OA20840A

OA20840A - Systems and methods for performing magnetic resonance imaging.

Info

Publication number: OA20840A
Application number: OA1202100382
Authority: OA
Inventors: Aleksandar NACEV; Muller Gomes; Pulkit MALIK; Hongli Dong; Dinesh Kumar; John NOLTE; Ram Narayanan; Miguel Algarín Guisado Jose; Athiveera Rama Pandian Sabareish
Original assignee: Promaxo, Inc
Priority date: 2019-02-22
Filing date: 2020-02-24
Publication date: 2023-05-29

Abstract

In accordance with various embodiments, a magnetic resonance imaging system is provided. In accordance with various embodiments, the system includes a housing having a front surface, a permanent magnet for providing a static magnetic field, a radio frequency transmit coil, and at least one gradient coil set. In accordance with various embodiments, the radio frequency transmit coil and the at least one gradient coil set are positioned proximate to the front surface. In accordance with various embodiments, the radio frequency transmit coil and the at least one gradient coil set are configured to generate an electromagnetic field in a region of interest. In accordance with various embodiments, the permanent magnet has an aperture through center of the permanent magnet. In accordance with various embodiments, the region of interest resides outside the front surface.

Description

SYSTEMS AND METHODS FOR PERFORMING MAGNETIC RESONANCE IMAGING

BACKGROUND

Magnetic résonance imagîng (MRI) Systems hâve primarily been focused on leveraging an enclosed form factor. This form factor includes surroundîng the imagîng région with electromagnetic field producing materials and imagîng System components. A typical MRI System includes a cylindrical bore magnet where the patient is placed within the tube of the magnet for imagîng. Components, such as radio frequency (RF) transmission (TX) and réception (RX) coils, gradient coîls and permanent magnet are posîtioned accordingly to produce the necessary magnetic field within the tube for imagîng the patient.

The majority of current MRI Systems thus suffer from multiple disadvantages, some examples of which are provided as follows. First, the footprint for these Systems is substantîal, often requiring that MRI Systems be housed in hospitals or extemal imagîng centers. Second, closed MRI Systems make interventions (e.g., image guided interventions such as MRI guided biopsies, treatment planning, robotic surgeries and radiation treatments) much more difficult. Third, the placement of the prîmary magnet components discussed above to virtually sunound the patient, as is the case in most current MRI Systems, severely limits the movement of the patient, often causing panic in patients situated inside the MRI System as well as additional burdens during situating or removing the patient to and from within the imagîng région. In other current MRI Systems, the patient is placed between two large plates to relieve some physical restrictions on patient placement. Regardless, a need exists to provide modem imagîng configurations in next génération MRI Systems to reduce footprint, allowing for in office MRI procedures across various régions of interest. A need also exists to provide MRI System designs that allow for various image guided interventions. Moreover, a need exists to provide MRI System designs that improve the patient expérience and ease at which a patient can be scanned.

SUMMARY

In accordance with various embodiments, a magnetic résonance imagîng System is provided. In accordance with various embodiments, the System includes a housing having a front surface, a permanent magnet for providîng a static magnetic field, a radio frequency transmit coil, and a single-sided gradient coil set. In accordance with various embodiments, the radio frequency transmit coil and the single-sided gradient coil set are positioned proxîmate to the front surface. In accordance wîth various embodiments, the System includes an electromagnet, a radio frequency receive coil, and a power source. In accordance with various embodiments, the power source is configured to flow current through at least one of the radio frequency transmit coil, the single-sided gradient coil set, or the electromagnet to generate an electromagnetic field in a région of interest. In accordance with various embodiments, the région of interest résides outside the front surface.

In accordance with various embodiments, a magnetic résonance imaging System is provided. In accordance with various embodiments, the System includes a housing having a concave front surface, a permanent magnet for providîng a static magnetic field, a radio frequency transmit coil, and at least one gradient coil set. In accordance with various embodiments, the radio frequency transmit coil and the at least one gradient coil set are positioned proximate to the concave front surface. In accordance with various embodiments, the radio frequency transmit coil and the at least one gradient coil set are configured to generate an electromagnetic field in a région of interest. In accordance with various embodiments, the région of interest résides outside the concave front surface. In accordance with various embodiments, the System includes a radio frequency receive coil for detecting signai in the région of interest.

In accordance with various embodiments, a method of performing magnetic résonance imaging is provided. The method includes inputting patient parameters into a magnetic résonance imaging System, the System comprising: a housing comprising: a front surface, a permanent magnet for providîng a static magnetic field, a radio frequency transmit coil, and a single-sided gradient coil set, wherein the radio frequency transmit coil and the single-sided gradient coil set are positioned proximate to the front surface; an electromagnet; a radio frequency receive coil; and a power source, wherein the power source is configured to flow current through at least one of the radio frequency transmit coil, the single-sided gradient coil set, or the electromagnet to generate an electromagnetic field in a région of interest, wherein the région of interest résides outside the front surface; executing a patient positioning protocol comprising running at least one first scan; running at least one second scan; reviewing the at least one second scan; and determining at least one path for conducting a bîopsy based on review of the at least one second scan.

In accordance with various embodiments, a method of performing magnetic résonance imaging is provided. The method includes inputting patient parameters into a magnetic résonance imaging System, the System comprising: a housing comprising: a concave front surface, a permanent magnet for providîng a static magnetic field, a radio frequency transmit coil, and at least one gradient coil set, wherein the radio frequency transmit coil and the at least one gradient coil set are positioned proximate to the concave front surface, wherein the radio frequency transmit coil and the at least one gradient coil set are confîgured to generate an electromagnetic fieid in a région of interest, wherein the région of interest résides outside the concave front surface; and a radio frequency receive coil for detecting signal in the région of interest; executing a patient positioning protocol comprising running at least one first scan; running at least one second scan; reviewing the at least one second scan; and determining at least one path for conducting a biopsy based on review of the at least one second scan.

In accordance with varions embodiments, a method of perfonning a scan on a magnetîc résonance imaging System is provided. The method includes providing a housing comprising: a front surface, a permanent magnet for providing a static magnetic fieid, a radio frequency transmit coil, and a single-sided gradient coil set, wherein the radio frequency transmit coil and the single-sided gradient coil set are positioned proximate to the front surface; providing an electromagnet; activating at least one of the radio frequency transmit coil, the single-sided gradient coil set, or the electromagnet to generate an electromagnetic fieid in a région of interest, wherein the région of interest résides outside the front surface; activating a radio frequency receive coil to obtain imaging data; reconstructing obtained imaging data to produce an output image for analysis; and displaying the output image for user review and annotation.

In accordance with varions embodiments, a method of perfonning a scan on a magnetic résonance imaging System is provided. The method includes providing a housing comprising: a concave front surface, a permanent magnet for providing a static magnetic fieid, a radio frequency transmit coil, and a single-sided gradient coil set, wherein the radio frequency transmit coil and the single-sided gradient coil set are positioned proximate to the front surface; activating at least one of the radio frequency transmit coil and the at least one gradient coil set to generate an electromagnetic fieid in a région of interest, wherein the région of interest résides outside the concave front surface; activating a radio frequency receive coil to obtain imaging data; reconstructing obtained imaging data to produce an output image for analysis; and displaying the output image for user review and annotation.

These and other aspects and implémentations are discussed in detail herein. The foregoing information and the following detailed description include illustrative examples of various aspects and implémentations, and provide an overview or Framework for understandîng the nature and character of the claimed aspects and implémentations. The drawings provide illustration and a further understandîng of the various aspects and implémentations, and are incorporated in and constitute a part of this spécification.

BR1EF DESCRIPTION OF THE DRAWINGS

The accompanying drawings are not intended to be drawn to scale. Like référencé numbers and désignations in the varions drawings indicate like éléments. For purposes of clarity, not every component may be labeled in every drawing. In the drawings :

Figure 1 is a schematic illustration of a magnetic résonance imaging system, in accordance with varions embodiments.

Figure 2A is a schematic illustration of a magnetic résonance imaging system, in accordance with varions embodiments.

Figure 2B illustrâtes an exploded view of the magnetic résonance imaging system shown in Figure 2A.

Figure 2C is a schematic front view of the magnetic résonance imaging system shown in Figure 2A, in accordance with varions embodiments.

Figure 2D is a schematic side view of the magnetic résonance imaging system shown in Figure 2A, in accordance with varions embodiments.

Figure 3 is a schematic view of an implémentation of a magnetic imaging apparatus, according to varions embodiments.

Figure 4 is a schematic view of an implémentation of a magnetic imaging apparatus, according to varions embodiments.

Figure 5 îs a schematic front view of a magnetic résonance imaging System 500, according to varions embodiments.

Figure 6A îs an example schematic illustration of a radio frequency receive coil (RF-RX) array including indîvidual coil éléments, in accordance with varions embodiments.

Figure 6B îs an example illustration of a loop coil along with example calculations for a loop coil magnetic field, in accordance with varions embodiments.

Figure 6C is an example X-Y chart illustrating the magnetic field as a function of radius of a loop coil, in accordance with varions embodiments disclosed herein.

Figure 6D is a cross-sectional illustration of a portion of the human body, namely in the area of the prostate.

Figure 7 is a flowchart for a method of performing magnetic résonance imaging, according to varions embodiments.

Figure S is a flowchart for another method of performing magnetic résonance îmagîng, according to various embodiments.

Figure 9 is a flowchart for a method of performing a scan on a magnetic résonance imaging system, according to various embodiments.

Figure 10 is a flowchart for another method of perfonning a scan on a magnetic résonance imagîng System, according to various embodiments.

Figures 11 A-l IX illustrate various positions of patient depending on the type of anatomical scan for imaging in a magnetic résonance imaging System, according to various embodiments.

It is to be understood that the figures are not necessarîly drawn to scale, nor are the objects in the figures necessarîly drawn to scale in relationship to one another. The figures are depictions that are intended to bring clarity and understanding to various embodiments of apparatuses, Systems, and methods disclosed herein. Wherever possible, the same reference numbers will be used throughout the drawings to refer to the same or like parts. Moreover, it should be appreciated that the drawings are not intended to limit the scope ofthe présent teachings in any way.

