installed on the first support surface 110, the second support surface 120, and the third support surface 130. A gradient coil is set between the third support surface 130 and the magnet coil 500, so that the shimming coil 400 can be set between the gradient coil and the radio frequency shielding layer 300. This allows for the spatial installation of the shimming coil 400, achieving local or global optimization of the magnetic field uniformity, improving the magnetic field uniformity, and thus improving the imaging effect.

[0092] It should be noted that the head magnetic resonance scanning device in this application includes the magnetic resonance radio frequency coil assembly described in any of the above embodiments, and its specific description will not be repeated here.

[0093] See Figures 8-11 In one embodiment, the head magnetic resonance imaging (MRI) scanner further includes:

[0094] The scanning bed 700 is capable of moving within the magnet cavity to the junction area between the first segment 111 and the second segment 112. Specifically, the magnet coil 500 forms the magnet cavity, the scanning bed 700 can enter the magnet cavity, and the scanning bed 700 is used to carry the subject being tested.

[0095] See Figures 8-11 In one embodiment, the head magnetic resonance imaging device has a patient end and a service end facing each other, with a second segment 112 disposed at the patient end and a first segment 111 disposed at the service end; the dimension of the second segment 112 along the axial direction of the magnet cavity is smaller than the dimension of the first segment 111 along the axial direction of the magnet cavity.

[0096] Specifically, in this embodiment, the side of the scanning bed 700 coupled to the magnet cavity is the patient end, where the technician can guide the patient's positioning and set scanning parameters. The patient can adjust the scanning bed 700 up and down on the patient end and can move into the magnet cavity with the scanning bed 700. The opposite side is the service end.

[0097] The support body 100 is located inside the gradient coil and includes a first segment 111 and a second segment 112 connected adjacent to each other. The diameter of the first segment 111 is smaller than that of the second segment 112, creating a stepped structure on the outer periphery of the support body 100. The scanning bed 20 can move from the patient end to the service end and carry the patient to the junction area between the second segment 112 and the first segment 111. In other words, the cavity space formed by the first segment 111 is smaller than that formed by the second segment 112. The radio frequency coil 200 is located in the first segment 111 and is used to transmit radio frequency pulses to the head of the subject. The gradient coil is arranged around the outer wall of the first segment 111 and the outer wall of the second segment 112. The gradient coil is located on the outer periphery of the transmitting coil, and the cavity formed by the gradient coil is adapted to the stepped structure of the support body 100.

[0098] Compared to the support 100 having a constant cylinder diameter, when the radio frequency coil 200 scans the subject's head, the distance between the gradient coil and other components arranged on the outer wall of the first segment 111 and the subject's head is reduced because the cylinder diameter of the first segment 111 is smaller than that of the second segment 112. When the gradient coil forms a magnetic resonance image of the head, the relatively reduced distance between the two components improves the clarity of the magnetic resonance image, ensuring the accuracy of the test results. Furthermore, to alleviate the patient's fear in a confined space, the dimension of the second segment 112 along the axial direction of the magnet cavity is smaller than that of the first segment 111 along the axial direction of the magnet cavity.

[0099] See Figure 7 In one embodiment, the head magnetic resonance imaging (MRI) scanner 600 has a chamber 620 with varying aperture, and the inner wall of the head MRI scanner 600 is provided with a clearance portion 610. When the head MRI scanner 600 scans, the subject can move into the chamber 620, a portion of which can accommodate the subject's head and neck, and the clearance portion 610 corresponds to the patient's shoulder area.

[0100] To prevent electromagnetic compatibility issues and ensure system stability, the conventional RF shielding layer 300 needs to share a common ground with the entire head magnetic resonance scanning device. In this configuration, since the RF shielding layer 300 shares a fixed structure with the coil antenna, in order to maintain the RF shielding layer sharing a common ground with the overall system, the grounding point reserved at the shielding layer server end of the RF coil 200 is connected to the balun structure of the RF line, thereby achieving a common ground with the entire system.

[0101] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0102] The embodiments described above are merely illustrative of several implementation methods of this application, and while the descriptions are relatively specific and detailed, they should not be construed as limiting the scope of the patent application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this patent application should be determined by the appended claims.

