System and method for performing magnetic resonance imaging

Abstract

According to various embodiments, a magnetic resonance imaging system is provided. According to various embodiments, the system includes a housing having a front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmission coil, and at least one gradient coil group. According to various embodiments, the RF transmission coil and the at least one gradient coil group are positioned close to the front surface. According to various embodiments, the RF transmission coil and the at least one gradient coil group are configured to generate an electromagnetic field in a region of interest. According to various embodiments, the permanent magnet has an aperture passing through its center. According to various embodiments, the region of interest is located outside the front surface.

Description

Background Technology

[0001] Magnetic resonance imaging (MRI) systems primarily focus on utilizing a closed shape factor. This shape factor involves surrounding the imaging area with materials and imaging system components that generate electromagnetic fields. A typical MRI system includes a cylindrical bore magnet, in which the patient is placed inside the magnet's tube for imaging. Components such as radio frequency (RF) transmit (TX) and receive (RX) coils, gradient coils, and permanent magnets are positioned accordingly to generate the necessary magnetic field within the tube for imaging the patient.

[0002] Therefore, most current MRI systems suffer from several drawbacks, some of which are illustrated below. First, these systems occupy a large space, often requiring installation in hospitals or external imaging centers. Second, the enclosed nature of MRI systems makes interventions (e.g., image-guided interventions such as MRI-guided biopsies, treatment planning, robotic surgery, and radiotherapy) more difficult. Third, placing the main magnet components, as discussed above, almost around the patient, as is the case with most current MRI systems, severely restricts patient movement, often causing patient panic within the MRI system and adding extra burden during patient placement or removal from the imaging area. In other current MRI systems, the patient is placed between two large plates to alleviate some of the physical limitations on patient placement. In any case, there is a need for next-generation MRI systems that offer modern imaging configurations to reduce space requirements and allow for office MRI procedures on a wide range of regions of interest. MRI system designs that allow for a variety of image-guided interventions are also needed. Furthermore, MRI system designs that improve patient experience and facilitate patient scanning are required. Summary of the Invention

[0003] According to various embodiments, a magnetic resonance imaging system is provided. According to various embodiments, the system includes a housing having a front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmit coil, and a unilateral gradient coil assembly. According to various embodiments, the RF transmit coil and the unilateral gradient coil assembly are positioned close to the front surface. According to various embodiments, the system includes an electromagnet, an RF receive coil, and a power supply. According to various embodiments, the power supply is configured to allow current to flow through at least one of the RF transmit coil, the unilateral gradient coil assembly, or the electromagnet to generate an electromagnetic field in a region of interest. According to various embodiments, the region of interest is located outside the front surface.

[0004] According to various embodiments, a magnetic resonance imaging system is provided. According to various embodiments, the system includes a housing having a recessed front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmitting coil, and at least one gradient coil group. According to various embodiments, the RF transmitting coil and the at least one gradient coil group are positioned proximate to the recessed front surface. According to various embodiments, the RF transmitting coil and the at least one gradient coil group are configured to generate an electromagnetic field in a region of interest. According to various embodiments, the region of interest is located outside the recessed front surface. According to various embodiments, the system includes an RF receiving coil for detecting signals in the region of interest.

[0005] According to various embodiments, a method for performing magnetic resonance imaging is provided. The method includes: inputting patient parameters into a magnetic resonance imaging system, the system including: a housing including: an anterior surface; a permanent magnet for providing a static magnetic field; a radio frequency (RF) transmit coil; and a unilateral gradient coil group, wherein the RF transmit coil and the unilateral gradient coil group are positioned proximal to the anterior surface; an electromagnet; an RF receive coil; and a power source, wherein the power source is configured to cause current to flow through at least one of the RF transmit coil, the unilateral gradient coil group, or the electromagnet to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the anterior surface; performing a patient positioning protocol, including running at least one first scan; running at least one second scan; examining at least one second scan; and determining at least one path for performing a biopsy based on the examination of the at least one second scan.

[0006] According to various embodiments, a method for performing magnetic resonance imaging is provided. The method includes: inputting patient parameters into a magnetic resonance imaging system, the system including: a housing including: a recessed anterior surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmitting coil, and at least one gradient coil group, wherein the RF transmitting coil and the at least one gradient coil group are positioned proximate to the recessed anterior surface, wherein the RF transmitting coil and the at least one gradient coil group are configured to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the recessed anterior surface; and an RF receiving coil for detecting a signal in the region of interest; performing a patient positioning protocol including running at least one first scan; running at least one second scan; examining at least one second scan; and determining at least one path for performing a biopsy based on the examination of the at least one second scan.

[0007] According to various embodiments, a method for performing a scan on a magnetic resonance imaging system is provided. The method includes: providing a housing comprising: a front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmitting coil, and a unilateral gradient coil group, wherein the RF transmitting coil and the unilateral gradient coil group are positioned proximate to the front surface; providing an electromagnet; activating at least one of the RF transmitting coil, the unilateral gradient coil group, or the electromagnet to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the front surface; activating an RF receiving coil to acquire imaging data; reconstructing the acquired imaging data to produce an output image for analysis; and displaying the output image for user review and annotation.

[0008] According to various embodiments, a method for performing a scan on a magnetic resonance imaging system is provided. The method includes: providing a housing comprising: a recessed front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmitting coil, and at least one gradient coil group, wherein the RF transmitting coil and the at least one gradient coil group are positioned proximate to the front surface; activating at least one of the RF transmitting coil and the at least one gradient coil group to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the recessed front surface; activating an RF receiving coil to acquire imaging data; reconstructing the acquired imaging data to generate an output image for analysis; and displaying the output image for user review and annotation.

[0009] These and other aspects and implementations are discussed in detail below. The foregoing information and the following detailed description include illustrative examples of the aspects and implementations, and provide an overview or framework for understanding the nature and characteristics of the claimed aspects and implementations. The accompanying drawings provide illustration and further understanding of the aspects and implementations, and are incorporated into and constitute a part of this specification. Attached Figure Description

[0010] The accompanying drawings are not intended to be drawn to scale. The same reference numerals and names in the various drawings denote the same elements. For clarity, not every component is labeled in every drawing. In the accompanying drawings:

[0011] Figure 1 This is a schematic diagram of a magnetic resonance imaging system according to various embodiments.

[0012] Figure 2A This is a schematic diagram of a magnetic resonance imaging system according to various embodiments.

[0013] Figure 2B The diagram shows Figure 2A The diagram shows an exploded view of the magnetic resonance imaging system.

[0014] Figure 2C It is based on each implementation method Figure 2A A schematic front view of the magnetic resonance imaging system shown.

[0015] Figure 2D It is based on each implementation method Figure 2A A schematic side view of the magnetic resonance imaging system shown.

[0016] Figure 3 This is a schematic diagram of the implementation scheme of the magnetic imaging device according to various embodiments.

[0017] Figure 4 This is a schematic diagram of the implementation scheme of the magnetic imaging device according to various embodiments.

[0018] Figure 5 This is a schematic front view of a magnetic resonance imaging system 500 according to various embodiments.

[0019] Figure 6A This is an example schematic diagram of an array of radio frequency receiving coils (RF-RX) including individual coil elements, according to various embodiments.

[0020] Figure 6B It is based on example illustrations of the toroidal coils in various embodiments and example calculations of the magnetic field of the toroidal coils.

[0021] Figure 6C The exemplary XY diagrams according to the various embodiments disclosed herein show the magnetic field as a function of the radius of the loop coil.

[0022] Figure 6D This is a cross-sectional view of the prostate region, a part of the human body.

[0023] Figure 7 This is a flowchart of a method for performing magnetic resonance imaging according to various embodiments.

[0024] Figure 8 This is a flowchart of another method for performing magnetic resonance imaging according to various embodiments.

[0025] Figure 9 This is a flowchart of a method for performing a scan on a magnetic resonance imaging system according to various embodiments.

[0026] Figure 10 This is a flowchart of another method for performing a scan on a magnetic resonance imaging system according to various embodiments.

[0027] Figures 11A to 11X The illustrations depict various patient positions according to different embodiments, depending on the type of anatomical scan used for imaging in a magnetic resonance imaging system.

[0028] It should be understood that the accompanying drawings are not necessarily drawn to scale, and the objects in the drawings are not necessarily drawn to scale according to their relationship to each other. The drawings are illustrations intended to make clear and understandable the various embodiments of the apparatuses, systems, and methods disclosed herein. Where possible, the same reference numerals will be used throughout the drawings to denote the same or similar parts. Furthermore, it should be understood that the drawings are not intended to limit the scope of this teaching in any way. Detailed Implementation

[0029] The following descriptions of various embodiments are merely exemplary and illustrative and should not be construed as limiting or restrictive in any way. Other embodiments, features, objects, and advantages of this teaching will become apparent from the specification, drawings, and claims.

[0030] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0031] Unless otherwise specified, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which the various embodiments pertain.

[0032] For the purpose of describing and disclosing the apparatus, compositions, formulations, and methods described herein and that may be used in conjunction with the contents of this disclosure, all publications mentioned herein are incorporated herein by reference.

[0033] As used herein, the terms “comprising,” “including,” “containing,” and “having,” and variations thereof, are not intended to be restrictive but rather inclusive or open-ended, and do not exclude additional, unlisted additives, components, wholes, elements, or method steps. For example, a treatment, method, system, composition, kit, or apparatus that includes the list of features is not necessarily limited to those features but may include other features not expressly listed or inherent to such treatment, method, system, composition, kit, or apparatus.

[0034] As discussed herein, and according to various embodiments, various combinations of systems and features constituting various system implementations may include a magnetic resonance imaging (MRI) system. According to various embodiments, the MRI system is a unilateral MRI system including a magnetic resonance imaging scanner or a magnetic resonance imaging spectrometer. According to various embodiments, the MRI system may include a magnet assembly for providing the magnetic field required to image anatomical sites of a patient. According to various embodiments, the MRI system may be configured to image in a region of interest located outside the magnet assembly.

[0035] Typical magnetic resonance components used in modern magnetic resonance imaging (MRI) systems include, for example, cage coil configurations. A typical cage configuration includes, for example, a radio frequency (RF) transmit coil, which may include two large loops placed on opposite sides of the imaging region (i.e., the region of interest where the patient is located), each of which is electrically connected by one or more crossbars. Since the more coils surrounding the patient, the better the imaging signal, cage coils are typically configured to surround the patient, ensuring sufficiently homogeneous signals generated from the imaging region—that is, the region of interest where the patient's anatomical target site is located. To improve patient comfort and reduce the cumbersome movement limitations of current MRI systems, the disclosures described herein generally relate to MRI systems, including unilateral MRI systems, and their applications.

[0036] As described herein, the disclosed unilateral magnetic resonance imaging (MRI) system can be configured to image a patient from one side while providing access to the patient from both sides. This is possible due to the following unilateral MRI system, which includes an access aperture (also referred to herein as an "aperture," "hole," or "hole") configured to project a magnetic field onto a region of interest completely outside the magnet assembly and MRI system. Because it is not completely surrounded by the material and imaging system components that generate the electromagnetic field, as in prior art systems, the novel unilateral configuration described herein provides less restriction on patient movement while reducing unnecessary burden during patient placement and / or removal from the MRI system. According to the various embodiments described herein, by placing the magnet assembly on one side of the patient during imaging, the patient will not feel trapped within the disclosed MRI system. As discussed herein, the disclosed system components enable configurations that allow for unilateral imaging or imaging from one side.

[0037] According to various embodiments, this document discloses various combinations of systems and features constituting various system components and embodiments of the disclosed magnetic resonance imaging system.

[0038] According to various embodiments, a magnetic resonance imaging system is disclosed herein. According to various embodiments, the system includes a housing having a front surface, a permanent magnet for providing a static magnetic field, an access aperture (also referred to herein as a "aperture," "hole," or "hole") within the permanent magnet assembly, a radio frequency (RF) transmit coil, and a single-sided gradient coil assembly. According to various embodiments, the RF transmit coil and the single-sided gradient coil assembly are positioned close to the front surface. According to various embodiments, the system includes an electromagnet, an RF receive coil, and a power supply. According to various embodiments, the power supply is configured to allow current to flow through at least one of the RF transmit coil, the single-sided gradient coil assembly, or the electromagnet to generate an electromagnetic field in a region of interest. According to various embodiments, the region of interest is located outside the front surface.

[0039] According to various embodiments, the radio frequency transmitting coil and the single-sided gradient coil group are located on the front surface. According to various embodiments, the front surface is a recessed surface. According to various embodiments, the permanent magnet has a hole passing through the center of the permanent magnet. According to various embodiments, the static magnetic field of the permanent magnet ranges from 1 mT to 1 T. According to various embodiments, the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

[0040] According to various embodiments, the radio frequency (RF) transmitting coil includes a first loop and a second loop connected via one or more capacitors and / or one or more crossbars. According to various embodiments, the RF transmitting coil is non-planar and oriented to partially surround the region of interest. According to various embodiments, a unilateral gradient coil group is non-planar and oriented to partially surround the region of interest. According to various embodiments, the unilateral gradient coil group is configured to project a magnetic field gradient onto the region of interest. According to various embodiments, the unilateral gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first and second positions being opposite each other with respect to the central region of the unilateral gradient coil group. According to various embodiments, the unilateral gradient coil group has a rise time of less than 10 μs.

[0041] According to various embodiments, an electromagnet is configured to alter the static magnetic field of a permanent magnet within the region of interest. According to various embodiments, the electromagnet has a magnetic field strength ranging from 10 mT to 1 T. According to various embodiments, the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging within the region of interest. According to various embodiments, the radio frequency receiving coil is one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest. According to various embodiments, the radio frequency transmitting coil and the unilateral gradient coil group are concentric with respect to the region of interest. According to various embodiments, the magnetic resonance imaging system is a unilateral magnetic resonance imaging system, which includes an aperture having an opening positioned around a central region of the anterior surface.

[0042] According to various embodiments, a magnetic resonance imaging system is disclosed herein. According to various embodiments, the system includes a housing having a recessed front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmitting coil, and at least one gradient coil group. According to various embodiments, the RF transmitting coil and the at least one gradient coil group are positioned proximate to the recessed front surface. According to various embodiments, the RF transmitting coil and the at least one gradient coil group are configured to generate an electromagnetic field in a region of interest. According to various embodiments, the region of interest is located outside the recessed front surface. According to various embodiments, the system includes an RF receiving coil for detecting signals in the region of interest.