DETAILED DESCRIPTION

The following description of various embodiments is exemplary and explanatory only and is not to be construed as limiting or restrictive in any way. Other embodiments, features, objects, and advantages of the présent teachings will be apparent from the description and accompanying drawings, and from the daims.

It should be understood that any use of subheadings herein are for organizational purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in all the various embodiments discussed herein and that all features described herein can be used in any contemplated combination, regardless ofthe spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

Unless defined otherwise, all technical and scientific ternis used herein hâve the same meanîng as commonly understood by one of ordinary skill in the art to which there various embodiments belong.

All publications mentioned herein are incorporated herein by reference for the purpose of describing and disclosing devices, compositions, formulations and méthodologies which are described in the publication and which might be used in connection with the présent disclosure.

As used herein, the tenus comprise, comprises, comprising, contain, contains, containing, hâve, having include, includes, and including and their variants are not intended to be limiting, are inclusive or open-ended and do not exclude additional, unrecited addîtîves, components, integers, éléments or method steps. For example, a process, method, System, composition, kit, or apparatus that comprises a list of features is not necessarily limited only to those features but may include other features not expressly listed or inhérent to such process, method, System, composition, kit, or apparatus.

As dîscussed herein, and in accordance with varions embodiments, the varions Systems, and varions combinations of features that make up the varions System embodiments, can include a magnetic résonance imaging System. In accordance with varions embodiments, the magnetic résonance imaging System is a single-sided magnetic résonance imaging System that comprises a magnetic résonance imaging scanner or a magnetic résonance imaging spectrometer. In accordance with varions embodiments, the magnetic résonance imaging System can include a magnet assembly for providing a magnetic field requîred for imaging an anatomical portion of a patient. In accordance with varions embodiments, the magnetic résonance imaging System can be configured for imaging in a région of interest which résides outside of the magnet assembly.

Typical magnet résonant assemblies used in modem magnetic résonance imaging Systems include, for example, a birdcage coil configuration. A typical birdcage configuration includes, for example, a radio frequency transmission coil that can include two large rings placed on opposite sides of the imaging région (i.e., the région of interest where the patient résides) that are each electrically connected b y one or more rangs. Since the imaging signal improves the more the coil surrounds the patient, the birdcage coil is typically configured to encompass a patient so that the signal produced from within the imaging région, i.e., the région of interest where the anatomical target portion of the patient résides, is sufficiently unifonn. To improve patient comfort and reduce burdensome moveinent limitations of the current magnetic résonance imaging Systems, the disclosure as described herein generally relates to a magnetic résonance imaging System that includes a single-sided magnetic résonance imaging System and its applications.

As described herein, the disclosed single-sided magnetic résonance imaging System can be configured to image the patient from one side whîle providing access to the patient from both sides. This is possible due to the single-sided magnetic résonance imaging System that contains an access aperture (also referred to herein as “aperture”, “hole” or “bore”), which is configured to project magnetic fields in the région of interest which résides completely outside of the magnet assembly and the magnetic résonance imaging System. Since not being completely surrounded by the electromagnetic field producîng materials and imaging System components as in current State of the art Systems, the novei single-sided configuration as described herein offer less restriction in patient movement whîle reducing unnecessary burden during situating and/or removing of the patient from the magnetic résonance imaging System. In accordance with varions embodiments as described herein, the patient would not feel entrapped in the disclosed magnetic résonance imaging System with the placement of the magnet assembly on the side of the patient during imaging. The configuration that enables single-sided or imaging from a side is made possible by the disclosed System components as discussed herein.

In accordance with varions embodiments, the varions Systems, and varions combinations of features that make up the varions System components and embodiments of the disclosed magnetic résonance imaging System are disclosed herein.

In accordance with varions embodiments, a magnetic résonance imaging System is disclosed herein. In accordance with varions embodiments, the System includes a housing having a front surface, a permanent magnet for provîding a static magnetic fieid, an access aperture (also referred to herein as “aperture”, “hole” or “bore”) within the permanent magnet assembly, a radio frequency transmit coil, and a single-sided gradient coil set. In accordance with varions embodiments, the radio frequency transmit coil and the single-sided gradient coil set are positioned proximate to the front surface. In accordance with varions embodiments, the System includes an electromagnet, a radio frequency receive coil, and a power source. In accordance with various embodiments, the power source is configured to flow current through at least one of the radio frequency transmit coil, the single-sided gradient coil set, or the electromagnet to generate an electromagnetic fieid in a région of interest. In accordance with various embodiments, the région of interest résides outside the front surface.

In accordance with various embodiments, the radio frequency transmit coil and the singlesided gradient coil set are located on the front surface. In accordance with various embodiments, the front surface is a concave surface. In accordance with various embodiments, the permanent magnet has an aperture through center of the permanent magnet. In accordance with various embodiments, the static magnetic fieid of the permanent magnet ranges from I mT to I T. In accordance with various embodiments, the static magnetic fieid of the permanent magnet ranges from 10 mT to 195 mT.

In accordance with various embodiments, the radio frequency transmit coil includes a first ring and a second ring that are connected via one or more capacitors and/or one or more rangs. In accordance with various embodiments, the radio frequency transmit coil is non-planar and oriented to partial 1 y surround the région of interest. In accordance with various embodiments, the single-sided gradient coil set is non-planar and oriented to partially surround the région of interest. In accordance with various embodiments, the single-sided gradient coil set is configured to project a magnetic fieid gradient to the région of interest. In accordance with various embodiments, the single-sided gradient coil set 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 located opposite each other about a center région of the single-sided gradient coil set. In accordance with various embodiments, the single-sided gradient coil set has a rise time less than 10 ps.

In accordance with various embodiments, the electromagnet is configured to alter the statîc magnetic field of the permanent magnet within the région of interest. In accordance with various embodiments, the electromagnet has a magnetic field strength from 10 mT to 1 T. In accordance with various embodiments, the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest. In accordance with various embodiments, the radio frequency receive coil is in one of a single-loop coil configuration, figure-8 coil configuration, or butterfiy coil configuration, wherein the coil is smaller than the région of interest. In accordance with various embodiments, the radio frequency transmit coil and the single-sided gradient coil set are concentric about the région of interest. In accordance with various embodiments, the magnetic résonance imaging System is a single-sided magnetic résonance imaging System that comprises a bore having an opening positioned about a center région of the front surface.

In accordance with various embodiments, a magnetic résonance imaging System is disciosed herein. In accordance with various embodiments, the system includes a housing having a concave front surface, a permanent magnet for providing a statîc magnetic field, a radio frequency transmit coil, and at least one gradient coil set. In accordance with various embodiments, the radio frequency transmit coil and the at least one gradient coil set are positioned proximate to the concave front surface. In accordance with various embodiments, the radio frequency transmit coil and the at least one gradient coil set are configured to generate an electromagnetic field in a région of interest. In accordance with various embodiments, the région of interest résides outside the concave front surface. In accordance with various embodiments, the System includes a radio frequency receive coil for detecting signal in the région of interest.

In accordance with various embodiments, the radio frequency transmit coil and the singlesided gradient cod set are located on the concave front surface. In accordance with various embodiments, the statîc magnetic field of the permanent magnet ranges from I mT to 1 T. In accordance with various embodiments, the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT. In accordance with various embodiments, the radio frequency transmit coil comprises a first ring and a second ring that are connected via one or more capacitors and/or one or more rungs. In accordance with varions embodiments, the radio frequency transmit coi H s non-planar and oriented to partially surround the région of interest. In accordance with varions embodiments, the at least one gradient coil set is non-planar, sîngle-sided, and oriented to partially surround the région of interest. In accordance with varions embodiments, the at least one gradient coil set is configured to project magnetic field gradient in the région of interest.

In accordance with varions embodiments, the at least one gradient coil set comprises 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 located opposite each other about a center région of the at least one gradient coil set. In accordance with varions embodiments, the at least one gradient coil set has a rise time less than 10 gs. In accordance with varions embodiments, the permanent magnet has an aperture through center of the permanent magnet In accordance with varions embodiments, the system further includes an electromagnet configured to alter the static magnetic field of the permanent magnet within the région of interest. In accordance with varions embodiments, the electromagnet has a magnetic field strength from 10 mT to 1 T. In accordance with varions embodiments, the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest. In accordance with varions embodiments, the radio frequency receive coil is in one of a single-loop coil configuration, figure-8 coil configuration, or butterfly coil configuration, where the coil is smaller than the région of interest.

In accordance with varions embodiments, the radio frequency transmit coil and the at least one gradient coil set are concentric about the région of interest. In accordance with varions embodiments, the magnetic résonance imaging system is a single-sided magnetic résonance imaging system that comprises a magnetic résonance imaging scanner or a magnetic résonance imaging spectrometer.

Figure 1 is a schematic illustration of a magnetic résonance imaging System 100, in accordance with various embodiments. The system 100 includes a housing 120. As shown in Figure 1, the housing 120 includes a permanent magnet 130, a radio frequency transmit coil 140, a gradient coil set 150, an optional electromagnet 160, a radio frequency receive coil 170, and a power source 180. In accordance with various embodiments, the system 100 can include various electronic components, such as for example, but not limited to a varactor, a PIN diode, a capacitor, or a switch, including a micro-electro-mechanical System (MEMS) switch, a solid State relay, or a mechanical relay. In accordance with various embodiments, the various electronic components listed above can be configured with the radio frequency transmit coil 140.

Figure 2A is a schematic illustration of a magnetic résonance imaging System 200, in accordance with varions embodiments. Figure 2B illustrâtes an exploded view of the magnetic résonance imaging System 200. Figure 2C is a schematic front view of the magnetic résonance imaging System 200, in accordance with various embodiments. Figure 2D is a schematic side view of the magnetic résonance imaging System 200, in accordance with various embodiments. As shown in Figures 2A and 2B, the magnetic résonance imaging System 200 includes a housing 220. The housing 220 includes a front surface 225. In accordance with various embodiments, the front surface 225 can be a concave front surface. In accordance with various embodiments, the front surface 225 can be a recessed front surface.