Claims

1. A magnetic resonance radio frequency coil assembly, characterized in that, The radio frequency coil (200) assembly includes: The support body (100) is cylindrical in shape. The support body (100) includes a first support surface (110), a second support surface (120) and a third support surface (130) arranged around itself in a circumferential direction. The first support surface (110), the second support surface (120) and the third support surface (130) are sequentially nested from the inside to the outside. A radio frequency coil (200) is disposed on the first support surface (110). An RF shielding layer (300) is disposed on the second support surface (120); and, A shimming coil (400) is disposed on the third support surface (130).

2. The magnetic resonance radio frequency coil assembly according to claim 1, characterized in that, The support body (100) includes at least two support cylinders (140) that are sequentially nested from the inside out, with the first support surface (110) and the third support surface (130) located on the cylinder walls of the two support cylinders (140) respectively.

3. The magnetic resonance radio frequency coil assembly according to claim 2, characterized in that, The magnetic resonance radio frequency coil assembly also includes a support block, and the support block is provided between any two adjacent support cylinders (140), and each support cylinder (140) abuts against the corresponding support block.

4. The magnetic resonance radio frequency coil assembly according to claim 3, characterized in that, The magnetic resonance radio frequency coil assembly also includes at least one fastener (150), and any two adjacent support cylinders (140) are connected by the corresponding fastener (150).

5. The magnetic resonance radio frequency coil assembly according to claim 2, characterized in that, In any two adjacent support cylinders (140), the axial length of the inner support cylinder (140) is greater than or equal to the axial length of the outer support cylinder (140).

6. The magnetic resonance radio frequency coil assembly according to claim 2, characterized in that, The support cylinder (140) with the third support surface (130) is provided with an installation groove (160), and the uniform field coil (400) is housed in the installation groove (160).

7. The magnetic resonance radio frequency coil assembly according to any one of claims 2-6, characterized in that, There are three support cylinders (140), and the first support surface (110), the second support surface (120) and the third support surface (130) are respectively located on the cylinder walls of the three support cylinders (140).

8. The magnetic resonance radio frequency coil assembly according to any one of claims 1-6, characterized in that, The magnetic resonance radio frequency coil assembly also includes two protective rings (170), which are sleeved on the support (100) and located at the two ends of the support (100) along its own axial direction.

9. A head magnetic resonance imaging (MRI) scanner, characterized in that, The head magnetic resonance scanning device includes: A magnet coil (500) forms a magnet cavity; A support body (100) is disposed inside the magnet cavity. The support body (100) comprises a first segment (111) and a second segment (112) connected adjacent to each other. The diameter of the first segment (111) is smaller than the diameter of the second segment (112). The first segment (111) of the support body (100) includes a first support surface (110), a second support surface (120), and a third support surface (130) arranged around itself in a circumferential direction. The first support surface (110), the second support surface (120), and the third support surface (130) are sequentially nested from the inside to the outside. A radio frequency coil (200) is disposed on the first support surface (110). An RF shielding layer (300) is disposed on the second support surface (120); and, A shimming coil (400) is disposed on the third support surface (130).

10. The head magnetic resonance imaging (MRI) scanner according to claim 9, characterized in that, The first segment (111) includes at least two support cylinders (140) that are sequentially nested from the inside out, with the first support surface (110) and the third support surface (130) located on the cylinder walls of the two support cylinders (140), respectively. A gradient coil is provided between the third support surface (130) and the magnet coil (500).

11. The head magnetic resonance imaging (MRI) scanner according to claim 10, characterized in that, The head magnetic resonance scanning device also includes: The scanning bed (700) is capable of moving within the magnet cavity to the junction area of ​​the first segment (111) and the second segment (112).

12. The head magnetic resonance imaging (MRI) scanner according to claim 11, characterized in that, The head magnetic resonance scanning device includes a patient end and a service end facing each other at the front and back; The second segment (112) is located at the patient end; The first segment (111) is located on the server side; the second segment (112) has a smaller dimension along the axial direction of the magnet cavity than the first segment (111) along the axial direction of the magnet cavity.

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