[0043] According to various embodiments, the radio frequency (RF) transmitting coil and the single-sided gradient coil group are located on the recessed front surface. According to various embodiments, the static magnetic field of the permanent magnet ranges from 1 mT to 1 T. According to various embodiments, the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT. According to various embodiments, the RF transmitting coil includes a first loop and a second loop connected via one or more capacitors and / or one or more crossbars. According to various embodiments, the RF transmitting coil is non-planar and oriented to partially surround the region of interest. According to various embodiments, at least one gradient coil group is non-planar, single-sided, and oriented to partially surround the region of interest. According to various embodiments, at least one gradient coil group is configured to project a magnetic field gradient onto the region of interest.

[0044] According to various embodiments, at least one gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first and second positions being opposite each other with respect to the central region of the at least one gradient coil group. According to various embodiments, the at least one gradient coil group has a rise time of less than 10 μs. According to various embodiments, the permanent magnet has an aperture passing through its center. According to various embodiments, the system further includes an electromagnet configured to change the static magnetic field of the permanent magnet within the region of interest. According to various embodiments, the electromagnet has a magnetic field strength ranging from 10 mT to 1 T. According to various embodiments, the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging within the region of interest. According to various embodiments, the radio frequency receiving coil is one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

[0045] According to various embodiments, the radio frequency transmission coil and at least one gradient coil group are concentric with respect to the region of interest. According to various embodiments, the magnetic resonance imaging system is a unilateral magnetic resonance imaging system comprising a magnetic resonance imaging scanner or a magnetic resonance imaging spectrometer.

[0046] Figure 1This is a schematic diagram of a magnetic resonance imaging system 100 according to various embodiments. The system 100 includes a housing 120. (As...) Figure 1 As shown, housing 120 includes a permanent magnet 130, an RF transmitting coil 140, a gradient coil assembly 150, an optional electromagnet 160, an RF receiving coil 170, and a power supply 180. According to various embodiments, system 100 may include various electronic components, such as, but not limited to, varactors, PIN diodes, capacitors, or switches (including microelectromechanical systems (MEMS) switches), solid-state relays, or mechanical relays. According to various embodiments, the various electronic components listed above may be configured with the RF transmitting coil 140.

[0047] Figure 2A This is a schematic diagram of a magnetic resonance imaging system 200 according to various embodiments. Figure 2B The figure shows an exploded view of the magnetic resonance imaging system 200. Figure 2C This is a schematic front view of a magnetic resonance imaging system 200 according to various embodiments. Figure 2D This is a schematic side view of a magnetic resonance imaging system 200 according to various embodiments. (e.g.) Figure 2A and Figure 2B As shown, the magnetic resonance imaging system 200 includes a housing 220. The housing 220 includes a front surface 225. According to various embodiments, the front surface 225 may be a recessed front surface. According to various embodiments, the front surface 225 may be a concave front surface.

[0048] like Figure 2A and Figure 2B As shown, housing 220 includes a permanent magnet 230, an RF transmitting coil 240, a gradient coil assembly 250, an optional electromagnet 260, and an RF receiving coil 270. Figure 2C and Figure 2D As shown, the permanent magnet 230 may include a plurality of magnets arranged in an array configuration. The plurality of magnets of the permanent magnet 230 are illustrated as covering the entire surface, such as... Figure 2C The front view is shown, and illustrated as bars in the horizontal direction, as... Figure 2D As shown in the side view. Figure 2A As shown, the main permanent magnet may include access apertures 235 for accessing the patient from multiple sides of the system.

[0049] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0050] permanent magnet

[0051] As discussed herein, and according to various embodiments, various combinations of systems and features constituting various system implementations may include permanent magnets.

[0052] According to various embodiments, the permanent magnet 230 provides a static magnetic field in the region of interest 290 (also referred to herein as a "given field of view"). According to various embodiments, the permanent magnet 230 may include, for example... Figure 2C and Figure 2D The diagram shows a plurality of cylindrical permanent magnets arranged in parallel. According to various embodiments, the permanent magnets 230 may comprise any suitable magnetic material, including but not limited to rare-earth-based magnetic materials, such as, for example, Nd-based magnetic materials. Figure 2A As shown, the main permanent magnet may include access apertures 235 for accessing the patient from multiple sides of the system.

[0053] According to various embodiments, for a given field of view, the static magnetic field of the permanent magnet 230 can vary from about 50 mT to about 60 mT, about 45 mT to about 65 mT, about 40 mT to about 70 mT, about 35 mT to about 75 mT, about 30 mT to about 80 mT, about 25 mT to about 85 mT, about 20 mT to about 90 mT, about 15 mT to about 95 mT, and about 10 mT to about 100 mT. The magnetic field can also vary from about 10 mT to about 15 mT, about 15 mT to about 20 mT, about 20 mT to about 25 mT, about 25 mT to about 30 mT, about 30 mT to about 35 mT, about 35 mT to about 40 mT, about 40 mT to about 45 mT, about 45 mT to about 50 mT, about 50 mT to about 55 mT, about 55 mT to about 60 mT, about 60 mT to about 65 mT, about 65 mT to about 70 mT, about 70 mT to about 75 mT, about 75 mT to about 80 mT, about 80 mT to about 85 mT, about 85 mT to about 90 mT, about 90 mT to about 95 mT and about 95 mT to about 100 mT. According to various embodiments, the static magnetic field of the permanent magnet 230 can also vary from about 1 mT to about 1 T, about 10 mT to about 195 mT, about 15 mT to about 900 mT, about 20 mT to about 800 mT, about 25 mT to about 700 mT, about 30 mT to about 600 mT, about 35 mT to about 500 mT, about 40 mT to about 400 mT, about 45 mT to about 300 mT, about 50 mT to about 200 mT, about 50 mT to about 100 mT, about 45 mT to about 100 mT, about 40 mT to about 100 mT, about 35 mT to about 100 mT, about 30 mT to about 100 mT, about 25 mT to about 100 mT, about 20 mT to about 100 mT, and about 15 mT to about 100 mT.

[0054] According to various embodiments, the permanent magnet 230 may include a hole 235 at its center. According to various embodiments, the permanent magnet 230 may not include a hole. According to various embodiments, the hole 235 may have a diameter between 1 inch and 20 inches. According to various embodiments, the hole 235 may have a diameter between 1 inch and 4 inches, between 4 inches and 8 inches, and between 10 inches and 20 inches. According to various embodiments, a given field of view may be a spherical or cylindrical field of view, such as… Figure 2A and Figure 2B As shown. According to various embodiments, the diameter of the spherical field of view can be between 2 inches and 20 inches. According to various embodiments, the spherical field of view can have a diameter between 1 inch and 4 inches, between 4 inches and 8 inches, and between 10 inches and 20 inches. According to various embodiments, the length of the cylindrical field of view is approximately between 2 inches and 20 inches. According to various embodiments, the cylindrical field of view can have a length between 1 inch and 4 inches, between 4 inches and 8 inches, and between 10 inches and 20 inches.

[0055] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0056] RF transmitting coil

[0057] As discussed herein, and according to various embodiments, the various combinations of systems and features constituting the various system implementations may also include a radio frequency transmitting coil.

[0058] Figure 3 This is a schematic diagram illustrating the implementation scheme of the magnetic imaging device 300 according to various embodiments. For example... Figure 3 As shown, the device 300 includes an RF transmitting coil 320 that projects RF power outward from the coil 320. The coil 320 has two loops 322 and 324 connected by one or more crossbars 326. Figure 3 As shown, coil 320 is also connected to power supply 350a and / or power supply 350b (collectively referred to herein as "power supply 350"). According to various embodiments, power supplies 350a and 350b can be configured for power input and / or signal input, and are generally referred to as coil inputs. According to various embodiments, power supplies 350a and / or 350b are configured to provide contact via electrical contacts 352 and 354 by attaching electrical contacts 352a and / or 352b (collectively referred to herein as "electrical contacts 352") and electrical contacts 354a and / or 354b (collectively referred to herein as "electrical contacts 354") to one or more crossbars 326. Coil 320 is configured to project a uniform RF field within field of view 340. According to various embodiments, field of view 340 is the region of interest (i.e., imaging region) for magnetic resonance imaging where the patient is located. Since the patient is located in field of view 340, which is remote from coil 320, device 300 is suitable for unilateral magnetic resonance imaging systems. According to various embodiments, coil 320 can be powered, for example, by two signals that are 90 degrees out of phase with each other via quadrature excitation.

[0059] According to various embodiments, coil 320 includes ring 322 and ring 324, which are coaxially positioned along the same axis but spaced a certain distance apart. Figure 3As shown. According to various embodiments, the spacing between rings 322 and 324 ranges from about 0.1m to about 10m. According to various embodiments, the spacing between rings 322 and 324 ranges from about 0.2m to about 5m, about 0.3m to about 2m, about 0.2m to about 1m, about 0.1m to about 0.8m, or about 0.1m to about 1m, including any spacing in between. According to various embodiments, coil 320 includes rings 322 and 324, which are non-coaxial but positioned in the same direction and spaced apart by a distance ranging from about 0.2m to about 5m. According to various embodiments, rings 322 and 324 may also be tilted relative to each other. According to various embodiments, the tilt angle can be from 1 degree to 90 degrees, from 1 degree to 5 degrees, from 5 degrees to 10 degrees, from 10 degrees to 25 degrees, from 25 degrees to 45 degrees, and from 45 degrees to 90 degrees.

[0060] According to various embodiments, rings 322 and 324 have the same diameter. According to various embodiments, rings 322 and 324 have different diameters, and ring 322 has a larger diameter than ring 324, such as... Figure 3 As shown. According to various embodiments, rings 322 and 324 have different diameters, and ring 322 has a smaller diameter than ring 324. According to various embodiments, rings 322 and 324 of coil 320 are configured to create an imaging region in a field of view 340 containing a uniform RF power distribution, which is not centered within the RF-TX coil but is projected outward from the coil itself in space.

[0061] According to various embodiments, the diameter of ring 322 is between about 10 μm and about 10 μm. According to various embodiments, the diameter of ring 322 is between about 0.001 μm and about 9 μm, between about 0.01 μm and about 8 μm, between about 0.03 μm and about 6 μm, between about 0.05 μm and about 5 μm, between about 0.1 μm and about 3 μm, between about 0.2 μm and about 2 μm, between about 0.3 μm and about 1.5 μm, between about 0.5 μm and about 1 μm, or between about 0.01 μm and about 3 μm, including any diameter in between.

[0062] According to various embodiments, the diameter of ring 324 is between about 10 μm and about 10 μm. According to various embodiments, the diameter of ring 324 is between about 0.001 μm and about 9 μm, between about 0.01 μm and about 8 μm, between about 0.03 μm and about 6 μm, between about 0.05 μm and about 5 μm, between about 0.1 μm and about 3 μm, between about 0.2 μm and about 2 μm, between about 0.3 μm and about 1.5 μm, between about 0.5 μm and about 1 μm, or between about 0.01 μm and about 3 μm, including any diameter in between.

[0063] According to various embodiments, rings 322 and 324 are connected by one or more crossbars 326, such as Figure 3 As shown. According to various embodiments, one or more crossbars 326 are connected to rings 322 and 324 to form a single circuit loop (or a single current loop). Figure 3 As shown, for example, one end of one or more crossbars 326 is connected to electrical contact 352 of power supply 350, and the other end of one or more crossbars 326 is connected to electrical contact 354, so that coil 320 completes the circuit.

[0064] According to various embodiments, ring 322 is a discontinuous ring, and electrical contacts 352 and 354 can be electrically connected to two opposite ends of ring 322 to form a circuit powered by power supply 350. Similarly, according to various embodiments, ring 324 is a discontinuous ring, and electrical contacts 352 and 354 can be electrically connected to two opposite ends of ring 324 to form a circuit powered by power supply 350.

[0065] According to various embodiments, rings 322 and 324 are not circular, but may have an elliptical, square, rectangular, or trapezoidal cross-section, or any shape or form with a closed loop. According to various embodiments, rings 322 and 324 may have a cross-section varying in two different axial planes, wherein the primary axis is circular and the secondary axis has a sinusoidal shape or some other geometry. According to various embodiments, coil 320 may include more than two rings 322 and 324, each ring being connected by a crossbar spanning and connecting all the rings. According to various embodiments, coil 320 may include more than two rings 322 and 324, each ring being connected by a crossbar at alternating connection points between the rings. According to various embodiments, ring 322 may include physical openings for access. According to various embodiments, ring 322 may be a solid sheet without physical openings.

[0066] According to various embodiments, coil 320 generates an electromagnetic field (also referred to herein as a "magnetic field") strength between approximately 1 μT and approximately 10 mT. According to various embodiments, coil 320 may generate a magnetic field strength between approximately 10 μT and approximately 5 mT, between approximately 50 μT and approximately 1 mT, or between approximately 100 μT and approximately 1 mT, or any magnetic field strength in between.

[0067] According to various embodiments, coil 320 generates an electromagnetic field with radio frequency pulsations between approximately 1 kHz and approximately 2 GHz. According to various embodiments, coil 320 generates a magnetic field with radio frequency pulsations between approximately 1 kHz and approximately 1 GHz, between approximately 10 kHz and approximately 800 MHz, between approximately 50 kHz and approximately 300 MHz, between approximately 100 kHz and approximately 100 MHz, between approximately 10 kHz and approximately 10 MHz, between approximately 10 kHz and approximately 5 MHz, between approximately 1 kHz and approximately 2 MHz, between approximately 50 kHz and approximately 150 kHz, between approximately 80 kHz and approximately 120 kHz, between approximately 800 kHz and approximately 1.2 MHz, between approximately 100 kHz and approximately 10 MHz, or between approximately 1 MHz and approximately 5 MHz, including any frequencies between them.

[0068] According to various embodiments, coil 320 is oriented to partially surround the region of interest. According to various embodiments, rings 322, 324, and one or more crossbars 326 are non-planar relative to each other. In other words, rings 322, 324, and one or more crossbars 326 form a three-dimensional structure surrounding the region of interest where the patient is located. According to various embodiments, ring 322 is closer to the region of interest than ring 324, such as... Figure 3 As shown. According to various embodiments, the region of interest has a size of approximately 0.1 m to approximately 1 m. According to various embodiments, the region of interest is smaller than the diameter of ring 322. According to various embodiments, the region of interest is smaller than both the diameter of ring 324 and the diameter of ring 322, as... Figure 3 As shown. According to various embodiments, the size of the region of interest is smaller than the diameter of ring 322 and larger than the diameter of ring 324.

[0069] According to various embodiments, rings 322, 324, or crossbars 326 comprise the same material. According to various embodiments, rings 322, 324, or crossbars 326 comprise different materials. According to various embodiments, rings 322, 324, or crossbars 326 comprise hollow or solid tubes. According to various embodiments, hollow or solid tubes may be configured for air or fluid cooling. According to various embodiments, each of rings 322, 324, or crossbars 326 comprises one or more conductive windings. According to various embodiments, the windings comprise Litz wire or any conductive wire. These additional windings can be used to improve performance by reducing the resistance of the windings at a desired frequency. According to various embodiments, rings 322, 324, or crossbars 326 comprise copper, aluminum, silver, silver paste, or any highly conductive material, including metals, alloys, or superconducting metals, alloys, or non-metals. According to various embodiments, rings 322, 324, or crossbars 326 may comprise metamaterials.