As shown in Figures 2A and 2B, the housing 220 includes a permanent magnet 230, a radio frequency transmit coil 240, a gradient coil set 250, an optional electromagnet 260, and a radio frequency receive coil 270. As shown in Figures 2C and 2D, the permanent magnet 230 can include a plurality of magnets disposed in an array configuration. The plural ity of magnets of the permanent magnet 230 are illustrated to cover an entire surface as shown in the front view of Figure 2C and illustrated as bars in a horizontal direction as shown in the side view of Figure 2D. As shown in Figure 2A, the main permanent magnet might include an access aperture 235 for accessing the patient from multiple sides of the System.

It should be understood that any use of subheadings herein are for organizationai purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

PERMANENT MAGNET

As discussed herein, and in accordance with various embodiments, the various Systems, and various combinations of features that make up the various System embodiments, can include a permanent magnet.

In accordance with various embodiments, the permanent magnet 230 provides a static magnetic field in a région of interest 290 (also referred to herein as “given field of view”). In accordance with various embodiments, the permanent magnet 230 can include a plurality of cylindrical permanent magnets in parallel configuration as shown in Figures 2C and 2D. In accordance with various embodiments, the permanent magnet 230 can include any suitable 10 magnetic materials, including but not limited, to rare-earth based magnetic materials, such as for example, Nd-based magnetic materials, and the like. As shown in Figure 2A, the main permanent magnet might include an access aperture 235 for accessîng the patient from multiple sides of the system.

In accordance with varions embodiments, the static magnetic field of the permanent magnet 230 may 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 to a given field of view. The magnetic field may 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. In accordance with varions embodiments, the static magnetic field of the permanent magnet 230 may 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.

In accordance with varions embodiments, the permanent magnet 230 can include a bore 235 in its center. In accordance with varions embodiments, the permanent magnet 230 may not include a bore. In accordance with varions embodiments, the bore 235 can hâve a diameter between 1 inch and 20 inches. In accordance with varions embodiments, the bore 235 can hâve a diameter between 1 inch and 4 inches, between 4 inches and 8 inches, and between 10 inches and 20 inches. In accordance with varions embodiments, the given field of view can be a spherical or cylindrical field of view, as shown in Figures 2A and 2B. In accordance with varions embodiments, the spherical field of view can be between 2 inches and 20 inches in diameter. In accordance with varions embodiments, the spherical field of view can hâve a diameter between 1 inch and 4 inches, between 4 inches and 8 inches, and between 10 inches and 20 inches. In accordance with varions embodiments, the cylindrical field of view is approximately between 2 inches and 20 inches in length. In accordance with varions embodiments, the cylindrical field of view can hâve a length between 1 inch and 4 inches, between 4 inches and 8 inches, and between 10 inches and 20 inches.

It should be understood that any use of subheadings herein are for organizational purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informatîonal purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

RADIO FREQUENCY TRANSMIT COIL

As discussed herein, and in accordance with various embodiments, the various Systems, and various combinations of features that make up the various System embodiments, can also include a radio frequency transmit coil.

Figure 3 is a schematic view of an implémentation of a magnetîc imaging apparatus 300, according to various embodiments. As shown in Figure 3, the apparatus 300 includes a radio frequency transmit coil 320 that projects the RF power outwards away from the coil 320. The coil 320 has two rings 322 and 324 that are connected by one or more rungs 326. As shown in Figure 3, the coil 320 is also connected to a power source 350a and/or a power source 350b (collectively referred to herein as “power source 350”). In accordance with various embodiments, power sources 350a and 350b can be configured for power input and/or signal input, and can generally be referred to as coil input. In accordance with various embodiments, the power source 350a and/or 350b are configured to provide contact via electrîcal contacts 352a and/or 352b (collectively referred to herein as “electrîcal contact 352”), and electrîcal contacts 354a and/or 354b (collectively referred to herein as “electrîcal contact 354b”) by attaching the electrîcal contacts 352 and 354 to one or more rungs 326. The coil 320 is configured to project a uniform RF field withîn a field of view 340. In accordance with various embodiments, the field of view 340 is a région of interest for magnetîc résonance imaging (i.e., imaging région) where a patient résides. Since the patient résides in the field of view 340 away from the coil 320, the apparatus 300 is suitable for use in a single-sided magnetîc résonance imaging System. In accordance with various embodiments, the coil 320 can be powered by two signais that are 90 degrees out of phase from each other, for example, via quadrature excitation.

In accordance with various embodiments, the coil 320 includes the ring 322 and the ring 324 that are positioned co-axially along the same axis but at a distance away from each other, as 12 shown in Figure 3. In accordance with various embodiments, the ring 322 and the ring 324 are separated by a distance ranging from about 0.1 m to about 10 m. In accordance with various embodiments, the ring 322 and the ring 324 are separated by a distance ranging from about 0.2 m to about 5 m, about 0.3 m to about 2 m, about 0.2 m to about 1 m, about 0.1 m to about 0.8 m, or about 0.1 m to about 1 m, inclusive of any séparation distance therebetween. In accordance with various embodiments, the coi) 320 includes the ring 322 and the ring 324 that are positioned nonco-axial ly but along the same direction and separated at a distance ranging from about 0.2 ni to about 5m. In accordance with various embodiments, the ring 322 and the ring 324 can also be tilted with respect to each other. In accordance with various embodiments, the tilt angle can be from 1 degree to 90 degrees, from I 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.

In accordance with various embodiments, the ring 322 and the ring 324 hâve the same diameter. In accordance with varions embodiments, the ring 322 and the ring 324 hâve different diameters and the ring 322 has a larger diameter than the ring 324, as shown in Figure 3. In accordance with various embodiments, the ring 322 and the ring 324 hâve different diameters and the ring 322 has a smaller diameter than the ring 324. In accordance with various embodiments, the ring 322 and the ring 324 of the coil 320 are configured to create the imaging région in the field of view 340 containing a uniform RF power profile within the field of view 340, a field of view that is not centered within the RF-TX coil and is instead projected outwards in space from the coil itself.

In accordance with various embodiments, the ring 322 has a diameter between about 10 pm and about 10 m. In accordance with various embodiments, the ring 322 has a diameter between about 0.001 m and about 9 m, between about 0.01 m and about 8 m, between about 0.03 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, inclusive of any diameter therebetween.

In accordance with various embodiments, the ring 324 has a diameter between about 10 pm and about 10 m. In accordance with various embodiments, the ring 324 has a diameter between about 0.001 m and about 9 m, between about 0.01 m and about 8 m, between about 0.03 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, inclusive of any diameter therebetween.

In accordance with various embodiments, the ring 322 and the ring 324 are connected by one or more rungs 326, as shown in Figure 3. In accordance with various embodiments, the one or more rungs 326 are connected to the ring 322 and 324 so as to form a single electrical circuit loop (or single current loop). As shown in Figure 3, for example, one end ofthe one or more rungs 326 is connected to the electrical contact 352 of the power source 350 and another end of the one or more rungs 326 be connected to the electrical contact 354 so that the coil 320 complétés an electrical circuit.

In accordance with various embodiments, the ring 322 is a discontinuons ring and the electrical contact 352 and the electrical contact 354 canbe electrically connected to two opposite ends ofthe ring 322 to form an electrical circuit powered by the power source 350. Similarly, in accordance with various embodiments, the ring 324 is a discontinuons ring and the electrical contact 352 and the electrical contact 354 can be electrically connected to two opposite ends of the ring 324 to form an electrical circuit powered by the power source 350.

In accordance with various embodiments, the rings 322 and 324 are not circular and can instead hâve a cross section that is elliptical, square, rectangular, or trapézoïdal, or any shape or form having a closed loop. In accordance with various embodiments, the rings 322 and 324 may hâve cross sections that vary in two different axial planes with the primary axis being a circle and the secondary axis having a sinusoïdal shape or some other géométrie shape. In accordance with various embodiments, the coil 320 may include more than two rings 322 and 324, each connected by rungs that span and connect ail the rings. In accordance with various embodiments, the coil 320 may include more than two rings 322 and 324, each connected by rungs that alternate connection points between rings. In accordance with various embodiments, the ring 322 may contain a physical aperture for access. In accordance with various embodiments, the ring 322 may be a solid sheet wîthout a physical aperture.

In accordance with various embodiments, the coil 320 generates an electromagnetic field (also referred to herein as “magnetic field”) strength between about 1 μΤ and about 10 mT. In accordance with various embodiments, the coil 320 can generate a magnetic field strength between about 10 μΤ and about 5 mT, about 50 μΤ and about 1 mT, or about 100 μΤ and about 1 mT, inclusive of any magnetic field strength therebetween.

In accordance with various embodiments, the coil 320 generates an electromagnetic field that is pulsed at a radio frequency between about 1 kHz and about 2 GHz. In accordance with various embodiments, the coil 320 generates a magnetic field that is pulsed at a radio frequency between about 1 kHz and about 1 GHz, 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, inclusive of any frequencies therebetween.

In accordance with various embodiments, the coil 320 is oriented to partially surround the région of interest. In accordance with various embodiments, the ring 322, the ring 324, and the one or more rungs 326 are non-planar to each other. Said another way, the ring 322, the ring 324, and the one or more rungs 326 form a three-dimensional structure that surrounds the région of interest where a patient résides. In accordance with various embodiments, the ring 322 is doser to the région of interest than the ring 324, as shown in Figure 3. In accordance with various embodiments, the région of interest has a size of about 0.1 m to about 1 m. In accordance with various embodiments, the région of interest îs smailer than the diameter of the ring 322. In accordance with various embodiments, the région of interest is smailer than both the diameter of the ring 324 and the diameter of the ring 322, as shown in Figure 3. In accordance with various embodiments, the région of interest has a size that is smailer than the diameter of the ring 322 and larger than the diameter of the ring 324.

In accordance with various embodiments, the ring 322, the ring 324, or the rungs 326 include the same material. In accordance with various embodiments, the ring 322, the ring 324, or the rungs 326 include different materials. In accordance with various embodiments, the ring 322, the ring 324, or the rungs 326 include hollow tubes or solid tubes. In accordance with various embodiments, the hollow tubes or solid tubes can be configured for air or fluid cooling. In accordance with various embodiments, each of the ring 322 or the ring 324 or the rungs 326 includes one or more electrically conductive windings. In accordance with various embodiments, the windings include litz wires or any electrical conducting wires. These additional windings could be used to improve performance by lowering the résistance of the windings at the desired frequency. in accordance with various embodiments, the ring 322, the ring 324, or the rungs 326 include copper, aluminum, silver, silver paste, or any high electrical conducting material, including métal, alloys or superconducting métal, alloys or non-métal. In accordance with various embodiments, the ring 322, the ring 324, or the rungs 326 may include metamaterials.