[0070] According to various embodiments, rings 322, 324, or crossbars 326 may include separate non-conductive thermal control channels designed to maintain the temperature of the structure at a specified setting. According to various embodiments, the thermal control channels may be made of conductive material and integrated to carry current.

[0071] According to various embodiments, coil 320 includes one or more electronic components for tuning the magnetic field. The one or more electronic components may include a varactor, a PIN diode, a capacitor, or a switch (including a microelectromechanical system (MEMS) switch), a solid-state relay, or a mechanical relay. According to various embodiments, the coil may be configured to include any of the one or more electronic components along the circuit. According to various embodiments, the one or more components may include a high-permeability alloy (mu metal), a dielectric, a non-actively conductive magnetic or metallic component, and may tune the coil. According to various embodiments, the one or more electronic components for tuning include at least one of a dielectric, a conductive metal, a metamaterial, or a magnetic metal. According to various embodiments, tuning the electromagnetic field includes changing the current or by changing the physical position of one or more electronic components. According to various embodiments, the coil is cryogenically cooled to reduce resistance and improve efficiency. According to various embodiments, the first and second loops include multiple windings or Litz wires.

[0072] According to various embodiments, coil 320 is configured for use in a magnetic resonance imaging system having a magnetic field gradient across the field of view. The field gradient allows for imaging of slices of the field of view without the use of an additional electromagnetic gradient. As disclosed herein, the coil can be configured to generate a large bandwidth by combining multiple center frequencies, each having its own bandwidth. By superimposing these multiple center frequencies with their respective bandwidths, coil 320 can efficiently generate a large bandwidth in a desired frequency range between approximately 1 kHz and approximately 2 GHz. According to various embodiments, coil 320 generates a magnetic field with radio frequency pulsations between about 10 kHz and about 800 MHz, about 50 kHz and about 300 MHz, about 100 kHz and about 100 MHz, about 10 kHz and about 10 MHz, about 10 kHz and about 5 MHz, about 1 kHz and about 2 MHz, about 50 kHz and about 150 kHz, about 80 kHz and about 120 kHz, about 800 kHz and about 1.2 MHz, about 100 kHz and about 10 MHz, or about 1 MHz and about 5 MHz, including any frequencies therein.

[0073] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0074] Gradient coil group

[0075] As discussed herein, and according to various embodiments, the various combinations of systems and features constituting the various system implementations may also include gradient coil groups.

[0076] Figure 4 This is a schematic diagram of the implementation scheme of the magnetic imaging device 400 according to various embodiments. For example... Figure 4 As shown, the device 400 includes a gradient coil assembly 420 (also referred to herein as a unilateral gradient coil assembly 420) configured to project a gradient magnetic field outwards from the coil assembly 420 and within a field of view 430. According to various embodiments, the field of view 430 is the region of interest (i.e., the imaging region) for magnetic resonance imaging of the patient. Because the patient is located in the field of view 430, which is remote from the coil assembly 420, the device 400 is suitable for unilateral MRI systems.

[0077] As shown in the figure, coil group 420 includes helical coils of various sizes in groups of helical coils 440a, 440b, 440c, and 440d (collectively referred to as "helical coils 440"). Each group of helical coils 440 includes at least one helical coil and Figure 4 The diagram shows three spiral coils. According to various embodiments, each spiral coil 440 has an electrical contact at its center and an electrical contact output at its outer edge, to form a single operating loop of conductive material spiraling outward from the center to the outer edge, and vice versa. According to various embodiments, each spiral coil 440 has a first electrical contact at a first position and a second electrical contact at a second position, to form a single operating loop of conductive material from the first position to the second position, and vice versa.

[0078] like Figure 4As shown, the coil assembly 420 also includes an aperture 425 at its center, around which a helical coil 440 is disposed. The aperture 425 itself does not contain any coil material for generating magnetic material. The coil assembly 420 also includes an opening 427 on the outer edge of the coil assembly 420 to which the helical coil 440 can be disposed. In other words, the aperture 425 and the opening 427 define the boundary of the coil assembly 420 within which the helical coil 440 can be disposed. According to various embodiments, the coil assembly 420 is formed in a bowl shape with a central hole.

[0079] According to various embodiments, a helical coil 440 is formed across an aperture 425. For example, a helical coil 440a is disposed opposite to the helical coil 440c with respect to the aperture 425. Similarly, a helical coil 440b is disposed opposite to the helical coil 440d with respect to the aperture 425. According to various embodiments, Figure 4 The spiral coil 440 in the coil group 420 shown is configured to create spatial coding in the magnetic gradient field within the field of view 430.

[0080] like Figure 4 As shown, coil group 420 is also connected to power supply 450 via electrical contacts 452 and 454 by attaching electrical contacts 452 and 454 to one or more helical coils 440. According to various embodiments, electrical contact 452 is connected to one of the helical coils 440, which is then connected in series and / or parallel to other helical coils 440, and then another helical coil 440 is connected to electrical contact 454 to form a current loop. According to various embodiments, all helical coils 440 are electrically connected in series. According to various embodiments, all helical coils 440 are electrically connected in parallel. According to various embodiments, some helical coils 440 are electrically connected in series, while other helical coils 440 are electrically connected in parallel. According to various embodiments, helical coil 440a is electrically connected in series, while helical coil 440b is electrically connected in parallel. According to various embodiments, helical coil 440c is electrically connected in series, while helical coil 440d is electrically connected in parallel. The electrical connections between each helical coil or between groups of helical coils 440 can be configured as needed to generate a magnetic field in the field of view 430.

[0081] According to various embodiments, the coil assembly 420 includes, for example: Figure 4The unfolded helical coil 440 is shown. According to various embodiments, each set of helical coils 440a, 440b, 440c, and 440d is configured as a line from the aperture 425 to the opening 427, such that each set of helical coils is separated from each other at an angle of 90°. According to various embodiments, 440a and 440b are set at 45° to each other, and 440c and 440d are set at 45° to each other, while 440c is set at 135° on the other side of 440b, and 440d is set at 135° on the other side of 440a. Essentially, for any number of “n” sets of helical coils 440, any set of helical coils 440 can be configured in any arrangement.

[0082] According to various embodiments, the helical coils 440 have the same diameter. According to various embodiments, each group of helical coils 440a, 440b, 440c, and 440d has the same diameter. According to various embodiments, the helical coils 440 have different diameters. According to various embodiments, each group of helical coils 440a, 440b, 440c, and 440d has different diameters. According to various embodiments, the helical coils in each group of helical coils 440a, 440b, 440c, and 440d have different diameters. According to various embodiments, 440a and 440b have the same first diameter and 440c and 440d have the same second diameter, but the first diameter and the second diameter are different.

[0083] According to various embodiments, each helical coil in the helical coil 440 has a diameter between about 10 μm and about 10 m. According to various embodiments, the diameter of each helical coil in the helical coil 440 is between about 0.001 m and about 9 m, between about 0.005 m and about 8 m, between about 0.01 m and about 6 m, between about 0.05 m and about 5 m, between about 0.1 m and about 3 m, between about 0.2 m and about 2 m, between about 0.3 m and about 1.5 m, between about 0.5 m and about 1 m, or between about 0.01 m and about 3 m, including any diameter in between.

[0084] According to various embodiments, the spiral coils 440 are connected to form a single circuit loop (or a single current loop). For example... Figure 4 As shown, for example, one spiral coil of the spiral coil 440 is connected to the electrical contact 452 of the power supply 450, while the other spiral coil is connected to the electrical contact 454, so that the spiral coil 440 completes the circuit.

[0085] According to various embodiments, the coil assembly 420 generates an electromagnetic field strength between approximately 1 μT and approximately 10 T (also referred to herein as an "electromagnetic field gradient" or "gradient magnetic field"). According to various embodiments, the coil assembly 420 can generate an electromagnetic field strength between approximately 100 μT and approximately 1 T, between approximately 1 mT and approximately 500 mT, or between approximately 10 mT and approximately 100 mT, including any magnetic field strength in between. According to various embodiments, the coil assembly 420 can generate an electromagnetic field strength greater than approximately 1 μT, approximately 10 μT, approximately 100 μT, approximately 1 mT, approximately 5 mT, approximately 10 mT, approximately 20 mT, approximately 50 mT, approximately 100 mT, or approximately 500 mT.

[0086] According to various embodiments, the coil group 420 generates an electromagnetic field that pulsates at a rate having a rise time of less than about 100 μs. According to various embodiments, the coil group 420 generates an electromagnetic field that pulsates at a rate having a rise time of less than about 1 μs, about 5 μs, about 10 μs, about 20 μs, about 30 μs, about 40 μs, about 50 μs, about 100 μs, about 200 μs, about 500 μs, about 1 ms, about 2 ms, about 5 ms, or about 10 ms.

[0087] According to various embodiments, coil groups 420 are oriented to partially surround the region of interest in the field of view 430. According to various embodiments, the helical coils 440 are non-planar relative to each other. According to various embodiments, helical coil groups 440a, 440b, 440c, and 440d are non-planar relative to each other. In other words, the helical coils 440 and each group of helical coils 440a, 440b, 440c, and 440d form a three-dimensional structure surrounding the region of interest in the field of view 430 where the patient is located.

[0088] According to various embodiments, the helical coil 440 comprises the same material. According to various embodiments, the helical coil 440 comprises different materials. According to various embodiments, the helical coils in group 440a comprise the same first material, the helical coils in group 440b comprise the same second material, the helical coils in group 440c comprise the same third material, and the helical coils in group 440d comprise the same fourth material, but the first, second, third, and fourth materials are different materials. According to various embodiments, the first and second materials are the same material, but this same material is different from the same third and fourth materials. Essentially, depending on the configuration of the coil group 420, any helical coil 440 may have the same or different materials.

[0089] According to various embodiments, the helical coil 440 includes a hollow tube or a solid tube. According to various embodiments, the helical coil 440 includes one or more windings. According to various embodiments, the windings include Litz wire or any conductive wire. According to various embodiments, the helical coil 440 includes copper, aluminum, silver, silver paste, or any highly conductive material, including metals, alloys, or superconducting metals, alloys, or non-metals. According to various embodiments, the helical coil 440 includes metamaterials.

[0090] According to various embodiments, the coil assembly 420 includes one or more electronic components for tuning the magnetic field. The one or more electronic components may include PIN diodes, mechanical relays, solid-state relays, or switches (including microelectromechanical systems (MEMS) switches). According to various embodiments, the coil may be configured to include any of the electronic components along the circuit. According to various embodiments, the one or more components may include highly permeable alloys, dielectrics, non-actively conductive magnetic or metallic components, and may tune the coil. According to various embodiments, the one or more electronic components for tuning include at least one of conductive metals, metamaterials, or magnetic metals. According to various embodiments, tuning the electromagnetic field includes changing the current or by changing the physical position of one or more electronic components. In some implementations, the coil is cryogenically cooled to reduce resistance and improve efficiency.

[0091] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0092] electromagnet

[0093] As discussed herein, and according to various embodiments, the various combinations of systems and features constituting the various system implementations may also include electromagnets.

[0094] Figure 5 This is a schematic front view of a magnetic resonance imaging system 500 according to various embodiments. According to various embodiments, system 500 can be any magnetic resonance imaging system, including, for example, a unilateral magnetic resonance imaging system that includes a magnetic resonance imaging scanner or a magnetic resonance imaging spectrometer as disclosed herein.

[0095] like Figure 5As shown, system 500 includes a housing 520 that can accommodate various components, including, but not limited to, magnets, electromagnets, coils for generating radio frequency fields, and various electronic components for controlling, powering, and / or monitoring system 500. According to various embodiments, housing 520 may house, for example, a permanent magnet 230, a radio frequency transmitting coil 240, and / or a gradient coil assembly 250. According to various embodiments, system 500 also includes a central aperture 535. Figure 5 As shown, housing 520 also includes a front surface 525 of system 500. According to various embodiments, the front surface 525 may be curved, flat, recessed, convex, or otherwise have a straight or curved surface. According to various embodiments, magnetic resonance imaging system 500 may be configured to provide a region of interest in field of view 530.

[0096] like Figure 5 As shown, system 500 includes an electromagnet 560 disposed near the front surface 525 of system 500. According to various embodiments, the electromagnet 560 is positioned near the center of the front surface 525 on the front side of system 500. According to various embodiments, the electromagnet 560 may be a solenoid coil configured to create, for example, a field added to or subtracted from the magnetic field of permanent magnet 230. According to various embodiments, this field may create a pre-polarized field for enhancing the signal or contrast from nuclear magnetic resonance.

[0097] like Figure 5 As shown, a given field of view 530 is located at the center of the front surface 525 of the system 500. According to various embodiments, an electromagnet 560 is disposed within the given field of view 530. According to various embodiments, the electromagnet 560 is disposed concentrically with the given field of view 530. According to various embodiments, the electromagnet 560 can be inserted into a hole 535. According to various embodiments, the electromagnet 560 can be placed close to the hole 535. For example, the electromagnet 560 can be placed in front of, behind, or in the middle of the hole 535. According to various embodiments, the electromagnet 560 can be placed close to the entrance of the hole 535 or placed at the entrance.

[0098] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0099] RF receiving coil

[0100] As discussed herein, and according to various embodiments, the various combinations of systems and features constituting the various system implementations may also include a radio frequency receiving coil.

[0101] A typical MR system creates a uniform field within the imaging region. This uniform field then generates a narrow band of magnetic resonance frequencies, which can then be captured, amplified, and digitized by a spectrometer using a receiving coil. Because the frequencies are within a narrow, well-defined bandwidth, the hardware architecture focuses on creating a statically tuned RF-RX coil with an optimal coil quality factor. Numerous variations of the coil structure have been created, exploring large single-volume coils, coil arrays, parallel coil arrays, or body-specific coil arrays. However, all of these structures are based on imaging a specific frequency at a high field strength close to the region of interest and within the smallest possible magnetoapex.

[0102] According to various embodiments, an MRI system is provided that may include a unique imaging region that can be offset from the surface of a magnet and is therefore unobstructed compared to conventional scanners. Furthermore, this shape factor may have a built-in magnetic field gradient that creates a range of field values ​​over the region of interest. Finally, compared to typical MRI systems, this system can operate at lower magnetic field strengths, allowing for reduced constraints on RX coil design and enabling the use of other mechanisms such as robots with MRI.

[0103] According to various embodiments, the unique architecture of the main magnetic field of an MRI system can create a different set of optimization constraints. Since the imaging volume now extends to a wider range of magnetic resonance frequencies, the hardware can be configured to be sensitive to and capture specific frequencies generated within the field of view. This frequency spread is typically much larger than the frequency spread that a single receiving coil tuned to a single frequency can be sensitive to. Furthermore, since the field strength can be much lower than in conventional systems, and since the signal strength can be proportional to the field strength, maximizing the signal-to-noise ratio of the receiving coil network is generally considered beneficial. Therefore, according to various embodiments, methods are provided for acquiring the entire frequency range generated within the field of view without sacrificing sensitivity.

[0104] According to various embodiments, several methods are provided for imaging within an MRI system. These methods may include combinations of: 1) variable-tunable RF-RX coils; 2) RF-RX coil arrays having elements tuned to frequencies dependent on spatial inhomogeneities of the magnetic field; 3) ultra-low noise preamplifier designs; and 4) RF-RX arrays having multiple receiving coils designed to optimize signals from a defined and limited field of view for a specific body part. These methods can be combined arbitrarily as needed.

[0105] According to various embodiments, the variable-tunable RF-RX coil may include one or more electronic components for tuning the electromagnetic receiving field. According to various embodiments, the one or more electronic components may include at least one of a varactor, a PIN diode, a capacitor, an inductor, a MEMS switch, a solid-state relay, or a mechanical relay. According to various embodiments, the one or more electronic components for tuning may include at least one of a dielectric, a capacitor, an inductor, a conductive metal, a metamaterial, or a magnetic metal. According to various embodiments, tuning the electromagnetic receiving field includes changing the current or by changing the physical position of one or more electronic components. According to various embodiments, the coil is cryogenically cooled to reduce resistance and improve efficiency.

[0106] According to various embodiments, the RF-RX array may include individual coil elements, each tuned to a variety of frequencies. For example, an appropriate frequency can be selected to match the frequency of the magnetic field located at a specific spatial position of a particular coil. Since the magnetic field can vary as a function of space, such as... Figure 6A As shown, the field and frequency of the coil can therefore be adjusted to roughly match the spatial location. Here, the coil can be designed to image field locations B1, B2, and B3 that are physically separated along a single axis.

[0107] For this low-field system, according to various embodiments, a low-noise preamplifier can be designed and configured to utilize the low-signal environment of the MRI system. This low-noise amplifier can be configured to utilize components that do not generate significant electronic and voltage noise at the desired frequencies (e.g., <3MHz and >2MHz). Typical junction field-effect transistor (J-FET) designs generally do not have suitable noise characteristics at these frequencies and generate high-frequency instabilities in the GHz range, which, although low by several decibels (dB), can permeate the measurement frequency range. Since the system gain can preferably be, for example, >80dB overall, any small instability or inherent electrical noise can be amplified and degrade signal integrity.

[0108] Reference Figure 6B RF-RX coils can be designed to image specific, limited fields of view based on target anatomical structures. For example, the prostate gland is approximately 60 millimeters deep within the human body (see...). Figure 6D Therefore, an RX coil for prostate imaging needs to be designed, configured to image at a depth of 60 mm within the human body. According to the Biot-Savart law, the magnetic field of the loop coil can be calculated using the following formula:

[0109]

[0110] Where μ0 = 4π × 10⁻⁷ H / m is the free permeability, R is the radius of the toroidal coil, z is the distance along the center line of the coil to its center, and I is the current in the coil (see...). Figure 6B Assuming I = 1 ampere, the goal is to locate the magnetic field (Bz) graph at z = 60 mm. Based on... Figure 6C The maximum position shown in the chart is when R is 85mm.

[0111] Due to the geometric constraints of the body, a loop coil can be positioned in the space between the legs on the torso. Therefore, while not impossible, fitting a 170mm diameter coil there is extremely difficult. Figure 6C When R is less than 85mm, the Bz field value is proportional to the loop radius. Therefore, it is advantageous to make the coil as large as possible. For example, the largest loop coil that can be placed between people is about 10mm in size.

[0112] Because the size of the coil is limited by the space between the legs, the magnetic field of a 10mm diameter coil typically cannot reach the depth of the prostate. Therefore, a single coil may be insufficient for prostate imaging; thus, multiple coils can prove advantageous in this case for acquiring signals from different directions. In various embodiments of the MRI system, a magnetic field is provided in the z-direction, and the RF coil is sensitive to both the x and y directions. In this example case, a loop coil in the xy-plane would not collect radiofrequency signals from the person because it is sensitive to the z-direction, whereas a butterfly coil could be used in this situation. The RF coil can then be either a loop coil or a butterfly coil, depending on its location and orientation. Additionally, the coil can be placed under the body, and its size is not limited.

[0113] Regarding the need for multiple RX coils, decoupling between them can prove advantageous in various implementations of RX coil arrays for MRI systems. In these cases, each coil can be decoupled from the other coils, and decoupling techniques can include, for example, 1) geometric decoupling, 2) capacitive / inductive decoupling, and 3) low / high impedance preamplifier coupling.

[0114] According to various embodiments, the MRI system may have a varying magnetic field from a magnet, and its intensity may vary linearly along the z-direction. The RX coils may be located at different positions in the z-direction, and each coil may be tuned to a different frequency, depending on the position of the coils in the system.

[0115] Due to the simplicity of single-coil circuits, these coils can be constructed from simple conductive traces that can be pre-tuned to the desired frequency and printed on, for example, a disposable substrate. This inexpensive manufacturing technique allows clinicians to place RX coils (or coil arrays) on the body at the region of interest for a given procedure and subsequent coil disposal. For example, and according to various embodiments, the RX coil can be a surface coil that can be attached (e.g., worn or adhered to) the patient's body. For other body parts, such as the ankle or wrist, surface coils can be in a single-loop configuration, a figure-eight configuration, or a butterfly coil configuration wound around the region of interest. For areas requiring considerable penetration depth, such as the torso or knee, the coil can consist of Helmholtz coil pairs. The main limitation of the receiving coil is similar to that of other MRI systems: the coil must be sensitive to a plane orthogonal to the B0 axis of the main magnetic field.

[0116] According to various implementations, the coil can be inductively coupled to another circuit that is electrically connected to the receiver preamplifier. This design will allow for easier and more unobstructed access to the receiver coil.

[0117] According to various embodiments, the size of the coil can be limited by the human body structure. For example, when imaging the prostate, the size of the coil should be positioned and configured to fit the space between the legs.

[0118] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0119] Programmable Logic Controller

[0120] As discussed herein, and according to various embodiments, the various combinations of systems and features constituting the various system implementations may also include programmable logic controllers (PLCs). A PLC is an industrial digital computer designed to operate reliably in harsh operating environments and conditions. A PLC can be designed to handle these types of conditions and environments not only within its enclosure but also within its internal components and cooling systems. Therefore, PLCs are suitable for controlling manufacturing processes, such as assembly lines or robotic equipment, or any activity requiring high-reliability control as well as ease of programming and troubleshooting.

[0121] According to various implementations, the system may include a PLC capable of controlling the system in pseudo-real-time. This controller can manage the power cycling and enabling of the gradient amplifier system, RF transmission system, and frequency tuning system, and send keep-alive signals (e.g., messages sent from one device to another to check if the link between the two devices is operational or to prevent link breach) to the system watchdog. The system watchdog continuously searches for strobe signals provided by the computer system. If the computer thread stops running, it will miss a strobe signal that could trigger the watchdog to enter a fault condition. If the watchdog enters a fault condition, the watchdog can be operated to shut down the system power.

[0122] PLCs typically handle low-level logic functions on incoming and outgoing signals within a system. This system can monitor the health of subsystems and control when power is needed or when a subsystem is enabled. PLCs can be designed in various ways. One design example includes a PLC with a main board and four expansion boards. Due to the speed of the microcontroller on the PLC, subsystems can be managed in pseudo-real-time mode, while real-time applications can be handled by a computer or spectrometer on the system.

[0123] A PLC can provide a number of functional responsibilities, including, for example, turning on / off the power supply of gradient amplifiers (discussed in more detail herein) and RF amplifiers (discussed in more detail herein), enabling / disabling gradient amplifiers and RF amplifiers, setting digital and analog voltages for RF coil tuning, and strobing the system watchdog.

[0124] It should be understood that any use of subheadings in this document is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0125] robot

[0126] As discussed herein, and according to various embodiments, the various combinations of systems and features constituting the various system implementations may also include robots.

[0127] In some medical procedures, such as prostate biopsies, patients often endure lengthy processes in an uncomfortable prone position, which typically involves remaining immobile in a specific body posture throughout the procedure. During such extended procedures, if a metallic ferromagnetic needle is used for the biopsy under the guidance of an MRI system, the needle may be attracted by the strong magnets of the MRI system, potentially causing it to deviate from its path throughout the process. Even when using non-magnetic needles, localized field distortion can lead to MRI image distortion, and therefore, the image quality around the needle may be poor. To avoid this distortion, pneumatic robots with compound compressed air mechanisms have been designed to work in conjunction with conventional MRI systems. Even so, accessing target anatomical structures remains challenging due to the shape factor of currently available MRI systems.

[0128] The embodiments described herein include improved MRI systems configured for guidance in medical procedures, including, for example, robot-assisted invasive medical procedures. The techniques, methods, and apparatuses disclosed herein relate to guided robotic systems that use magnetic resonance imaging as guidance to automatically guide robots (generally referred to herein as "robotic systems") during medical procedures. According to the embodiments, the disclosed techniques combine robotic systems with magnetic resonance imaging as guidance. According to the embodiments, the robotic systems disclosed herein are combined with other suitable imaging techniques, such as ultrasound, X-rays, lasers, or any other suitable diagnostic or imaging methods.

[0129] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0130] Spectrometer

[0131] As discussed herein, and according to various embodiments, the various combinations of systems and features constituting the various system implementations may also include a spectrometer.

[0132] The spectrometer can be operated to control all real-time signaling used to generate the image. It creates RF transmit (RF-TX) waveforms, gradient waveforms, frequency-tuned trigger waveforms, and blanking bit waveforms. These waveforms are then synchronized with the RF receiver (RF-RX) signal. The system can generate swept RF-TX pulses and phase-cycled RF-TX pulses. Sweeped RF-TX pulses allow the non-uniform B1+ field (RF-TX field) to excite the sample volume more effectively and efficiently. It can also digitize multiple RF-RX channels using the current configuration of four receiver channels. However, this system architecture allows for easy expansion of the system to increase the number of transmit and receive channels to a maximum of 32 transmit channels and 16 receive channels without changing the underlying hardware or software architecture.

[0133] Spectrometers can serve many functional duties, including, for example, generating and synchronizing RF-TX waveforms (discussed in more detail herein), X-gradient waveforms, Y-gradient waveforms, blanking bit waveforms, frequency-tuned trigger waveforms, and RF-RX windows, as well as digitizing and signal processing RF-RX data using, for example, quadrature demodulation (followed by finite impulse response filter decimation, such as, for example, cascaded integrator comb (CIC) filter decimation).

[0134] Spectrometers can be designed in different ways. One design example includes a spectrometer with three main components: 1) a first software-designed radio (SDR1) that operates with the basic RF-TX daughter card and the basic RF-RX daughter card; 2) a second software-designed radio (SDR2) that operates with the LFRF TX daughter card and the basic RF-RX daughter card; and 3) a clock distribution module (octoclock) that can synchronize the two devices.

[0135] SDRs are real-time communication devices between transmitted and received MRI signals. They can communicate with computers via 10Gbit fiber optic cables using the Small Pluggable Enhanced Transceiver (SFP+) communication protocol. This communication speed allows for waveform generation with high fidelity and high reliability.

[0136] Each SDR may include a motherboard with an integrated field-programmable gate array (FPGA), a digital-to-analog converter (DAC), an analog-to-digital converter (ADC), and four module slots for integrating different daughter cards. Each of these daughter cards can be used to modify the frequency response of the associated TX or RX channel. Depending on the implementation, the system can utilize many variant daughter cards, including, for example, a basic RF version and a low-frequency (LF) RF version. The basic RF daughter card can be used to generate and measure RF signals. The LF RF version can be used to generate gradient, trigger, and blanking bit signals.

[0137] An eight-channel clock (octoclock) can be used to synchronize a multi-channel SDR system with a common timing source while providing high-precision time and frequency reference allocation. For example, it can do this with eight time and frequency allocations (1PPS and 10MHz). An example of an eight-channel clock is the Ettus Octoclock CDA, which can allocate a common clock to up to eight SDRs to ensure phase consistency between two or more SDR sources.

[0138] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0139] RF AMP / Gradient AMP

[0140] As discussed herein, and according to various embodiments, the various combinations of systems and features constituting the various system implementations may also include radio frequency amplifiers (RF amplifiers) and gradient amplifiers.

[0141] An RF amplifier is an electronic amplifier that converts low-power radio frequency signals into higher-power signals. In operation, an RF amplifier can accept low-amplitude signals and provide gains up to 60 dB, for example, with a flat frequency response. The amplifier accepts a three-phase AC input voltage and has a maximum duty cycle of 10%. The amplifier can be gated using a 5V digital signal, preventing the generation of unwanted noise when receiving signals for MRI.

[0142] In operation, a gradient amplifier amplifies the signal's energy before it reaches the gradient coil, making the field strength strong enough to generate changes in the main magnetic field for localization of later-received signals. The gradient amplifier can have two independently controllable active amplification channels. Each channel can send current to either the X or Y channel. The spatially encoded third axis is typically processed using a permanent gradient in the main magnetic field (B0). Through combinations of pulse sequence variations, the signal can be localized and reconstructed in three dimensions to create an object.

[0143] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0144] Display / GUI

[0145] As discussed herein, and according to various embodiments, the various combinations of systems and features constituting the various system implementations may also include, for example, a display in the form of a graphical user interface (GUI). According to various embodiments, the GUI may take any desired form for conveying the information required to perform the magnetic resonance imaging procedure.

[0146] Furthermore, it should be recognized that displays can be implemented in any of a variety of other forms, such as, for example, rack-mounted computers, mainframes, supercomputers, servers, clients, desktop computers, laptops, tablets, handheld computing devices (e.g., PDAs, mobile phones, smartphones, handheld computers, etc.), clustered grids, netbooks, embedded systems, or any other type of dedicated or general-purpose display device suitable for or appropriate for a given application or environment.

[0147] A GUI is a system of interactive visual components for computer software. A GUI can display objects that convey information and present actions that a user can take. When a user interacts with an object, the object changes its color, size, or visibility. GUI objects include, for example, icons, cursors, and buttons. These graphical elements are sometimes enhanced by sound or visual effects such as transparency and shadows.