In accordance with various embodiments, the ring 322, the ring 324, or the rungs 326 may contain separate electrically non-conductive thermal control channels designed to maintain the température of the structure to a specified setting. In accordance with various embodiments, the thermal control channels can be made from electrically conductive materials and integrated as to carry the electrical current.

In accordance with various embodiments, the coil 320 includes one or more electronic components for tuning the magnetic field. The one or more electronic components can include a varactor, a PIN diode, a capacitor, or a switch, including a micro-electromechanîcal system (MEMS) switch, a solid State relay, or a mechanical relay. In accordance with various embodiments, the coil can be configured to include any of the one or more electronic components along the electrical circuit. In accordance with various embodiments, the one or more components can include mu metals, dielectrics, magnetic, or metallic components not actively conducting electricity and can tune the coil. In accordance with various embodiments, the one or more electronic components used for tuning includes at least one of dielectrics, conductîve metals, metamaterials, or magnetic metals. In accordance with various embodiments, tuning the electromagnetic field includes changing the current or by changing physical locations of the one or more electronic components. In accordance with various embodiments, the coil is cryogenically cooled to reduce résistance and improve efficiency. In accordance with various embodiments, the first ring and the second ring comprise a plurality of wîndings or lîtz wires.

In accordance with various embodiments, the coil 320 is configured for a magnetic résonance imaging system that has a magnetic field gradient across the field of view. The field gradient allows for imaging slices of the field of view without using an additional electromagnetic gradient. As disciosed herein, the coil can be configured to generate a large bandwidth by combining multiple center frequencies, each with their own bandwidth. By superimposing these multiple center frequencies with their respective bandwidths, the coil 320 can effectively generate a large bandwidth over a desired frequency range between about 1 kHz and about 2 GHz. In accordance with various embodiments, the coil 320 générâtes a magnetic field that is pulsed at a radio frequency 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, inclusive of any frequencies therebetween.

GRADIENT COIL SET

As discussed herein, and in accordance with various embodiments, the various Systems, and various combinations of features that make up the various System embodiments, can also include a gradient coil set.

Figure 4 is a schematic view of an implémentation of a magnetic imagîng apparatus 400, according to various embodiments. As shown in Figure 4, the apparatus 400 includes a gradient coil set 420 (also referred to herein as single-sided gradient coil set 420) that is configured to project a gradient magnetic field outwards away from the coil set 420 and within a field of view 430. In accordance with various embodiments, the field of view 430 is a région of interest for magnetic résonance imagîng (Le., imagîng région) where a patient résides. Since the patient résides in the field of view 430 away from the coil set 420, the apparatus 400 is suitable for use in a single-sided MRI System.

As shown in the figure, the coil set 420 includes variously sized spiral coils in various sets of spiral coils 440a, 440b, 440c, and 440d (collectively referred to as “spiral coils 440”). Each set of the spiral coils 440 include at least one spiral coil and Figure 4 is shown to include 3 spiral coils. In accordance with various embodiments, each spiral coil în the spiral coils 440 has an electrical contact at its center and an electrical contact output on the outer edge of the spiral coil so as to form a single running loop of electrically conducting material spiraling out from the center to the outer edge, or vice versa. In accordance wîth various embodiments, each spiral coil in the spiral coils 440 has a first electrical contact at a first position of the spiral coil and a second electrical contact at a second position the spiral coil so as to form a single running loop of electrically conducting material from the first position to the second position, or vice versa.

As shown in Figure 4, the coil set 420 also includes an aperture 425 at its center where the spiral coils 440 are disposed around the aperture 425. The aperture 425 itself does not contaîn any coil material within it for generating magnetic material. The coil set 420 also includes an opening 427 on the outer edge of the coil set 420 to which the spiral coils 440 can be disposed. Said another way, the aperture 425 and the opening 427 define the boundaries of the coil set 420 within which the spiral coils 440 can be disposed. In accordance with various embodiments, the coil set 420 forms a bowl shape with a hole in the center.

In accordance with various embodiments, the spiral coils 440 form across the aperture 425. For example, the spiral coils 440a are disposed across from the spiral coils 440c wîth respect to the aperture 425. Similarly, the spiral coils 440b are disposed across from the spiral coils 440d with respect to the aperture 425. In accordance with various embodiments, the spiral coils 440 în the coil set 420 shown in Figure 4 are confîgured to create spatial encoding in the magnetic gradient fieid within the fieid of view 430.

As shown in Figure 4, the coil set 420 is also connected to a power source 450 via electrical contacts 452 and 454 by attaching the electrical contacts 452 and 454 to one or more of the spiral coils 440. In accordance with various embodiments, the electrical contact 452 is connected to one of the spiral coils 440, which is then connected to other spiral coils 440 in sériés and/or in parallel, and one other spiral coil 440 is then connected to the electrical contact 454 so as to form an electrical entrent loop. In accordance with various embodiments, the spiral coils 440 are ail electrically connected in sériés. In accordance with various embodiments, the spiral coils 440 are ail electrically connected in parallel. In accordance with various embodiments, some of the spiral coils 440 are electrically connected in sériés while other spiral coils 440 are electrically connected in parallel. In accordance with various embodiments, the spiral coils 440a are electrically connected in sériés while the spiral coils 440b are electrically connected in parallel. In accordance with various embodiments, the spiral coils 440c are electrically connected in sériés while the spiral coils 440d are electrically connected in parallel. The electrical connections between each spiral coil in the spiral coils 440 or each set of spiral coils 440 can be confîgured as needed to generate the magnetic fieid in the fieid of view 430.

In accordance with various embodiments, the coil set 420 includes the spiral coils 440 spread out as shown in Figure 4. In accordance with various embodiments, each of the sets of spiral coils 440a, 440b, 440c, and 440d are confîgured în a line from the aperture 425 to the opening 427 so that each set of spiral coils is set apart from another by an angle of 90°. In accordance with various embodiments, 440a and 440b are set at 45° from one another, and 440c and 440d are set at 45° from one another, while 440c is set 135° on the other side of 440b and 440d is set 135° on the other side of 440a. In essence, any of the sets of spiral coils 440 can be confîgured in any arrangement for any number “n” of sets of spiral coils 440.

In accordance with various embodiments, the spiral coils 440 hâve the same diameter. In accordance with various embodiments, each of the sets of spiral coils 440a, 440b, 440c, and 440d hâve the same diameter. In accordance with various embodiments, the spiral coils 440 hâve different diameters. In accordance with various embodiments, each of the sets of spiral coils 440a, 440b, 440c, and 440d hâve different diameters. In accordance with various embodiments, the spiral coils in each of the sets of spiral coils 440a, 440b, 440c, and 440d hâve different diameters. In accordance with various embodiments, 440a and 440b hâve the same first diameter and 440c and 440d hâve the same second diameter, but the first diameter and the second diameter are not the same.

In accordance with various embodiments, each spiral coil in the spiral coils 440 has a diameter between about 10 pm and about 10 m. In accordance with various embodiments, each spiral coil in the spiral coils 440 has a diameter 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 ni, between about 0.5 m and about 1 m, or between about 0.01 m and about 3 m, inclusive of any diameter therebetween.

In accordance with various embodiments, the spiral coils 440 are connected to form a single electrical circuit loop (or single current loop). As shown in Figure 4, for example, one spiral coil in the spiral coils 440 is connected to the electrical contact 452 of the power source 450 and another spiral coil be connected to the electrical contact 454 so that the spiral coils 440 complétés an electrical circuit.

In accordance with various embodiments, the coil set 420 generates an electromagnetic fieid strength (also referred to herein as “electromagnetic fieid gradient” or “gradient magnetic fieid”) between about 1 pT and about 10 T. In accordance with various embodiments, the coil set 420 can generate an electromagnetic fieid strength between about 100 pT and about 1 T, about 1 mT and about 500 mT, or about 10 mT and about 100 mT, inclusive of any magnetic fieid strength therebetween. In accordance with various embodiments, the coil set 420 can generate an electromagnetic fieid strength greater than about 1 pT, about 10 μΤ, about 100 pT, about 1 mT, about 5 mT, about 10 mT, about 20 mT, about 50 mT, about 100 mT, or about 500 mT.

In accordance with various embodiments, the coil set 420 generates an electromagnetic fieid that is pulsed at a rate with a rise-time less than about 100 ps. In accordance with various embodiments, the coil set 420 generates an electromagnetic fieid that is pulsed at a rate with a rise-time less than about 1 ps, about 5 ps, about 10 ps, about 20 ps, about 30 ps, about 40 ps, about 50 ps, about 100 ps, about 200 ps, about 500 ps, about 1 ms, about 2 ms, about 5 ms, or about 10 ms.

In accordance with various embodiments, the coil set 420 is oriented to partîally surround the région of interest in the fieid of view 430. In accordance with various embodiments, the spiral coils 440 are non-planar to each other. In accordance with various embodiments, the sets of spiral coils 440a, 440b, 440c, and 440d are non-planar to each other. Said another way, the spiral coils 440 and each of the sets of spiral coils 440a, 440b, 440c, and

440d form a three-dimensional structure that surrounds the région of interest in the field of view 430 where a patient résides.

In accordance with various embodiments, the spiral coils 440 include the same material. In accordance with various embodiments, the spiral coils 440 include different materials. In accordance with various embodiments, the spiral coils in set 440a include the same fïrst material, the spiral coils in set 440b include the same second material, the spiral coils in set 440c include the same third material, the spiral coils in set 440d include the same fourth material, but the fïrst, second, third and fourth materials are different materials. In accordance with various embodiments, the fïrst and second materials are the same material, but that same material is different from the third and fourth materials, which are the same. In essence, any of the spiral coils 440 can be of the same material or different materials depending on the configuration of the coil set 420.

In accordance with various embodiments, the spiral coils 440 include hollow tubes or solid tubes. In accordance with various embodiments, the spiral coils 440 include one or more windings. In accordance with various embodiments, the windings include litz wîres or any electrical conducting wîres. In accordance with various embodiments, the spiral coils 440 include copper, aluminum, silver, silver paste, or any high electrical conducting material, încluding métal, alloys or superconducting métal, alloys or non-metal. In accordance with various embodiments, the spiral coils 440 include metamaterials.

In accordance with various embodiments, the coil set 420 includes one or more electronic components for tuning the magnetic field. The one or more electronic components can include a PIN diode, a mechanical relay, a solid State relay, or a switch, încluding a microelectro-mechanical System (MEMS) switch. In accordance with various embodiments, the coil can be configured to include any of the one or more electronic components along the electrical circuit. In accordance with various embodiments, the one or more components can include mu metals, dielectrics, magnetic, or metallic components not actively conducting electricity and can tune the coil. In accordance with various embodiments, the one or more electronic components used for tuning includes at least one of conductive metals, metamaterials, or magnetic metals. In accordance with various embodiments, tuning the electromagnetic field includes changing the current or by changing physical locations of the one or more electronic components. In some implémentations, the coil is cryogenically cooled to reduce résistance and improve efficiency.

It should be understood that any use of subheadings herein are for organizational purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in all the various embodiments discussed herein and that all features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largeiy for informational purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

ELECTROMAGNET

As discussed herein, and in accordance with various embodiments, the various Systems, and various combinations of features that make up the various System embodiments, can also include an electromagnet.

Figure 5 is a schematic front view of a magnetic résonance imaging System 500, according to various embodiments. In accordance with various embodiments, the System 500 can be any magnetic résonance imaging System, including for example, a sîngle-sided magnetic résonance imaging System that comprises a magnetic résonance imaging scanner or a magnetic résonance imaging spectrometer, as disclosed herein.

As shown in Figure 5, the System 500 includes a housing 520 that can house various components, including, for example but not limited to, magnets, electromagnets, coils for producing radio frequency fields, various electronic components, for example but not limited to, for contrelling, powering, and/or monitoring of the System 500. In accordance with various embodiments, the housing 520 can house, for example, the permanent magnet 230, the radio frequency transmît coil 240, and/or the gradient coil set 250 within the housing 520. In accordance with various embodiments, the System 500 also includes a bore 535 in îts center. As shown in Figure 5, the housing 520 also includes a front surface 525 of the System 500. In accordance with various embodiments, the front surface 525 can be curved, fiat, concave, convex, or otherwise hâve a straight or curvilinear surface. In accordance with various embodiments, the magnetic résonance imaging System 500 can be configured to provide a région of interest in field of view 530.

As shown in Figure 5, the System 500 includes an electromagnet 560 disposed proximate to the front surface 525 of the System 500. In accordance with various embodiments, the electromagnet 560 is disposed proximate to the center of the front surface 525 on the front side of the System 500. In accordance with various embodiments, the electromagnet 560 can be a solenoid coil configured to create a field that either adds or subtracts from the magnetic field, for example, of the permanent magnet 230. In accordance with various embodiments, this field can create a prepolarizing field for enhancing ihe signal or contrast from the nuclear magnetic résonance.

As shown in Figure 5, the given field of view 530 résides at the center of the front surface 525 of the System 500. In accordance with various embodiments, the electromagnet 560 is disposed within the given field of view 530. In accordance with various embodiments, the electromagnet 560 is disposed concentrically with the given field of view 530. In accordance with various embodiments, the electromagnet 560 can be inserted in the bore 535. In accordance with various embodiments, the electromagnet 560 can be placed proximate to the bore 535. For example, the electromagnet 560 can be placed in front, back or middle of the bore 535. In accordance with various embodiments, the electromagnet 560 can be placed proximate to, or at the entrance of the bore 535.

It should be understood that any use of subheadings herein are for organizational purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for inforrnational purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

RADIO FREQUENCY RECEIVE COIL

As discussed herein, and in accordance with various embodiments, the various Systems, and various combinations of features that make up the various System embodiments, can also include a radio frequency receive coil.

Typical MR Systems create a uniform field within the imaging région. This uniform field then generates a narrow band of magnetic résonance frequencies that can then be captured by a receive coil, amplîfied, and digitized by a spectrometer. Since frequencies are within a narrow well-defined bandwidth, hardware architecture is focused on creating a statically tuned RF-RX coil with an optimal coil quality factor. Many variations in coil architectures hâve been created that explore large single volume coils, coil arrays, parallelized coil arrays, or body spécifie coil arrays. However, these structures are ail predicated on imaging a spécifie frequency close to the région of interest at high field strengths and small as possible within a magnetic bore.

In accordance with various embodiments, an MRI System is provided that can include a unique imaging région that can be offset from the face of a magnet and therefore unobstructed as compared to traditional scanners. In addition, this form factor can hâve a built-in magnetic field gradient that créâtes a range of field values over the région of interest. Lastly, this system can operate at a lower magnetic field strength as compared to typîcal MRI Systems allowing for a relaxation on the RX coil design constraints and allowing for additional mechanisms like robotics to be used with the MRI.

The unique architecture of the main magnetic field of the MRI system, in accordance with various embodiments, can create a different set of optimization constraints. Because the imaging volume now extends over a broader range of magnetic résonance frequencies, the hardware can be configured to be sensitive to and capture the spécifie frequencies that are generated across the field of view. This frequency spread is usually much larger than a single receive coil tuned to a single frequency can be sensitive to. In addition, because the field strength can be much lower than tradîtional Systems, and because signal intensity can be proportional to the field strength, it is generally considered to be bénéficiai to maximize the signal to noise ratio of the receive coil network. Methods are therefore provided, in accordance with various embodiments, to acquire the full range of frequencies that are generated within the field of view without loss of sensitivity.

In accordance with various embodiments, several methods are provided that can enable imaging within the MRI system. These methods can include combining 1) a variable tuned RF-RX coil; 2) a RF-RX coil array with éléments tuned to frequencies that are dépendent upon the spatial inhomogeneity of the magnetic field; 3) a ultralow-noîse pre-amplifier design; and 4) an RF-RX array with multiple receive coils designed to optimize the signal from a defined and limited field of view for a spécifie body part. These methods can be combined in any combination as needed.

In accordance with various embodiments, a variable tuned RF-RX coil can comprise one or more electronic components for tuning the electromagnetic receive field. In accordance with various embodiments, the one or more electronic components can 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. In accordance with various embodiments, the one or more electronic components used for tuning can include at least one of dielectrics, capacitors, inductors, conductive metals, metamaterials, or magnetic metals. In accordance with various embodiments, tuning the electromagnetic receive field includes changing the current or by changing physical locations of the one or more electronic components. In accordance with various embodiments, the coil is cryogenically cooled to reduce résistance and improve efficiency.

In accordance with various embodiments, the RF-RX array can be comprised of individual coil éléments that are each tuned to a variety of frequencies. The appropriate frequency can be chosen, for example, to match the frequency of the magnetic field located at the spécifie spatial location where the spécifie coil is located. Because the magnetic field can vary as a fonction of space, as shown in Figure 6A, the field and frequency of the coil can be adjusted to approximately match the spatial location. Here the coîls can be designed to image the field locations Bl, B2, and B3, which are physically separated along a single axis.

For this low field system, in accordance with varions embodiments, a low-noise preamplîfier can be designed and configured to leverage the low signal environment ofthe 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 (for example, < 3 MHz and >2 MHz). Typîcal junction field effect transistor designs (J-FET) generally do not hâve the appropriate noise characteristîcs at this frequency and can create high frequency instabilities at the GHz range that can bleed into, although severai décades of dB lower, into the measured frequency range. Since the gain of the system can preferably be, for example, > 80 dB overall, any small instabilities or intrinsic electrical noise can be amplified and dégradé signal integrity.

Referring to Figure 6B, RF-RX coiis can be designed to image spécifie limited field of views based upon the target anatomy. The prostate, for example, is about 60 milliineters deep within the human body (see Figure 6D), so to design a RX coil for prostate imaging, the coil should be configured to enable imaging 60 mm deep inside human body. According to BiotSavait law, the magnetic field of a loop coil can be calculated by the following équation, u₀ 2π * R² I Bz= -------3 ^4π (z² + R²)2 where μ() = 4π * 10-7H/m is the vacuum permeability, R is the radius of the loop coil, z is distance along the center line of the coil from its center, and I is the current on the coil (see Figure 6B). Assuming I = 1 Ampere, with the goal of locating a figure of magnetic field (Bz) at z = 60 mm, the maximum position is when R is 85 mm according to the chart shown in Figure 6C.

Based upon the geometrical constraints of the body, the loop coil can be set up at the space between the human legs upon the torso. As such, it is extremely difficult, if not impossible, to fit a 170-mm diameter coil there. According to Figure 6C, the Bz field value is proportional to the radius of the loop when R is less than 85 mm. As such, it is advantageous that the coil be as large as it can be. For example, the largest loop coil that can be placed between people is about 10 mm large.

As the size of the coil is limited by the space between legs, the magnetic field of a 10mm diameter coil is generally not capable of reaching the depth of prostate. Therefore, single coil may not be enough for prostate imaging thus, in this case, multiple coils could prove bénéficiai in getting signal from different directions. In varions embodiments ofthe MRI System, the magnetic field is provided in the z-direction and RF coils are sensitive to x- and y-direction. In this example case, a loop coil in x-y plane would not collect RF signal from a human since it is sensitive to z-direction, while a butterfly coil can be used in this case. Then based on the location and orientation, RF coil couid be a loop coil or butterfly coil. In addition, a coil can be placed in under the body and there is no limitation for its size.

As for the needs of multiple RX coils, in varions embodiments, decoupling between them can prove bénéficiai for varions embodiments of an MRI System RX coil array. In those cases, each coil can be de-coupled with the other coils, and the decoupling techniques can include, for example, 1) geometry decoupling, 2) capacitive/inductive decoupling, and 3) low/high impédance pre-amplifier coupling.

The MRI System, in accordance with varions embodiments, can hâve a variant magnetic field from the magnet, and its strength can vary linearly along the z direction. The RX coils can be located in different positions in z-direction, and each coil can be tuned to different frequencies, which can dépend on the location ofthe coils in the System.