[0148] Users can interact with the GUI using input devices, which may include, for example, alphanumeric keys and other keys, a mouse, a trackball, or cursor arrow keys, to transmit directional information and command selections to the processor and to control cursor movement on the display. The input device can also be a display configured with touchscreen input capabilities. This input device typically has two degrees of freedom on two axes, namely the first axis (x) and the second axis (y), allowing the device to specify its position in a plane. However, it should be understood that input devices allowing 3D (x, y, and z) cursor movement are also anticipated.

[0149] According to various embodiments, a touchscreen or touchscreen monitor can be used as the primary human-machine interface device allowing the user to interact with the MRI. The screen may be a projected capacitive touch-sensitive display with an interactive virtual keyboard. The touchscreen may have several functions, including, for example, displaying a graphical user interface (GUI) to the user, relaying user input to a computer system, and starting or stopping the scan.

[0150] Depending on the implementation, a GUI view can typically be a screen (Qt widget) displayed to the user with appropriate buttons, editing fields, labels, images, etc. These screens can be constructed using designer tools such as the Qt Designer tool to control the widgets' arrangement, alignment, fonts, colors, etc. The user interface (UI) sub-controller can have modules configured to control the behavior (display and responsiveness) of the individual view modules.

[0151] Several application utility modules can perform specific functions. For example, the S3 module can handle data communication between the system and, for example, Amazon Web Services (AWS). Event filters can exist to ensure that valid characters are displayed on the screen when user input is required. Dialog messages can be used to display various statuses, progress messages, or prompts for the user. Furthermore, the system controller module can be used to handle coordination between sub-controller modules and key data processing blocks, pulse sequence generators, pulse interpreters, spectrometers, and reconfiguration units within the system.

[0152] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0153] Processing module

[0154] As discussed herein, and according to various embodiments, various workflows or methods, and various combinations of steps constituting various workflow or method embodiments, may also include processing modules.

[0155] According to various embodiments, the processing module provides numerous functions. For example, the processing module is typically operable to receive signal data acquired during scanning, process the data, and reconstruct these signals to produce an image that can be viewed, analyzed, and annotated by a system user (e.g., via a touchscreen monitor displaying a GUI to the user). Typically, to create an image, the NMR signal must be positioned in three-dimensional space. Magnetic gradient coils position and manipulate the signal before or during RF acquisition. By specifying a sequence of RF and gradient coil applications (called a pulse sequence), the acquired signal corresponds to a specific magnetic field and RF field arrangement. Using mathematical operators and image reconstruction techniques, the array of these acquired signals can be reconstructed into an image. These images are typically generated from a simple linear combination of magnetic field gradients. According to various embodiments, the system can be operable to reconstruct the acquired signal based on, for example, prior knowledge of the gradient field, RF field, and pulse sequence.

[0156] According to various implementations, the processing module can also be operated to compensate for patient displacement during the scanning process. Displacement (e.g., heartbeat, lung breathing, overall patient movement) is one of the most common sources of artifacts in MRI, leading to image misinterpretation and subsequent diagnostic degradation, thus affecting image quality. Therefore, displacement compensation protocols can help address these issues at minimal cost in terms of temporal and spatial resolution, temporal resolution, and signal-to-noise ratio.

[0157] According to various embodiments, the processing module may include an artificial intelligence machine learning module designed to denoise signals and improve the signal-to-noise ratio of images.

[0158] According to various embodiments, the processing module can also be operated to assist clinicians in planning pathways for subsequent patient interventions, such as biopsies. According to various embodiments, a robot can be provided as part of the system to perform the intervention. The processing module can transmit instructions to the robot based on image analysis to correctly access, for example, the appropriate area of ​​the body requiring a biopsy.

[0159] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0160] According to various embodiments, this document discloses various combinations of systems and features constituting various system components and embodiments of the disclosed magnetic resonance imaging system.

[0161] Figure 7 This is a flowchart of a method S100 for performing magnetic resonance imaging according to various embodiments. According to various embodiments, method S100 includes inputting patient parameters into a magnetic resonance imaging system in step S110. According to various embodiments, the system includes a housing having a front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmitting coil, and a unilateral gradient coil group. According to various embodiments, the RF transmitting coil and the unilateral gradient coil group are positioned close to the front surface. According to various embodiments, the system includes an electromagnet, an RF receiving coil, and a power supply. According to various embodiments, the power supply is configured to allow current to flow through at least one of the RF transmitting coil, the unilateral gradient coil group, or the electromagnet to generate an electromagnetic field in a region of interest. According to various embodiments, the region of interest is located outside the front surface.

[0162] like Figure 7 As shown, method S100 further includes: performing a patient localization protocol in step S120, including running at least one first scan; running at least one second scan in step S130; examining at least one second scan in step S140; and determining at least one path for performing a biopsy in step S150 based on the examination of at least one second scan.

[0163] According to various embodiments, the radio frequency transmitting coil and the single-sided gradient coil group are located on the front surface. According to various embodiments, the front surface is a recessed surface. According to various embodiments, the permanent magnet has a hole passing through the center of the permanent magnet. According to various embodiments, the static magnetic field of the permanent magnet ranges from 1 mT to 1 T. According to various embodiments, the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

[0164] According to various embodiments, the radio frequency (RF) transmitting coil includes a first loop and a second loop connected via one or more capacitors and / or one or more crossbars. According to various embodiments, the RF transmitting coil is non-planar and oriented to partially surround the region of interest. According to various embodiments, a unilateral gradient coil group is non-planar and oriented to partially surround the region of interest. According to various embodiments, the unilateral gradient coil group is configured to project a magnetic field gradient onto the region of interest. According to various embodiments, the unilateral gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first and second positions being opposite each other with respect to the central region of the unilateral gradient coil group. According to various embodiments, the unilateral gradient coil group has a rise time of less than 10 μs.

[0165] According to various embodiments, an electromagnet is configured to alter the static magnetic field of a permanent magnet within the region of interest. According to various embodiments, the electromagnet has a magnetic field strength ranging from 10 mT to 1 T. According to various embodiments, the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging within the region of interest. According to various embodiments, the radio frequency receiving coil is one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest. According to various embodiments, the radio frequency transmitting coil and the unilateral gradient coil group are concentric with respect to the region of interest. According to various embodiments, the magnetic resonance imaging system is a unilateral magnetic resonance imaging system, which includes an aperture having an opening positioned around a central region of the anterior surface.

[0166] Figure 8 This is a flowchart of a method S200 for performing magnetic resonance imaging according to various embodiments. According to various embodiments, method S200 includes inputting patient parameters into a magnetic resonance imaging system in step S210. According to various embodiments, the system includes a housing having a recessed front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmitting coil, and at least one gradient coil group. According to various embodiments, the RF transmitting coil and at least one gradient coil group are positioned proximate to the recessed front surface. According to various embodiments, the RF transmitting coil and at least one gradient coil group are configured to generate an electromagnetic field in a region of interest. According to various embodiments, the region of interest is located outside the recessed front surface. According to various embodiments, the system includes an RF receiving coil for detecting signals in the region of interest.

[0167] like Figure 8 As shown, method S200 includes: performing a patient localization protocol in step S220, including running at least one first scan; running at least one second scan in step S230; examining at least one second scan in step S240; and determining at least one path for performing a biopsy based on the examination of at least one second scan in step S250.

[0168] According to various embodiments, the radio frequency (RF) transmitting coil and the single-sided gradient coil group are located on the recessed front surface. According to various embodiments, the static magnetic field of the permanent magnet ranges from 1 mT to 1 T. According to various embodiments, the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT. According to various embodiments, the RF transmitting coil includes a first loop and a second loop connected via one or more capacitors and / or one or more crossbars. According to various embodiments, the RF transmitting coil is non-planar and oriented to partially surround the region of interest. According to various embodiments, at least one gradient coil group is non-planar, single-sided, and oriented to partially surround the region of interest. According to various embodiments, at least one gradient coil group is configured to project a magnetic field gradient onto the region of interest.

[0169] According to various embodiments, at least one gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first and second positions being opposite each other with respect to the central region of the at least one gradient coil group. According to various embodiments, the at least one gradient coil group has a rise time of less than 10 μs. According to various embodiments, the permanent magnet has an aperture passing through its center. According to various embodiments, the system further includes an electromagnet configured to change the static magnetic field of the permanent magnet within the region of interest. According to various embodiments, the electromagnet has a magnetic field strength ranging from 10 mT to 1 T. According to various embodiments, the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging within the region of interest. According to various embodiments, the radio frequency receiving coil is one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

[0170] According to various embodiments, the radio frequency transmission coil and at least one gradient coil group are concentric with respect to the region of interest. According to various embodiments, the magnetic resonance imaging system is a unilateral magnetic resonance imaging system comprising a magnetic resonance imaging scanner or a magnetic resonance imaging spectrometer.

[0171] Figure 9 This is a flowchart of method S300 for performing a scan on a magnetic resonance imaging system according to various embodiments. According to various embodiments, method S300 includes: providing a housing in step S310, the housing having a front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmission coil, and a unilateral gradient coil group. According to various embodiments, the RF transmission coil and the unilateral gradient coil group are positioned close to the front surface. According to various embodiments, method S300 includes providing an electromagnet in step S320. According to various embodiments, method S300 includes: activating at least one of the RF transmission coil, the unilateral gradient coil group, or the electromagnet in step S330 to generate an electromagnetic field in a region of interest. According to various embodiments, the region of interest is located outside the front surface.

[0172] According to various embodiments, method S300 includes: activating an RF receiving coil in step S340 to acquire imaging data; reconstructing the acquired imaging data in step S350 to generate an output image for analysis; and displaying the output image in step S360 for user inspection and annotation.

[0173] According to various embodiments, the radio frequency transmitting coil and the single-sided gradient coil group are located on the front surface. According to various embodiments, the front surface is a recessed surface. According to various embodiments, the permanent magnet has a hole passing through the center of the permanent magnet. According to various embodiments, the static magnetic field of the permanent magnet ranges from 1 mT to 1 T. According to various embodiments, the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

[0174] According to various embodiments, the radio frequency (RF) transmitting coil includes a first loop and a second loop connected via one or more capacitors and / or one or more crossbars. According to various embodiments, the RF transmitting coil is non-planar and oriented to partially surround the region of interest. According to various embodiments, a unilateral gradient coil group is non-planar and oriented to partially surround the region of interest. According to various embodiments, the unilateral gradient coil group is configured to project a magnetic field gradient onto the region of interest. According to various embodiments, the unilateral gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first and second positions being opposite each other with respect to the central region of the unilateral gradient coil group. According to various embodiments, the unilateral gradient coil group has a rise time of less than 10 μs.

[0175] According to various embodiments, an electromagnet is configured to alter the static magnetic field of a permanent magnet within the region of interest. According to various embodiments, the electromagnet has a magnetic field strength ranging from 10 mT to 1 T. According to various embodiments, the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging within the region of interest. According to various embodiments, the radio frequency receiving coil is one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest. According to various embodiments, the radio frequency transmitting coil and the unilateral gradient coil group are concentric with respect to the region of interest. According to various embodiments, the magnetic resonance imaging system is a unilateral magnetic resonance imaging system, which includes an aperture having an opening positioned around a central region of the anterior surface.

[0176] Figure 10 This is a flowchart of method S400 for performing a scan on a magnetic resonance imaging system according to various embodiments. According to various embodiments, method S400 includes: providing a housing in step S410 having a recessed front surface, a permanent magnet for providing a static magnetic field, a radio frequency transmission coil, and a unilateral gradient coil assembly. According to various embodiments, the radio frequency transmission coil and the unilateral gradient coil assembly are positioned close to the front surface.

[0177] According to various embodiments, method S400 includes: activating at least one of a radio frequency transmitting coil and at least one gradient coil group in step S420 to generate an electromagnetic field in a region of interest. According to various embodiments, the region of interest is located outside the recessed front surface.

[0178] According to various embodiments, method S400 includes: activating an RF receiving coil in step S430 to acquire imaging data; reconstructing the acquired imaging data in step S440 to generate an output image for analysis; and displaying the output image in step S450 for user inspection and annotation.

[0179] According to various embodiments, the radio frequency (RF) transmitting coil and the single-sided gradient coil group are located on the recessed front surface. According to various embodiments, the static magnetic field of the permanent magnet ranges from 1 mT to 1 T. According to various embodiments, the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT. According to various embodiments, the RF transmitting coil includes a first loop and a second loop connected via one or more capacitors and / or one or more crossbars. According to various embodiments, the RF transmitting coil is non-planar and oriented to partially surround the region of interest. According to various embodiments, at least one gradient coil group is non-planar, single-sided, and oriented to partially surround the region of interest. According to various embodiments, at least one gradient coil group is configured to project a magnetic field gradient onto the region of interest.

[0180] According to various embodiments, at least one gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first and second positions being opposite each other with respect to the central region of the at least one gradient coil group. According to various embodiments, the at least one gradient coil group has a rise time of less than 10 μs. According to various embodiments, the permanent magnet has an aperture passing through its center. According to various embodiments, the system further includes an electromagnet configured to change the static magnetic field of the permanent magnet within the region of interest. According to various embodiments, the electromagnet has a magnetic field strength ranging from 10 mT to 1 T. According to various embodiments, the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging within the region of interest. According to various embodiments, the radio frequency receiving coil is one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

[0181] According to various embodiments, the radio frequency transmission coil and at least one gradient coil group are concentric with respect to the region of interest. According to various embodiments, the magnetic resonance imaging system is a unilateral magnetic resonance imaging system comprising a magnetic resonance imaging scanner or a magnetic resonance imaging spectrometer.

[0182] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0183] Patient entry

[0184] As discussed herein, and according to various embodiments, workflows or methods, and various combinations of steps constituting various workflow or method embodiments, a patient entry step may also be included.

[0185] As part of this step, according to the various embodiments described herein, any and all relevant information may be part of the patient entry step, including the entry of all data related to the execution of the magnetic resonance system.

[0186] According to various embodiments, the patient entry step may include not only data entered by the user, but also data downloaded from any storage source, whether it is from a remote data storage device (e.g., the cloud), an onboard data storage device, or a portable data storage device (e.g., an external flash / solid-state drive and an external hard disk drive).

[0187] According to various embodiments, and further relating to memory sources, onboard data storage components (e.g., onboard computing systems within an MRI system) may be random access memory (RAM) or other dynamic memory, or read-only memory (ROM) or other static storage devices.

[0188] According to various embodiments, and further relating to memory sources, remote or portable data storage components may include, for example, disks, optical disks, solid-state drives (SSDs), and media drives and removable storage interfaces. Media drives may include drives or other mechanisms that support fixed or removable storage media, such as hard disk drives, floppy disk drives, magnetic tape drives, optical disk drives, CD or DVD drives (R or RW), flash memory drives, or other removable or fixed media drives. As these examples illustrate, storage media may include computer-readable storage media in which specific computer software, instructions, or data are stored.

[0189] According to various embodiments, the storage device may include other similar tools for allowing computer programs or other instructions or data to be loaded into the computing system. Such tools may include, for example, removable storage units and interfaces (such as program cartridges and cartridge interfaces), removable memory (e.g., flash memory or other removable memory modules), and memory slots that allow software and data to be transferred from the storage device to the computing system.

[0190] Depending on the implementation, the data types that can be input, uploaded, downloaded, etc., by the user may include, for example, patient name, patient gender, patient weight, patient height, patient contact information, patient date of birth, patient referring physician, and patient ethnicity. In addition, the user can input clinical baseline information, including, for example, Gleason scores from any past biopsies, frequency of sexual intercourse, last mealtime, and patient PSA levels.

[0191] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0192] Patient positioning

[0193] As discussed herein, and according to various embodiments, workflows or methods, and various combinations of steps constituting various workflow or method embodiments, a patient positioning step may also be included.

[0194] As a precursor to localization, patients typically undergo patient preparation and screening procedures, where they are screened for foreign bodies and devices that may indicate contraindications to imaging, such as pacemakers. Important health conditions (including allergies) and patient data received as part of the patient entry process are also examined.

[0195] To locate the patient in a standard whole-body MRI, the patient is typically placed on a stage, usually in a supine position. Receiver imaging coils are positioned around the body part of interest (head, chest, knees, etc.). If an EKG or respiratory gating is required, these devices are attached at this time. Key anatomical structures (such as the bridge of the nose or navel) are identified as landmarks using laser guidance and associated with the stage position by pressing a button on the gantry.

[0196] According to each implementation method, use Figures 11A to 11X The example system shown serves as the basis for this article, positioning the patient in any number of different locations depending on the type of anatomical scan.

[0197] like Figure 11A As shown, when the abdomen is the area being scanned, the patient can lie on their side on the surface. As illustrated, for an abdominal scan, the patient can be positioned in a side-lying position facing the aperture, with the arm closest to the stage extended and the other arm placed at the side. The abdominal region can be positioned so that it is directly in front of the aperture.

[0198] like Figure 11B As shown, when the appendage (e.g., an arm or hand) is the area being scanned, the patient can lie supine on the surface. As illustrated, for appendage scanning, the patient can be positioned lying down with the arm or hand to be scanned directly in front of the aperture.

[0199] like Figure 11CAs shown, the patient can also be positioned in a seated position when the appendage (e.g., arm or hand) is the area being scanned. As illustrated, for appendage scanning, the patient can be positioned sitting with the arm being scanned resting on the system and raised so that it is directly in front of the aperture.

[0200] like Figure 11D As shown, when the appendage (e.g., the elbow) is the area being scanned, the patient can also be positioned in a seated position. As illustrated, for appendage scanning, the patient can be positioned sitting with the elbow being scanned resting on the system and raised, so that the elbow is directly in front of the aperture, while the other arm rests comfortably.

[0201] like Figure 11E As shown, when the appendage (e.g., the knee) is the area being scanned, the patient can also stand with one leg raised. As illustrated, for appendage scanning, the patient can be positioned standing and facing the aperture, with the leg of interest raised, the knee placed directly in front of the aperture, and the other leg firmly placed on the ground for stability.

[0202] like Figure 11F As shown, when the appendage (e.g., the knee) is the area being scanned, the patient can also be in a lateral decubitus position. As illustrated, for appendage scanning, the patient can be positioned in a lateral decubitus position facing the aperture, with the leg of interest bent and the other leg resting on the stage and extended. The patient's knee can be placed directly in front of the aperture.

[0203] like Figure 11G As shown, when the appendage (e.g., the foot) is the area being scanned, the patient can also be in a lateral decubitus position. As illustrated, for appendage scanning, the patient can be positioned in a lateral decubitus position with their back to the aperture, the leg of interest bent and resting on the stage, while the other leg is extended. The patient's foot can be placed directly in front of the aperture.

[0204] like Figure 11H As shown, the patient can also be seated when the appendage (e.g., the foot) is the area being scanned. For appendage scanning, the patient can be positioned facing the aperture while seated, with the leg of interest extended towards the aperture and the other leg resting comfortably. The patient's foot can be placed directly in front of the aperture.

[0205] like Figure 11I As shown, when an appendage (e.g., the wrist) is the area being scanned, the patient can be seated. For appendage scanning, the patient can be positioned sitting parallel to the system, with the wrist of interest directly in front of the aperture, while the other arm rests comfortably to one side.

[0206] like Figure 11JAs shown, when the breast is the area being scanned, the patient can lie on their side on the surface. As illustrated, for a breast scan, the patient can lie on their side facing the aperture, with one arm extended above the head and the other hand placed at their side. The breast area can be directly positioned in front of the aperture.

[0207] like Figure 11K As shown, when the breast is the area being scanned, the patient can also be positioned in a seated position. As illustrated, for a breast scan, the patient can be positioned facing the aperture, sitting with their arms extended and resting on top of the system. The breast area can be positioned directly in front of the aperture.

[0208] like Figure 11L As shown, when the breast is the area being scanned, the patient can also be positioned in a kneeling position. As illustrated, for a breast scan, the patient can be positioned kneeling facing the aperture, with their arms extended and resting on top of the system. The breast area can be positioned directly in front of the aperture.

[0209] like Figure 11M As shown, when the head is the area being scanned, the patient can lie on their side on the surface. As illustrated, for head scanning, the patient can be positioned in a side-lying position with their back to the aperture, and their head placed directly in front of the aperture.

[0210] like Figure 11N As shown, when the head is the area being scanned, the patient can also lie supine on the surface. As illustrated, for head scanning, the patient can lie face up with the top of their head resting on the system, so that it is directly in front of the aperture.

[0211] like Figure 11O As shown, when the heart is the area being scanned, the patient can be positioned either sitting or standing. For example, in a cardiac scan, the patient can be positioned facing the aperture while seated, so that the heart region is directly in front of the aperture.

[0212] like Figure 11P As shown, when the kidney is the area being scanned, the patient can lie on their side on the surface. As illustrated, for a kidney scan, the patient can lie on their side facing the aperture, with the arm closest to the stage extended and the other arm placed at their side. The kidney area can be positioned directly in front of the aperture.

[0213] like Figure 11Q As shown, when the liver is the area being scanned, the patient can lie on their side on the surface. For a liver scan, the patient can lie on their side facing the aperture, with the arm closest to the stage extended or bent to support the head, and the other arm placed at the side of the body. The liver area can be positioned directly in front of the aperture.

[0214] like Figure 11RAs shown, when the lungs are the area being scanned, the patient can be positioned in a sitting position. As illustrated, for a lung scan, the patient can be positioned with their back to the aperture, so that the lung area is directly in front of the aperture.

[0215] like Figure 11S As shown, when the neck is the area being scanned, the patient can lie on their side on the surface. As also shown, for a neck scan, the patient can lie on their side with their back to the aperture. The neck region can be positioned directly in front of the aperture.

[0216] like Figure 11T As shown, when the pelvis is the area being scanned, the patient can be placed on the surface in the lithotomy position. As illustrated, for a pelvic scan, the patient can be positioned with their back resting on the platform and their legs raised to rest against the top of the system. The pelvic region can be positioned directly in front of the aperture.

[0217] like Figure 11U As shown, when the pelvis is the area being scanned, the patient can also lie on their side on the surface. As illustrated, for a pelvic scan, the patient can lie on their side with their back to the aperture. The pelvic region of the body can be directly positioned in front of the aperture.

[0218] like Figure 11V As shown, when the pelvis is the area being scanned, the patient can also be placed in a prone position. As illustrated, for a pelvic scan, the patient can be positioned with their chest resting on the surface, facing away from the aperture. The pelvic region can be positioned directly in front of the aperture.

[0219] like Figure 11W As shown, when the shoulder is the area being scanned, the patient can be positioned in a seated position. As illustrated, for shoulder scanning, the patient can be positioned sitting next to the system, with the shoulder to be scanned directly in front of the aperture.

[0220] like Figure 11X As shown, when the spine is the area being scanned, the patient can be positioned in a seated position. As illustrated, for a spinal scan, the patient can be positioned sitting with their back to the aperture, and the spine is directly within the aperture's field of view.

[0221] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0222] Biopsy guidance

[0223] As discussed herein, and according to various embodiments, workflows or methods, and various combinations of steps constituting various workflow or method embodiments, biopsy guidance using the disclosed MRI system may also be included.

[0224] According to various embodiments, the procedure for biopsy guidance using the disclosed MRI system may include one of the following medical procedures: transperineal biopsy, transperineal LDR brachytherapy, transperineal HDR brachytherapy, transperineal laser ablation, transperineal cryoablation, transrectal HIFU, breast biopsy, deep brain stimulation (DBS), brain biopsy, liver biopsy, kidney biopsy, lung biopsy, coronary artery stenting, brain stenting, and intensity-modulated radiotherapy (IMRT) guidance.

[0225] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0226] calibration

[0227] As discussed herein, and according to various embodiments, workflows or methods, and various combinations of steps constituting various workflow or method embodiments, a calibration step may also be included.

[0228] Calibration can take many forms. Typically, calibration involves running a full scan, similar to a scan performed on a patient, to ensure image quality. Depending on the implementation, the user may be prompted to initiate a calibration routine, such as an RF calibration routine, after a predetermined time period. As part of initiating calibration, a calibration phantom is positioned to allow calibration to proceed. Calibration phantoms can take many forms. Typically, a calibration phantom can be an object of known size and composition (usually an artificial object) that is imaged to test, adjust, or monitor the homogeneity, imaging performance, and orientation aspects of an MRI system. A phantom can be a fluid-filled container or bottle, typically filled with plastic structures of various sizes and shapes.

[0229] Specifically, the RF calibration routine optimizes RF pulse parameters, such as signal power, signal duration, and signal bandwidth, to ensure image quality. The calibration routine acquires signal data from the calibration phantom using a predetermined set of parameters and sequences. The calibration data can be processed to determine the set of parameters to be used during imaging scans.

[0230] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0231] Prepolarizer

[0232] As discussed herein, and according to various embodiments, workflows or methods, and various combinations of steps constituting various workflow or method embodiments, a pre-polarization step may also be included.

[0233] In some implementations, the pre-polarizer can be charged by a system power supply. The power supply to the polarizer temporarily alters the magnetic field within the field of view by increasing or decreasing the strength of the main magnetic field. This change in the magnetic field subsequently produces a change in the total number of nuclear spins aligned within the field of view, and it alters the time constant of nuclear spin relaxation. An increase in the field allows more nuclear spins to align with the field, thereby temporarily increasing the signal from a given voxel. A decrease in the field alters the relaxation characteristics of the object and can increase contrast within the field of view.

[0234] According to various embodiments, the prepolarizer can be first charged to increase the field strength and thus the signal strength. Then, after waiting for an appropriate amount of time (as indicated by the desired spin's T1 time) for nuclear spin alignment, the prepolarizer can be removed. When the prepolarizer is de-energized, the aligned spins will begin to relax and release energy, but can still be imaged by the magnetic resonance system with an increased signal level compared to when the system has not applied a prepolarization pulse.

[0235] It should be understood that any use of subheadings herein is for organizational purposes and should not be construed as limiting the application of those subheading features to the various embodiments described herein. Regardless of the specific example embodiments described herein, each feature described herein is applicable to and can be used in all embodiments discussed herein, and all features described herein can be used in any contemplated combination. It should also be noted that the exemplary descriptions using particular features are primarily for informational purposes and do not in any way limit the design, sub-features, and functionality of the specifically described features.

[0236] Description of the implementation method

[0237] 1. A magnetic resonance imaging system comprising: a housing, the housing including: a front surface; a permanent magnet for providing a static magnetic field; a radio frequency (RF) transmit coil; and a unilateral gradient coil group, wherein the RF transmit coil and the unilateral gradient coil group are positioned close to the front surface; an electromagnet; an RF receive coil; and a power supply, wherein the power supply is configured to cause current to flow through at least one of the RF transmit coil, the unilateral gradient coil group, or the electromagnet to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the front surface.

[0238] 2. The system according to embodiment 1, wherein the radio frequency transmitting coil and the single-sided gradient coil group are located on the front surface.

[0239] 3. The system according to any one of embodiments 1 to 2, wherein the front surface is a recessed surface.

[0240] 4. The system according to any one of embodiments 1 to 3, wherein the permanent magnet has a hole passing through the center of the permanent magnet.

[0241] 5. The system according to any one of embodiments 1 to 4, wherein the static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

[0242] 5-1. The system according to any one of embodiments 1 to 4, wherein the static magnetic field of the permanent magnet is in the range of 10 mT to 195 mT.

[0243] 6. The system according to any one of embodiments 1 to 5, wherein the radio frequency transmitting coil includes a first ring and a second ring connected via one or more capacitors and / or one or more crossbars.

[0244] 7. The system according to any one of embodiments 1 to 6, wherein the radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

[0245] 8. The system according to any one of embodiments 1 to 7, wherein the single-sided gradient coil group is non-planar and oriented to partially surround the region of interest, and wherein the single-sided gradient coil group is configured to project a magnetic field gradient onto the region of interest.

[0246] 9. The system according to any one of embodiments 1 to 8, wherein the single-sided gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first position and the second position being opposite to each other with respect to the central region of the single-sided gradient coil group.

[0247] 10. The system according to any one of embodiments 1 to 9, wherein the single-sided gradient coil group has a rise time of less than 10 μs.

[0248] 11. The system according to any one of embodiments 1 to 10, wherein the electromagnet is configured to change the static magnetic field of the permanent magnet in the region of interest.

[0249] 12. The system according to any one of embodiments 1 to 11, wherein the electromagnet has a magnetic field strength of 10 mT to 1 T.

[0250] 13. The system according to any one of embodiments 1 to 12, wherein the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of a patient for imaging in the region of interest.

[0251] 14. The system according to any one of embodiments 1 to 13, wherein the radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

[0252] 15. The system according to any one of embodiments 1 to 14, wherein the radio frequency transmitting coil and the single-sided gradient coil group are concentric with respect to the region of interest.

[0253] 16. The system according to any one of embodiments 1 to 15, wherein the magnetic resonance imaging system is a unilateral magnetic resonance imaging system, which includes a hole having an opening positioned around a central region of the front surface.

[0254] 17. A magnetic resonance imaging system, comprising: a housing, the housing including: a recessed front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmitting coil, and at least one gradient coil group, wherein the RF transmitting coil and the at least one gradient coil group are positioned close to the recessed front surface, wherein the RF transmitting coil and the at least one gradient coil group are configured to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the recessed front surface; and an RF receiving coil for detecting a signal in the region of interest.