Based upon the simplicity of single coil loops, these coils can be constructed from simple conductive traces that can be pre-tuned to a desired frequency and printed, for example, on a disposabie substrate. This cheaply fabricated technology can allow a clinician to place the RX coil (or coil array) upon the body at the région of interest for a given procedure and dispose ofthe coil afterwards. For example, and in accordance with varions embodiments, the RX coils can be surface coils, which can be affixed to, e.g., wom or taped to, a patient’s body. For other body parts, e.g. an ankle or a wrist, the surface coil might be a single-loop configuration, figure-8 configuration, or butterfly coil configuration wrapped around the région of interest. For régions that require significant pénétration depth, e.g. the torso or knee, the coil might consist of a Helmholtz coil pair. The main restriction to the reçoive coil is similar to other MRI Systems: the coil must be sensitive to a plane that is orthogonal to the main magnetic field, B0, axis.

In accordance with varions embodiments, the coils might be inductîvely coupled to another loop that is electrically connected to the receive preamplifier. This design would allow for easier and unobstructed access of the receive coils.

In accordance with various embodiments, the size of coils can be limited by the structure of human body. For example, the coils’ size should be posîtioned and configured to fit in the space between human legs when imaging the prostate.

It should be understood that any use of subheadings herein are for organîzatîonal purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used în any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to lirait the design, subfeature, and functionaîity of the specifically described feature.

PROGRAMMABLE LOGIC CONTROLLER

As discussed herein, and in accordance with various embodiments, the various Systems, and various combinations of features that make up the various system embodiments, can also include a programmable logic controller (PLC). PLCs are industrial digital computers which can be designed to operate reliably in harsh usage environments and conditions. PLCs can be designed to handle these types of conditions and environments, not just in the extemal housing, but in the internai components and coolîng arrangements as well. As such, PLCs can be adapted for the control of manufacturing processes, such as assembly lines, or robotic devices, or any activity that requires high reliability control and ease of programming and process fault diagnosis.

In accordance with various embodiments, the System can contain a PLC that can control the system in pseudo real-time. This controller can manage the power cycling and enablîng of the gradient amplifier system, the radio frequency transmission System, the frequency tuning system, and sends a keep alive signal (e.g., a message sent by one device to another to check that the link between the two is operating, or to prevent the link from being broken) to the system watchdog. The system watchdog can continually look for a strobe signal supplied by the computer system. If the computer threads stall, a strobe is mîssed that can trigger the watchdog to enter a fault condition. If the watchdog enters a fault condition, the watchdog can operated to depower the system.

The PLC can generally handle low level logic fonctions on încoming and outgoing signais into system. This system can monitor the subsystem health and control when subsystems needed to be powered or enabled. The PLC can be designed in different ways. One design example includes a PLC with one main motherboard with four expansion boards. Due to the speed of the microcontroller on the PLC, subsystems can be managed in pseudo real-time, while real-time applications can be handled by the computer or spectrometer on the system.

The PLC can serve many functional responsibilities including, for example, powering on/off the gradient amplifiers (discussed în greater detail herein) and the RF amplifier (discussed in greater detail herein), enabling/disabling the gradient amplifiers and the RF amplifier, setting the digital and analog voltages for the RF coil tuning, and strobing the System watchdog.

As discussed above, it should be understood that any use of subheadings herein are for organizational purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to limit the design, sub feature, and functionality of the specifically described feature.

ROBOT

As discussed herein, and in accordance with various embodiments, the various Systems, and various combinations of features that make up the various system embodiments, can also include a robot.

In some medical procedures, such as a prostate biopsy, it is typical for the patient to endure a lengthy procedure in an uncomfortable prône position, which often includes remaîning motionless in one spécifie body position during the entire procedure. In such long procedures, if a metallic ferromagnetic needle is used for the biopsy with guidance from an MRI system, the needle may expérience attraction force from the strong magnets of the MRI system, and thus may cause it to devîate from its path during the length of the procedure. Even in the case of using a non-magnetic needle, the local field distortions can cause distortions in the magnetîc résonance images, and therefore, the image quality surrounding the needle may resuit in a poor quality. To avoid such distortions, pneumatic robots with complex compressed air mechanism hâve been designed to work în conjunction with conventional MRI Systems. Even then, access to target anatomy remains challenging due to the form factor of currently available MRI Systems.

The various embodiments presented herein include improved MRI Systems that are configured to use for guiding in medical procedures, including, for example, robot-assisted, invasive medical procedures. The technologies, methods and apparatuses disclosed herein relate to a guided robotic system using magnetîc résonance imaging as a guidance to automatically guide a robot (generally referred to herein as “a robotic System”) în medical procedures. In accordance with varions embodiments, the disclosed technologies combine a robotic system with magnetîc résonance imaging as guidance. In accordance with varions embodiments, the robotic system disclosed herein is combined with other suitable imaging techniques, for example, ultrasound, x-ray, laser, or any other suitable diagnostic or imaging méthodologies.

It should be understood that any use of subheadings herein are for organizational purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments dîscussed herein and that ail features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

SPECTROMETER

As dîscussed herein, and in accordance with various embodiments, the various Systems, and various combinations of features that make up the various System embodiments, can also include a spectrometer.

A spectrometer can operate to control ail real-time signaling used to generate images. It créâtes the RF transmission (RF-TX) waveform, gradient wavefonns, frequency tuning trigger waveform, and blanking bit wavefonns. These wavefonns are then synchronized with the RF receiver (RF-RX) signais. This System can generate frequency swept RF-TX puises and phase cycled RF-TX puises. The swept RF-TX puises allow for an inhomogeneous B1+ field (RF-TX field) to excite a sample volume more effectively and efficiently. It can also digitize multiple RF-RX channels with the current configuration set to four receiver channels. However, this System architecture allows for an easy System scale-up to increase the number of transmit and receive channels to a maximum of 32 transmit channels and 16 receive channels wîthout having to change the underlying hardware or software architecture.

The spectrometer can serve many functional responsibilities including, for example, generating and synchronizing the RF-TX (dîscussed in greater detail herein) wavefonns, Xgradient wavefonns, Y-gradient wavefonns, blanking bit waveforms, frequency tuning trigger waveform and RF-RX Windows, and digitizîng and signal processing the RF-RX data using, for example, quadrature démodulation followed by a finite impulse response filter décimation such as, for example, a cascade integrating comb (CIC) filter décimation.

The spectrometer can be designed in different ways. One design example includes a spectrometer with three main components: 1) a first software design radio (SDR 1) operating with Basic RF-TX daughter cards and Basic RF-RX daughter cards; 2) a second software design radio (SDR 2) operating with LFRF TX daughter cards and Basic RF-RX daughter cards; and 3) a clock distribution module (octoclock) that can synchronize the two devices.

SDRs are the real-time communication device between the transmitted signais and received MRI signais. They can communicate over 10Gbit optical fiber to the computer using a Small Form-factor Pluggable Plus transceiver (SFP+) communication protocol. This communication speed can allows the waveforms to be generated with high fidelity and high reliability.

Each SDR can include a motherboard with an integrated field-programmable gâte array (FPGA), digital to analog converters, analog to digital converters, and four module slots for integrating different daughtercards. Each of these daughtercards can function to change the frequency response of the associated TX or RX channel. In accordance with varions embodiments, the System can utilizes many variations daughtercards inciuding, for example, a Basic RF version, and a low frequency (LF) RF version. The Basic RF daughtercards can be used for generating and measuring RF signais. The LF RF version can be used for généraiing gradient, trigger and blanking bit signais.

The octociock can be used to synchronize a multi-channel SDR System to a common timing source while providing high-accuracy time and frequency reference distribution. It can do so, for example, with 8-way time and frequency distribution (1 PPS and 10MHz). An example of an octociock is the Ettus Octociock CDA, which can distribute a common clock to up to eight SDRs to ensure phase coherency between the two or more SDR sources.

It should be understood that any use of subheadings herein are for organizational purposes, and should not be read to lirait the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for infonnational purposes, and not in any way to lirait the design, subfeature, and functionaîity of the specifically described feature.

RF AMP/GRADIENT AMP

As discussed herein, and in accordance with various embodiments, the various Systems, and various combinations of features that make up the various System embodiments, can also include a radio frequency amplifier (RF amplifier) and a gradient amplifier.

A RF amplifier is a type of electronic amplifier that can couverts a low-power radiofrequency signal into a higher power signal. In operation, the RF amplifier can accept signais at low amplitudes and provide, for example, up to 60 dB of gain with a fiat frequency response. This amplifier can accept three phase AC input voltage and can hâve a 10% max duty cycle. The 29 amplifier can be gated b y a 5 V digital signal so that unwanted noise is not generated when the MRI is receiving signal.

In operation, a gradient amplifier can increase the energy of the signal before it reaches the gradient coils such that the field strength can be intense enough to produce the variations in the main magnetic field for localization of the later received signal. The gradient amplifier can hâve two active amplification channels that can be controlled independently. Each channel can send out current to either the X or Y channel respectively. The third axis of spatial encoding is generally handled by a permanent gradient in the main magnetic field (B0). With varying combinations of puise sequences, the signal can be localized in three dimensions and reconstructed to create an object.

It should be understood that any use of subheadings herein are for organizatîonal puiposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein îs applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

DISPLAY/GUI

As discussed herein, and in accordance with valions embodiments, the various Systems, and various combinations of features that make up the various system embodiments, can also include a display in the form of, for example, a graphical user interface (GUI). In accordance with various embodiments, the GUI can take any contemplated form necessary to convey the information necessary to run magnetic résonance imaging procedures.

Further, it should be appreciated that the display may be embodied in any of a number of other forms, such as, for example, a rack-mounted computer, mainframe, supercomputer, server, client, a desktop computer, a laptop computer, a tablet computer, hand-held computing device (e.g., PDA, cell phone, Smart phone, palmtop, etc.), cluster grid, netbook, embedded Systems, or any other type of spécial or general purpose display device as may be désirable or appropriate for a given application or environment.

The GUI is a system of interactive visual components for computer software. A GUI can display objects that convey information, and represent actions that can be taken by the user. The objects change color, size, or vîsibîlity when the user interacts with them. GUI objects include, for example, icons, cursors, and buttons. These graphical éléments are sometimes enhanced with sounds, or visual effects like transparency and drop shadows.

A user can internet with a GUI using an input device, which can include, for example, alphanumeric and other keys, mouse, a trackball or cursor direction keys for communicating direction information and command sélections to a processor and for controlling cursor movement on the display. An input device may also be the display confîgured with touchscreen input capabilities. This input device typically has two degrees of freedom in two axes, a first axis (i.e., x) and a second axis (i.e., y), that allows the device to specify positions in a plane. However, it should be understood that input devices allowing for 3 dimensional (x, y and z) cursor movement are also contemplated herein.

In accordance with various embodiments, the touchscreen, or touchscreen monitor, can serves as the primary human interface device that allows a user to interact with the MRI. The screen can hâve a projected capacitive touch sensitive display with an interactive Virtual keyboard. The touchscreen can hâve several fonctions including, for example, displaying the graphical user interface (GUI) to the user, relaying user input to the system’s computer, and starting or stopping a scan.

In accordance with various embodiments, GUI views can be typically screens displayed (Qt widgets) to the user with appropriate buttons, edit fields, labels, images, etc. These screens can be constructed using a designer tool such as, for example, the Qt designer tool, to control placement of widgets, their alignment, fonts, colors, etc. A user interface (UI) sub controller can possess modules confîgured to control the behavior (display and responses) of the respective view modules.

Several application utilities (App Util) modules can performs spécifie funétions. For example, S3 modules can handle data communication between the System and, for example. Amazon Web Services (AWS). Event Fiiters can be présent to ensure valid characters are displayed on screen when user inputs are required. Dialog messages can be used to show various status, progress messages or require user prompts. Moreover, a System controller module can be utilized to handle coordination between the sub controller modules, and key data processing blocks in the System, the puise sequence generator, puise inteipreter, spectrometer and reconstruction.

It should be understood that any use of subheadings herein are for orgamzational purposes, and should not be read to lirait the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

PROCESSING MODULE

As discussed herein, and in accordance with various embodiments, the various workflows or methods, and various combinations of steps that make up the various workflow or method embodiments, can also include a processing module.

In accordance with various embodiments, a processing module serves many fonctions. For example, a processing module can generally operate to receive signal data acquîred during the scan, process the data, and reconstruct those signais to produce an image that can be viewed (for example, via a touchscreen monitor that displays a GUI to the user), analyzed and annotai ed b y System users. Generally, to create an image, an NMR signal must be local ized in three-dimensional space. Magnetic gradient coils localize the signal and are operated before or during the RF acquisition. By prescribing a RF and gradient coil application sequence, called a puise sequence, the signais acquired cônes pond to a spécifie magnetic field and RF field arrangement. Using mathematical operators and image reconstruction techniques, arrays of these acquired signais can be reconstructed into an image. Usually these images are generated from simple linear combinations of magnetic field gradients. In accordance with various embodiments, the System can operate to reconstruct the acquired signais from a-priori knowledge of, for ex ample, the gradient fields, RF fields, and puise sequences.

In accordance with various embodiments, the processing module can also operate to compensate for patient motion during a scan procedure. Motion (e.g., beating heart, breathing lungs, bulk patient movement) is one of the most common sources of artifacts in MRI, with such artifacts affecting image quality by leading to misinterpretations in the images and a subséquent loss în diagnostic quality. Therefore, motion compensation protocols can help address these issues at minimal cost in time, spatial resolution, temporal resolution, and signal-to-noise ratio.

In accordance with various embodiments, the processing module might include artîficial intelligence machine learning modules designed to denoise the signal and improve the image signal-to-noise ratio.

In accordance with various embodiments, the processing module can also operate to assist clinicians in planning a path for subséquent patient intervention procedures, such as biopsy. In accordance with various embodiments, a robot can be provided as part of the System to perform the intervention procedure. The processing module can communicate instructions to the robot, 32 based on image analysis, to properly access, for example, the appropriate région of the body requiring a biopsy.

It should be understood that any use of subheadings herein are for organizational purposes, and should not be read to limît the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described below. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

In accordance with various embodiments, the various Systems, and various combinations of features that make up the various System components and embodiments of the disclosed magnetic résonance imaging System are disclosed herein.

Figure 7 is a flowehart for a method S100 of performing magnetic résonance imaging, according to various embodiments. In accordance with various embodiments, the method S100 includes inputting patient parameters into a magnetic résonance imaging System at step SI 10. In accordance with various embodiments, the System includes a housîng having a front surface, a permanent magnet for provîding a static magnetic fieid, a radio frequency transmit coil, and a single-sided gradient coil set. In accordance with various embodiments, the radio frequency transmit coil and the single-sided gradient coil set are positioned proxîmate to the front surface. In accordance with various embodiments, the System includes an electromagnet, a radio frequency receive coil, and a power source. In accordance with various embodiments, the power source is configured to flow current through at least one of the radio frequency transmit coil, the single-sided gradient coil set, or the electromagnet to generate an electromagnetic fieid in a région of interest. In accordance with various embodiments, the région of interest résides outside the front surface.

As shown in Figure 7, the method SI 00 also includes executing a patient positioning protocol comprising running at least one first scan at step S120, running at least one second scan at step S130, reviewing the ai least one second scan at step S140, and determining at least one path for conducting a biopsy based on review of the at least one second scan at step SI50.

In accordance with various embodiments, the radio frequency transmit coil and the singlesided gradient coil set are located on the front surface. In accordance with various embodiments, the front surface is a concave surface. In accordance with various embodiments, the permanent magnet has an aperture through center of the permanent magnet. In accordance with various embodiments, the static magnetic field of the permanent magnet ranges from 1 mT to 1 T. In accordance with various embodiments, the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

In accordance with various embodiments, the radio frequency transmit coil includes a first ring and a second ring that are connected via one or more capacitors and/or one or more rungs. In accordance with various embodiments, the radio frequency transmit coil is non-planar and oriented to partîally surround the région of interest. In accordance with various embodiments, the single-sided gradient coil set is non-planar and oriented to parti al ly surround the région of interest. In accordance with various embodiments, the single-sided gradient coil set is configured to project a magnetic field gradient to the région of interest. In accordance with various embodiments, the single-sided gradient coil set 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 located opposite each other about a center région of the single-sided gradient coil set. In accordance with various embodiments, the single-sided gradient coil set has a rise time less than 10 ps.

In accordance with various embodiments, the electromagnet is configured to alter the static magnetic field of the permanent magnet within the région of interest. In accordance with various embodiments, the electromagnet has a magnetic field strength from 10 mT to 1 T. In accordance with various embodiments, the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest. In accordance with various embodiments, the radio frequency receive coil is in one of a single-loop coil configuration, figure-8 coil configuration, or butterfly coil configuration, wherein the coil is smaller than the région of interest. In accordance with various embodiments, the radio frequency transmit coil and the single-sided gradient coil set are concentric about the région of interest. In accordance with various embodiments, the magnetic résonance imaging system is a single-sided magnetic résonance imaging system that comprises a bore having an openmg positioned about a center région of the front surface.

Figure 8 is a flowchart for a method S200 of performing magnetic résonance imaging, according to various embodiments. In accordance with various embodiments, the method S200 includes inputting patient parameters into a magnetic résonance imaging system at step S210. In accordance with various embodiments, the system includes a housing having a concave front surface, a permanent magnet for providing a static magnetic field, a radio frequency transmît coil, and at least one gradient coil set. In accordance with various embodiments, the radio frequency transmit coil and the at least one gradient coil set are positioned proximale to the concave front surface. In accordance with various embodiments, the radio frequency transmit coil and the at least one gradient coil set are configured to generate an electromagnetic field in a région of interest. In accordance with various embodiments, the région of interest résides outside the concave front surface. In accordance with various embodiments, the System includes a radio frequency receive coil for detecting signal in the région of interest.

As shown in Figure 8, the method S2Q0 includes executing a patient positioning protocol comprising running at least one first scan at step S220, running at least one second scan at step S230, reviewîng the ai least one second scan at step S240, and detennining at least one path for conducting a biopsy based on review of the at least one second scan at step S250.

In accordance with various embodiments, the radio frequency transmit coil and the singlesided gradient coil set are located on the concave front surface. In accordance with various embodiments, the static magnetic field of the permanent magnet ranges from 1 mT to 1 T. In accordance with various embodiments, the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT. In accordance with various embodiments, the radio frequency transmit coil comprises a first ring and a second ring that are connected via one or more capacitors and/or one or more rangs. In accordance with various embodiments, the radio frequency transmit coil is non-planar and oriented to partially surround the région of interest. In accordance with various embodiments, the at least one gradient coil set is non-planar, single-sided, and oriented to partially surround the région of interest. In accordance with various embodiments, the at least one gradient coil set is configured to project magnetic field gradient în the région of interest.

In accordance with various embodiments, the at least one gradient coil set comprises 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 located opposite each other about a center région of the at least one gradient coil set. In accordance with various embodiments, the at least one gradient coil set has a rise time less than 10 gs. In accordance with various embodiments, the permanent magnet has an aperture through center of the permanent magnet. In accordance with various embodiments, the System further includes an electromagnet configured to alter the static magnetic field of the permanent magnet within the région of interest. In accordance with various embodiments, the electromagnet has a magnetic field strength from 10 mT to 1 T. In accordance with various embodiments, the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest. In accordance with various embodiments, the radio frequency receive coil is in one of a single-loop coil configuration, figure-8 coil configuration, or butterfly coil configuration, where the coil is smaller than the région of înterest.

In accordance with various embodiments, the radio frequency transmit coil and the at least one gradient coil set are concentric about the région of interest. In accordance with various embodiments, the magnetic résonance imaging System is a single-sided magnetic résonance imaging System that comprises a magnetic résonance imaging scanner or a magnetic résonance imaging spectrometer.

Figure 9 is a flowchart for a method S300 of performing a scan on a magnetic résonance imaging System, according to various embodiments. In accordance with various embodiments, the method S300 includes at step S310 providing a housing having a front surface, a permanent magnet for providing a static magnetic field, a radio frequency transmit coil, and a single-sided gradient coil set. In accordance with varions embodiments, the radio frequency transmit coil and the single-sided gradient coil set are positioned proximate to the front surface. In accordance with various embodiments, the method S300 includes providing an electromagnet at step S320. In accordance with various embodiments, the method S300 includes at step S330 activating at least one of the radio frequency transmit coil, the single-sided gradient coil set, or the electromagnet to generate an electromagnetic field in a région of interest. In accordance with various embodiments, the région of interest résides outside the front surface.