[0255] 18. The system according to embodiment 17, wherein the radio frequency transmitting coil and the at least one gradient coil group are located on the recessed front surface.

[0256] 19. The system according to any one of embodiments 17 to 18, wherein the static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

[0257] 20. The system according to any one of embodiments 17 to 19, wherein the static magnetic field of the permanent magnet is in the range of 10 mT to 195 mT.

[0258] 21. The system according to any one of embodiments 17 to 20, wherein the radio frequency transmitting coil includes a first loop and a second loop connected via one or more capacitors and / or one or more crossbars.

[0259] 22. The system according to any one of embodiments 17 to 21, wherein the radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

[0260] 23. The system according to any one of embodiments 17 to 22, wherein the at least one gradient coil group is non-planar, one-sided and oriented to partially surround the region of interest, and wherein the at least one gradient coil group is configured to project a magnetic field gradient into the region of interest.

[0261] 24. The system according to any one of embodiments 17 to 23, wherein the at least one gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first position and the second position being opposite each other with respect to the central region of the at least one gradient coil group.

[0262] 25. The system according to any one of embodiments 17 to 24, wherein the at least one gradient coil group has a rise time of less than 10 μs.

[0263] 26. The system according to any one of embodiments 17 to 25, wherein the permanent magnet has a hole passing through the center of the permanent magnet.

[0264] 27. The system according to any one of embodiments 17 to 26 further includes: an electromagnet configured to change the static magnetic field of the permanent magnet in the region of interest.

[0265] 28. The system according to any one of embodiments 17 to 27, wherein the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of a patient for imaging in the region of interest.

[0266] 29. The system according to any one of embodiments 17 to 28, wherein the radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

[0267] 30. The system according to any one of embodiments 17 to 29, wherein the radio frequency transmitting coil and the at least one gradient coil group are concentric with respect to the region of interest.

[0268] 31. The system according to embodiment 27, wherein the electromagnet has a magnetic field strength of 10 mT to 1 T.

[0269] 32. The system according to any one of embodiments 17 to 31, wherein the magnetic resonance imaging system is a unilateral magnetic resonance imaging system including a magnetic resonance imaging scanner or a magnetic resonance imaging spectrometer.

[0270] 33. A method of performing magnetic resonance imaging, comprising: inputting patient parameters into a magnetic resonance imaging system, the system comprising: a housing including: a front surface; a permanent magnet for providing a static magnetic field; a radio frequency (RF) transmit coil; and a unilateral gradient coil group, wherein the RF transmit coil and the unilateral gradient coil group are positioned adjacent to the front surface; an electromagnet; an RF receive coil; and a power source, wherein the power source is configured to cause current to flow through at least one of the RF transmit coil, the unilateral gradient coil group, or the electromagnet to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the front surface; performing a patient positioning protocol including running at least one first scan; running at least one second scan; examining the at least one second scan; and determining at least one path for performing a biopsy based on the examination of the at least one second scan.

[0271] 34. The method according to embodiment 33, wherein the radio frequency transmitting coil and the single-sided gradient coil group are located on the front surface.

[0272] 35. The method according to any one of embodiments 33 to 34, wherein the front surface is a recessed surface.

[0273] 36. The method according to any one of embodiments 33 to 35, wherein the permanent magnet has a hole passing through the center of the permanent magnet.

[0274] 37. The method according to any one of embodiments 33 to 36, wherein the static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

[0275] 37-1. The method according to any one of embodiments 33 to 36, wherein the static magnetic field of the permanent magnet is in the range of 10 mT to 195 mT.

[0276] 38. The method according to any one of embodiments 33 to 37, wherein the radio frequency transmitting coil includes a first ring and a second ring connected via one or more capacitors and / or one or more crossbars.

[0277] 39. The method according to any one of embodiments 33 to 38, wherein the radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

[0278] 40. The method according to any one of embodiments 33 to 39, wherein the unilateral gradient coil group is non-planar and oriented to partially surround the region of interest, and wherein the unilateral gradient coil group is configured to project a magnetic field gradient onto the region of interest.

[0279] 41. The method according to any one of embodiments 33 to 40, wherein the unilateral gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first position and the second position being opposite to each other with respect to the central region of the unilateral gradient coil group.

[0280] 42. The method according to any one of embodiments 33 to 41, wherein the single-sided gradient coil group has a rise time of less than 10 μs.

[0281] 43. The method according to any one of embodiments 33 to 42, wherein the electromagnet is configured to change the static magnetic field of the permanent magnet in the region of interest.

[0282] 44. The method according to any one of embodiments 33 to 43, wherein the electromagnet has a magnetic field strength of 10 mT to 1 T.

[0283] 45. The method according to any one of embodiments 33 to 44, wherein the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging in the region of interest.

[0284] 46. ​​The method according to any one of embodiments 33 to 45, wherein the radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

[0285] 47. The method according to any one of embodiments 33 to 46, wherein the radio frequency transmitting coil and the single-sided gradient coil group are concentric with respect to the region of interest.

[0286] 48. The method according to any one of embodiments 33 to 47, wherein the magnetic resonance imaging system is a unilateral magnetic resonance imaging system, which includes a hole having an opening positioned around a central region of the front surface.

[0287] 49. A method of performing magnetic resonance imaging, comprising: inputting patient parameters into a magnetic resonance imaging system, the system comprising: a housing including: a recessed anterior surface; a permanent magnet for providing a static magnetic field; a radio frequency (RF) transmitting coil; and at least one gradient coil group, wherein the RF transmitting coil and the at least one gradient coil group are positioned proximate to the recessed anterior surface, wherein the RF transmitting coil and the at least one gradient coil group are configured to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the recessed anterior surface; and an RF receiving coil for detecting a signal in the region of interest; performing a patient positioning protocol including running at least one first scan; running at least one second scan; examining the at least one second scan; and determining at least one path for performing a biopsy based on the examination of the at least one second scan.

[0288] 50. The method according to embodiment 49, wherein the radio frequency transmitting coil and the at least one gradient coil group are located on the recessed front surface.

[0289] 51. The method according to any one of embodiments 49 to 50, wherein the static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

[0290] 52. The method according to any one of embodiments 49 to 51, wherein the static magnetic field of the permanent magnet is in the range of 10 mT to 195 mT.

[0291] 53. The method according to any one of embodiments 49 to 52, wherein the radio frequency transmitting coil includes a first ring and a second ring connected via one or more capacitors and / or one or more crossbars.

[0292] 54. The method according to any one of embodiments 49 to 53, wherein the radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

[0293] 55. The method according to any one of embodiments 49 to 54, wherein the at least one gradient coil group is non-planar, one-sided and oriented to partially surround the region of interest, and wherein the at least one gradient coil group is configured to project a magnetic field gradient into the region of interest.

[0294] 56. The method according to any one of embodiments 49 to 55, wherein the at least one gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first position and the second position being opposite each other with respect to the central region of the at least one gradient coil group.

[0295] 57. The method according to any one of embodiments 49 to 56, wherein the at least one gradient coil group has a rise time of less than 10 μs.

[0296] 58. The method according to any one of embodiments 49 to 57, wherein the permanent magnet has a hole passing through the center of the permanent magnet.

[0297] 59. The method according to any one of embodiments 49 to 58 further includes: an electromagnet configured to change the static magnetic field of the permanent magnet in the region of interest.

[0298] 60. The method according to any one of embodiments 49 to 59, wherein the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging in the region of interest.

[0299] 61. The method according to any one of embodiments 49 to 60, wherein the radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

[0300] 62. The method according to any one of embodiments 49 to 61, wherein the radio frequency transmitting coil and the at least one gradient coil group are concentric with respect to the region of interest.

[0301] 63. The method according to embodiment 59, wherein the electromagnet has a magnetic field strength of 10 mT to 1 T.

[0302] 64. The method according to any one of embodiments 49 to 63, wherein the magnetic resonance imaging system is a unilateral magnetic resonance imaging system including a magnetic resonance imaging scanner or a magnetic resonance imaging spectrometer.

[0303] 65. A method of performing a scan on a magnetic resonance imaging system, comprising: providing a housing including: a front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmit coil, and a unilateral gradient coil group, wherein the RF transmit coil and the unilateral gradient coil group are positioned proximate to the front surface; providing an electromagnet; activating at least one of the RF transmit coil, the unilateral gradient coil group, or the electromagnet to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the front surface; activating an RF receive coil to acquire imaging data; reconstructing the acquired imaging data to produce an output image for analysis; and displaying the output image for user inspection and annotation.

[0304] 66. The method according to embodiment 65, wherein the radio frequency transmitting coil and the single-sided gradient coil group are located on the front surface.

[0305] 67. The method according to any one of embodiments 65 to 66, wherein the front surface is a recessed surface.

[0306] 68. The method according to any one of embodiments 65 to 67, wherein the permanent magnet has a hole passing through the center of the permanent magnet.

[0307] 69. The method according to any one of embodiments 65 to 68, wherein the static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

[0308] 69-1. The method according to any one of embodiments 65 to 68, wherein the static magnetic field of the permanent magnet is in the range of 10 mT to 195 mT.

[0309] 70. The method according to any one of embodiments 65 to 69, wherein the radio frequency transmitting coil includes a first ring and a second ring connected via one or more capacitors and / or one or more crossbars.

[0310] 71. The method according to any one of embodiments 65 to 70, wherein the radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

[0311] 72. The method according to any one of embodiments 65 to 71, wherein the single-sided gradient coil group is non-planar and oriented to partially surround the region of interest, and wherein the single-sided gradient coil group is configured to project a magnetic field gradient onto the region of interest.

[0312] 73. The method according to any one of embodiments 65 to 72, wherein the unilateral gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first position and the second position being opposite to each other with respect to the central region of the unilateral gradient coil group.

[0313] 74. The method according to any one of embodiments 65 to 73, wherein the single-sided gradient coil group has a rise time of less than 10 μs.

[0314] 75. The method according to any one of embodiments 65 to 74, wherein the electromagnet is configured to change the static magnetic field of the permanent magnet in the region of interest.

[0315] 76. The method according to any one of embodiments 65 to 75, wherein the electromagnet has a magnetic field strength of 10 mT to 1 T.

[0316] 77. The method according to any one of embodiments 65 to 76, wherein the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging in the region of interest.

[0317] 78. The method according to any one of embodiments 65 to 77, wherein the radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

[0318] 79. The method according to any one of embodiments 65 to 78, wherein the radio frequency transmitting coil and the single-sided gradient coil group are concentric with respect to the region of interest.

[0319] 80. The method according to any one of embodiments 65 to 79, wherein the magnetic resonance imaging system is a unilateral magnetic resonance imaging system, which includes a hole having an opening positioned around a central region of the front surface.

[0320] 81. A method of performing a scan on a magnetic resonance imaging system, comprising: providing a housing including: a recessed front surface, a permanent magnet for providing a static magnetic field, a radio frequency (RF) transmitting coil, and at least one gradient coil group, wherein the RF transmitting coil and the at least one gradient coil group are positioned proximate to the front surface; activating at least one of the RF transmitting coil and the at least one gradient coil group to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the recessed front surface; activating an RF receiving coil to acquire imaging data; reconstructing the acquired imaging data to generate an output image for analysis; and displaying the output image for user inspection and annotation.

[0321] 82. The method according to embodiment 81, wherein the radio frequency transmitting coil and the at least one gradient coil group are located on the recessed front surface.

[0322] 83. The method according to any one of embodiments 81 to 82, wherein the static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

[0323] 84. The method according to any one of embodiments 81 to 83, wherein the static magnetic field of the permanent magnet is in the range of 10 mT to 195 mT.

[0324] 85. The method according to any one of embodiments 81 to 84, wherein the radio frequency transmitting coil comprises a first ring and a second ring connected via one or more capacitors and / or one or more crossbars.

[0325] 86. The method according to any one of embodiments 81 to 85, wherein the radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

[0326] 87. The method according to any one of embodiments 81 to 86, wherein the at least one gradient coil group is non-planar, one-sided and oriented to partially surround the region of interest, and wherein the at least one gradient coil group is configured to project a magnetic field gradient into the region of interest.

[0327] 88. The method according to any one of embodiments 81 to 87, wherein the at least one gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first position and the second position being opposite to each other with respect to the central region of the at least one gradient coil group.

[0328] 89. The method according to any one of embodiments 81 to 88, wherein the at least one gradient coil group has a rise time of less than 10 μs.

[0329] 90. The method according to any one of embodiments 81 to 89, wherein the permanent magnet has a hole passing through the center of the permanent magnet.

[0330] 91. The method according to any one of embodiments 81 to 90 further includes: an electromagnet configured to change the static magnetic field of the permanent magnet in the region of interest.

[0331] 92. The method according to any one of embodiments 81 to 91, wherein the radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging in the region of interest.

[0332] 93. The method according to any one of embodiments 81 to 92, wherein the radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

[0333] 94. The method according to any one of embodiments 81 to 93, wherein the radio frequency transmitting coil and the at least one gradient coil group are concentric with respect to the region of interest.

[0334] 95. The method according to embodiment 91, wherein the electromagnet has a magnetic field strength of 10 mT to 1 T.

[0335] 96. The method according to any one of embodiments 81 to 95, wherein the magnetic resonance imaging system is a unilateral magnetic resonance imaging system including a magnetic resonance imaging scanner or a magnetic resonance imaging spectrometer.

[0336] Although this specification contains many specific implementation details, these should not be construed as limiting the scope of any invention or the scope that may be claimed, but rather as descriptions of features specific to particular implementations of particular embodiments. Certain features described herein in the context of a single implementation may also be implemented in combination within a single implementation. Conversely, various features described in the context of a single implementation may be implemented individually or in any suitable sub-combination in multiple implementations. Furthermore, although features may be described above as functioning in certain combinations, or even initially claimed in this way, in some cases one or more features of the claimed combination may be removed from the combination, and the claimed combination may involve sub-combinations or variations thereof.

[0337] Similarly, although the operations are depicted in a specific order in the accompanying drawings, this should not be construed as requiring these operations to be performed in the specific order or sequential order shown, or to perform all the illustrated operations to achieve the desired result. In some cases, multitasking and parallel processing may be advantageous. Furthermore, the separation of the various system components in the above implementation schemes should not be construed as requiring such separation in all implementation schemes, and it should be understood that the described program components and systems can generally be integrated together into a single software product or packaged into multiple software products.

[0338] A reference to "or" can be interpreted as inclusive, meaning that any term described using "or" can refer to any one, more than one, or all of the terms described. Labels such as "first," "second," "third," etc., do not necessarily indicate order and are typically used only to distinguish identical or similar items or elements.

[0339] Various modifications to the implementations described in this disclosure will be apparent to those skilled in the art, and the general principles defined herein can be applied to other implementations without departing from the spirit or scope of this disclosure. Therefore, the claims are not intended to limit them to the implementations shown herein, but are consistent with the widest scope of this disclosure, its principles, and novel features.

Claims

1. A unilateral magnetic resonance imaging system, comprising: Housing, the housing comprising: Front surface, A hole having an opening positioned around a central region of the front surface. Permanent magnets used to provide a static magnetic field. An RF transmitting coil, the RF transmitting coil being located on the front surface and having a central region coaxial with the aperture, and A single-sided helical gradient coil group, located on the front surface and comprising a plurality of gradient coil groups arranged around a central region of the single-sided helical gradient coil group, wherein the central region of the single-sided helical gradient coil group is coaxial with the hole. Electromagnets; RF receiving coil; and A power source, wherein the power source is configured to allow current to flow through at least one of the radio frequency transmitting coil, the single-sided spiral gradient coil group, or the electromagnet to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the front surface.

2. The system according to claim 1, wherein, The front surface is a recessed surface.

3. The system according to claim 1, wherein, The permanent magnet has a hole passing through the center of the permanent magnet.

4. The system according to claim 1, wherein, The static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

5. The system according to claim 1, wherein, The radio frequency transmitting coil includes a first ring and a second ring connected via one or more capacitors and / or one or more crossbars.

6. The system according to claim 1, wherein, The radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

7. The system according to claim 1, wherein, The single-sided spiral gradient coil group is non-planar and oriented to partially surround the region of interest, and wherein the single-sided spiral gradient coil group is configured to project a magnetic field gradient onto the region of interest.

8. The system according to claim 1, wherein, The single-sided spiral gradient coil group includes one or more first spiral coils at a first position and one or more second spiral coils at a second position, the first position and the second position being opposite each other with respect to the central region of the single-sided spiral gradient coil group.

9. The system according to claim 1, wherein, The single-sided spiral gradient coil group has a rise time of less than 10 μs.

10. The system according to claim 1, wherein, The electromagnet is configured to change the static magnetic field of the permanent magnet within the region of interest.

11. The system according to claim 1, wherein, The electromagnet has a magnetic field strength of 10 mT to 1 T.

12. The system according to claim 1, wherein, The radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging in the region of interest.

13. The system according to claim 1, wherein, The radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

14. The system according to claim 1, wherein, The radio frequency transmitting coil and the single-sided spiral gradient coil group are concentric with respect to the region of interest.

15. A magnetic resonance imaging system, comprising: Housing, the housing comprising: concave in front surface, Permanent magnets used to provide a static magnetic field. RF transmitting coil, and At least one single-sided gradient coil group, The radio frequency transmitting coil and the at least one unilateral gradient coil group are positioned close to the recessed front surface, and the radio frequency transmitting coil and the at least one unilateral gradient coil group are configured to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the recessed front surface; and Radio frequency receiving coil used to detect signals in the region of interest.

16. The system according to claim 15, wherein, The radio frequency transmitting coil and the at least one single-sided gradient coil group are located on the recessed front surface.

17. The system according to claim 15, wherein, The static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

18. The system according to claim 15, wherein, The static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

19. The system according to claim 15, wherein, The radio frequency transmitting coil includes a first ring and a second ring connected via one or more capacitors and / or one or more crossbars.

20. The system according to claim 15, wherein, The radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

21. The system according to claim 15, wherein, The at least one-sided gradient coil group is non-planar and oriented to partially surround the region of interest, and wherein the at least one-sided gradient coil group is configured to project a magnetic field gradient into the region of interest.

22. The system according to claim 15, wherein, The at least one unilateral gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first position and the second position being opposite each other with respect to the central region of the at least one unilateral gradient coil group.

23. The system according to claim 15, wherein, The at least one single-sided gradient coil group has a rise time of less than 10 μs.

24. The system according to claim 15, wherein, The permanent magnet has a hole passing through the center of the permanent magnet.

25. The system of claim 15, further comprising: An electromagnet configured to change the static magnetic field of the permanent magnet within the region of interest.

26. The system according to claim 15, wherein, The radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging in the region of interest.

27. The system according to claim 15, wherein, The radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

28. The system according to claim 15, wherein, The radio frequency transmitting coil and the at least one single-sided gradient coil group are concentric with respect to the region of interest.

29. The system according to claim 25, wherein, The electromagnet has a magnetic field strength of 10 mT to 1 T.

30. The system according to claim 15, wherein, The magnetic resonance imaging system is a unilateral magnetic resonance imaging system that includes a magnetic resonance imaging scanner or a magnetic resonance imaging spectrometer.

31. A method for performing magnetic resonance imaging, the method comprising: Patient parameters are input into a unilateral magnetic resonance imaging (MRI) system, the unilateral MRI system comprising: Housing, the housing comprising: Front surface, A hole having an opening positioned around a central region of the front surface. Permanent magnets used to provide a static magnetic field. An RF transmitting coil, the RF transmitting coil being located on the front surface and having a central region coaxial with the aperture, and A single-sided helical gradient coil group, located on the front surface and comprising a plurality of gradient coil groups arranged around a central region of the single-sided helical gradient coil group, wherein the central region of the single-sided helical gradient coil group is coaxial with the hole. Electromagnets; RF receiving coil; and A power source, wherein the power source is configured to allow current to flow through at least one of the radio frequency transmitting coil, the single-sided spiral gradient coil group, or the electromagnet to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the front surface; Implement the patient localization protocol, including running at least one initial scan; Run the second scan at least once; Check the at least one second scan; and At least one path for performing a biopsy is determined based on the examination of the at least one second scan.

32. The method according to claim 31, wherein, The front surface is a recessed surface.

33. The method according to claim 31, wherein, The permanent magnet has a hole passing through the center of the permanent magnet.

34. The method according to claim 31, wherein, The static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

35. The method according to claim 31, wherein, The radio frequency transmitting coil includes a first ring and a second ring connected via one or more capacitors and / or one or more crossbars.

36. The method according to claim 31, wherein, The radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

37. The method according to claim 31, wherein, The single-sided spiral gradient coil group is non-planar and oriented to partially surround the region of interest, and wherein the single-sided spiral gradient coil group is configured to project a magnetic field gradient onto the region of interest.

38. The method according to claim 31, wherein, The single-sided spiral gradient coil group includes one or more first spiral coils at a first position and one or more second spiral coils at a second position, the first position and the second position being opposite each other with respect to the central region of the single-sided spiral gradient coil group.

39. The method according to claim 31, wherein, The single-sided spiral gradient coil group has a rise time of less than 10 μs.

40. The method according to claim 31, wherein, The electromagnet is configured to change the static magnetic field of the permanent magnet within the region of interest.

41. The method according to claim 31, wherein, The electromagnet has a magnetic field strength of 10 mT to 1 T.

42. The method according to claim 31, wherein, The radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging in the region of interest.

43. The method according to claim 31, wherein, The radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

44. The method according to claim 31, wherein, The radio frequency transmitting coil and the single-sided spiral gradient coil group are concentric with respect to the region of interest.

45. A method for performing magnetic resonance imaging, comprising: Patient parameters are input into a magnetic resonance imaging system, the system comprising: Housing, the housing comprising: concave in front surface, Permanent magnets used to provide a static magnetic field. RF transmitting coil, and At least one single-sided gradient coil group, The radio frequency transmitting coil and the at least one unilateral gradient coil group are positioned close to the recessed front surface, and the radio frequency transmitting coil and the at least one unilateral gradient coil group are configured to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the recessed front surface; and Radio frequency receiving coil for detecting signals in the region of interest; Implement the patient localization protocol, including running at least one initial scan; Run the second scan at least once; Check the at least one second scan; and At least one path for performing a biopsy is determined based on the examination of the at least one second scan.

46. ​​The method according to claim 45, wherein, The radio frequency transmitting coil and the at least one single-sided gradient coil group are located on the recessed front surface.

47. The method according to claim 45, wherein, The static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

48. The method according to claim 45, wherein, The static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

49. The method according to claim 45, wherein, The radio frequency transmitting coil includes a first ring and a second ring connected via one or more capacitors and / or one or more crossbars.

50. The method of claim 45, wherein, The radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

51. The method according to claim 45, wherein, The at least one unilateral gradient coil group is non-planar and oriented to partially surround the region of interest, and wherein the at least one gradient coil group is configured to project a magnetic field gradient into the region of interest.

52. The method according to claim 45, wherein, The at least one unilateral gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first position and the second position being opposite each other with respect to the central region of the at least one unilateral gradient coil group.

53. The method according to claim 45, wherein, The at least one single-sided gradient coil group has a rise time of less than 10 μs.

54. The method according to claim 45, wherein, The permanent magnet has a hole passing through the center of the permanent magnet.

55. The method of claim 45, further comprising: An electromagnet configured to change the static magnetic field of the permanent magnet within the region of interest.

56. The method according to claim 45, wherein, The radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging in the region of interest.

57. The method according to claim 45, wherein, The radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

58. The method according to claim 45, wherein, The radio frequency transmitting coil and the at least one single-sided gradient coil group are concentric with respect to the region of interest.

59. The method according to claim 55, wherein, The electromagnet has a magnetic field strength of 10 mT to 1 T.

60. The method of claim 45, wherein, The magnetic resonance imaging system is a unilateral magnetic resonance imaging system that includes a magnetic resonance imaging scanner or a magnetic resonance imaging spectrometer.

61. A method for performing a scan on a unilateral magnetic resonance imaging system, the method comprising: A housing is provided, the housing comprising: Front surface, A hole having an opening positioned around a central region of the front surface. Permanent magnets used to provide a static magnetic field. An RF transmitting coil, the RF transmitting coil being located on the front surface and having a central region coaxial with the aperture, and A single-sided helical gradient coil group, located on the front surface and comprising a plurality of gradient coil groups arranged around a central region of the single-sided helical gradient coil group, wherein the central region of the single-sided helical gradient coil group is coaxial with the hole. Provide electromagnets; Activate at least one of the radio frequency transmitting coil, the single-sided spiral gradient coil group, or the electromagnet to generate an electromagnetic field in a region of interest, wherein the region of interest is located outside the front surface; Activate the radio frequency receiving coil to acquire imaging data; Reconstruct the acquired imaging data to produce an output image for analysis; and The output image is displayed for user inspection and annotation.

62. The method according to claim 61, wherein, The front surface is a recessed surface.

63. The method according to claim 61, wherein, The permanent magnet has a hole passing through the center of the permanent magnet.

64. The method according to claim 61, wherein, The static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

65. The method according to claim 61, wherein, The radio frequency transmitting coil includes a first ring and a second ring connected via one or more capacitors and / or one or more crossbars.

66. The method according to claim 61, wherein, The radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

67. The method according to claim 61, wherein, The single-sided spiral gradient coil group is non-planar and oriented to partially surround the region of interest, and wherein the single-sided spiral gradient coil group is configured to project a magnetic field gradient onto the region of interest.

68. The method according to claim 61, wherein, The single-sided spiral gradient coil group includes one or more first spiral coils at a first position and one or more second spiral coils at a second position, the first position and the second position being opposite each other with respect to the central region of the single-sided spiral gradient coil group.

69. The method according to claim 61, wherein, The single-sided spiral gradient coil group has a rise time of less than 10 μs.

70. The method according to claim 61, wherein, The electromagnet is configured to change the static magnetic field of the permanent magnet within the region of interest.

71. The method according to claim 61, wherein, The electromagnet has a magnetic field strength of 10 mT to 1 T.

72. The method according to claim 61, wherein, The radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging in the region of interest.

73. The method according to claim 61, wherein, The radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

74. The method according to claim 61, wherein, The radio frequency transmitting coil and the single-sided spiral gradient coil group are concentric with respect to the region of interest.

75. A method for performing a scan on a unilateral magnetic resonance imaging system, the method comprising: A housing is provided, the housing comprising: concave in front surface, Permanent magnets used to provide a static magnetic field. RF transmitting coil, and At least one single-sided gradient coil group, The radio frequency transmitting coil and the at least one single-sided gradient coil group are positioned close to the recessed front surface; Activate at least one of the radio frequency transmitting coil and the at least one single-sided gradient coil group to generate an electromagnetic field in the region of interest, wherein the region of interest is located outside the recessed front surface; Activate the radio frequency receiving coil to acquire imaging data; Reconstruct the acquired imaging data to produce an output image for analysis; and The output image is displayed for user inspection and annotation.

76. The method according to claim 75, wherein, The radio frequency transmitting coil and the at least one single-sided gradient coil group are located on the recessed front surface.

77. The method according to claim 75, wherein, The static magnetic field of the permanent magnet is in the range of 1 mT to 1 T.

78. The method according to claim 75, wherein, The static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

79. The method according to claim 75, wherein, The radio frequency transmitting coil includes a first ring and a second ring connected via one or more capacitors and / or one or more crossbars.

80. The method according to claim 75, wherein, The radio frequency transmitting coil is non-planar and oriented to partially surround the region of interest.

81. The method according to claim 75, wherein, The at least one-sided gradient coil group is non-planar and oriented to partially surround the region of interest, and wherein the at least one-sided gradient coil group is configured to project a magnetic field gradient into the region of interest.

82. The method according to claim 75, wherein, The at least one unilateral gradient coil group includes one or more first helical coils at a first position and one or more second helical coils at a second position, the first position and the second position being opposite each other with respect to the central region of the at least one unilateral gradient coil group.

83. The method according to claim 75, wherein, The at least one single-sided gradient coil group has a rise time of less than 10 μs.

84. The method according to claim 75, wherein, The permanent magnet has a hole passing through the center of the permanent magnet.

85. The method of claim 75, further comprising: An electromagnet configured to change the static magnetic field of the permanent magnet within the region of interest.

86. The method according to claim 75, wherein, The radio frequency receiving coil is a flexible coil configured to be attached to an anatomical site of the patient for imaging in the region of interest.

87. The method according to claim 75, wherein, The radio frequency receiving coil has one of a single-loop coil configuration, a figure-eight coil configuration, or a butterfly coil configuration, wherein the coil is smaller than the region of interest.

88. The method according to claim 75, wherein, The radio frequency transmitting coil and the at least one single-sided gradient coil group are concentric with respect to the region of interest.

89. The method according to claim 85, wherein, The electromagnet has a magnetic field strength of 10 mT to 1 T.

90. The method according to claim 75, wherein, The magnetic resonance imaging system is a single-sided magnetic resonance imaging system that includes a magnetic resonance imaging scanner or a magnetic resonance imaging spectrometer.

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