In accordance with various embodiments, the method S300 includes activating a radio frequency receive coil to obtain imaging data at step S340, reconstructing obtaîned imaging data to produce an output image for analysis at step S35O, and displaying the output image for user review and annotation at step S360.

In accordance with various embodiments, the radio frequency transmit coil and the singlesided gradient coil set are Iocated on the front surface. In accordance with various embodiments, the front surface is a concave surface. In accordance with various embodiments, the permanent magnet has an aperture through center of the permanent magnet. In accordance with various embodiments, the static magnetic field of the permanent magnet ranges from l mT to 1 T. In accordance with various embodiments, the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

In accordance with various embodiments, the radio frequency transmit coil includes a fïrst ring and a second ring that are connected via one or more capacîtors and/or one or more rangs. In accordance with various embodiments, the radio frequency transmit coil is non-planar and oriented to partially surround the région of interest. In accordance with various embodiments, the single-sided gradient coil set is non-planar and oriented to partially surround the région of interest. In accordance with various embodiments, the single-sided gradient coil set is configured to project a magnetic field gradient to the région of interest. In accordance with various embodiments, the single-sided gradient coil set 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 located opposite each other about a center région of the single-sided gradient coil set. In accordance with various embodiments, the single-sided gradient coil set has a rise time less than 10 ps.

In accordance with various embodiments, the electromagnet is configured to alter the static magnetic field of the permanent magnet within the région of interest. In accordance with various embodiments, the electromagnet has a magnetic field strength from 10 mT to 1 T. In accordance with various embodiments, the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest. In accordance with various embodiments, the radio frequency receive coil is in one of a single-loop coil configuration, figure-8 coil configuration, or butterfly coil configuration, wherein the coil îs smaller than the région of interest. In accordance with various embodiments, the radio frequency transmit coil and the single-sided gradient coil set are concentric about the région of interest. In accordance with various embodiments, the magnetic résonance imaging System is a single-sided magnetic résonance imaging System that comprises a bore having an opening positioned about a center région of the front surface.

Figure 10 is a flowchart for a method S400 of performing a scan on a magnetic résonance imaging System, according to various embodiments. In accordance with various embodiments, the method S400 includes at step S410 providing a housing having a concave front surface, a permanent magnet for providing a static magnetic field, a radio frequency transmit coil, and a single-sided gradient coil set. In accordance with various embodiments, the radio frequency transmit coil and the single-sided gradient coil set are positioned proximate to the front surface.

In accordance with various embodiments, the method S400 includes at step S420 activating at least one of the radio frequency transmit coil and the at least one gradient coil set to generate an electromagnetic field in a région of interest. In accordance with various embodiments, the région of interest résides outside the concave front surface.

In accordance with various embodiments, the method S400 includes activating a radio frequency receive coil to obtain imaging data at step S430, reconstructing obtained imaging data to produce an output image for analysis at step S440, and displaying the output image for user review and annotation at step S450.

In accordance with varions embodiments, the radio frequency transmit coil and the singlesided gradient coil set are located on the concave front surface. In accordance with various embodiments, the static magnetic field of the permanent magnet ranges from 1 mT to 1 T. In accordance with various embodiments, the static magnetic field ofthe permanent magnet ranges from 10 mT to 195 mT. In accordance with various embodiments, the radio frequency transmit coil comprises a first ring and a second ring that are connected via one or more capacitors and/or one or more rangs. In accordance with various embodiments, the radio frequency transmit coil is 5 non-planar and oriented to partially surround the région of interest. In accordance with various embodiments, the at least one gradient coil set is non-planar, single-sided, and oriented to partially surround the région of interest. In accordance with various embodiments, the at least one gradient coil set is configured to project magnetic field gradient in the région of interest.

In accordance with various embodiments, the at least one gradient coil set comprises one 10 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 located opposite each other about a center région of the ai least one gradient coil set. In accordance with various embodiments, the at least one gradient coil set has a rise time less than 10 gs. In accordance with various embodiments, the permanent magnet has an aperture through center of the permanent magnet. In 15 accordance with various embodiments, the system further includes an electromagnet configured to al ter the static magnetic field of the permanent magnet within the région of interest. In accordance with various embodiments, the electromagnet has a magnetic field strength from 10 mT to 1 T. In accordance with various embodiments, the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the 20 région of interest. In accordance with various embodiments, the radio frequency receive coil is in one of a single-loop coil configuration, figure-S coil configuration, or butterfly coil configuration, where the coil is smaller than the région of interest.

In accordance with various embodiments, the radio frequency transmit coil and the at least one gradient coil set are concentric about the région of interest. In accordance with various 25 embodiments, the magnetic résonance imaging system is a single-sided magnetic résonance imaging system that comprises a magnetic résonance imaging scanner or a magnetic résonance imaging spectrometer.

It should be understood that any use of subheadings herein are for organizatîonal purposes, and should not be read to limit the application of those subheaded features to the 30 varions embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used in any contemplated combination, regardless ofthe spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, large! y for informational purposes, and not in any way to limit the design, sub feature, and functionaîity of the specifïcally described feature.

PATIENT INTAKE

As discussed herein, and in accordance with various embodiments, the various workflows or methods, and various combinations of steps that make up the various workflow or method embodiments, can also include a patient intake step.

As part of this step, and any ail relevant information can be part of the patient intake step, including the intake of ali data relevant to the performance of the magnetic résonance system, în accordance with various embodiments herein.

In accordance with various embodiments, the patient intake step can include, not only data inputted by user, but also data downloaded from any memory source, whether it be, for example, data from a remote data storage component (e.g., the cioud), an on-board data storage component, or portable data storage component (e.g., extemal flash/solid State drives and external hard drives).

In accordance with various embodiments, and further related to memory sources, an onboard data storage component (e.g., on-board a computing system within an MRI system) can be a random access memory (RAM) or other dynamic memory, or a read only memory (ROM) or other static storage device.

In accordance with various embodiments, and further related to memory sources, a remote or portable data storage component can include, for ex ample, a magnetic disk, optical disk, solid State drive (SSD), and a media drive and a removable storage interface. A media drive may include a drive or other mechanism to support fixed or removable storage media, such as a hard disk drive, a floppy disk drive, a magnetic tape drive, an optical disk drive, a CD or DVD drive (R or RW), flash drive, or other removable or fixed media drive. As these examples illustrate, the storage media may include a computer-readable storage medium havîng stored therein particular computer software, instructions, or data.

In accordance with various embodiments, a storage device may include other similar instrumental!ties for allowing computer programs or other instructions or data to be loaded into computing system. Such instrumentalities may include, for example, a removable storage unit and an interface, such as a program cartridge and cartridge interface, a removable memory (for example, a flash memory or other removable memory module) and memory slot, and other removable storage units and interfaces that allow software and data to be transferred from the storage device to computing system.

In accordance with various embodiments, the data types that can be user înputted, uploaded, downloaded, etc., can include, for example, patient name, patient sex, patient weight, patient height, patient contact information, patient birthdate, patient’s referring physician, and patient race. In addition, a clinical baseline can be user înputted that includes information such as the patient’s Gleason score for any past biopsies, the frequency of sexual intercourse, the last tinte the patient had food, and the patient’s PSA level.

It should be understood that any use of subheadings herein are for organîzational purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in all the various embodiments discussed herein and that ail features described herein can be used în any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

PATIENT POSITIONING

As discussed herein, and in accordance with various embodiments, the various workflows or methods, and various combinations of steps that make up the various workflow or method embodiments, can also include a patient posîtioning step.

As a precursor to the posîtioning, a patient will generally undergo a patient préparation and screening process, whereby the patient is screened for foreign bodies and devices such as pacemakers that may represent a contraîndication to imaging. The patient’s important health conditions, including allergies, as well as patient data received as part of the patient intake process, are also revîewcd.

For posîtioning in standard full-body MRIs, a patient would generally be placed on a table, usually in the supine position. Receiver imaging coils are arranged around the body part of interest (head, chest, knee, etc.) If EKG or respiratory gating is required, then these devices are attached at this time. A key anatomie structure such as the bridge of the nose or umbiliens is identified as a landmark using laser guidance, and this is correlated with table position by pressing a button on the gantry.

In accordance with various embodiments, using the example system illustrated in Figures 11 A-l 1X as a basis herein, a patient is positioned in any number of different positions depending on the type of anatomical scan.

As illustrated in Figure 11 A, when the abdomen is the région scanned, the patient can be laid on a surface at a latéral position. As illustrated, for the abdominal scan, a patient can be positioned to lay sideways facing the bore, with the arm closest to the table stretched out and the other at the side of the body. The abdomen région can be positioned such that it is directly in front of the bore.

As ilîustrated in Figure 11 B, when an appendage (e.g., arm or hand) is the région scanned, the patient can be laid on a surface at a supine position. As ilîustrated, for the appendage scan, a patient can be positioned to be laid down with the arm or hand to be scanned situated directly in front of the bore.

As ilîustrated in Figure 1 IC, when an appendage (e.g., ann or hand) is the région scanned, the patient can also be placed ai a seated position. As ilîustrated, for the appendage scan, a patient can be positioned to be seated with ann to be scanned raised up against the System such that it is situated directly in front of the bore.

As ilîustrated in Figure 11D, when an appendage (e.g., elbow) is the région scanned, the patient can also be placed at a seated position. As ilîustrated, for the appendage scan, a patient can be positioned to be seated with elbow to be scanned raised up against the System such that it is situated directly in front of the bore and the other arm resting comfortably.

As ilîustrated in Figure HE, when an appendage (e.g., knee) is the région scanned, the patient can also be situated to stand with the one leg lifted that is to be scanned. As ilîustrated, for the appendage scan, a patient can be positioned to be standing and facing the bore such that the leg of interest is lifted with the knee resting directly in front of the bore and the other leg placed firmly on the ground for stability.

As ilîustrated in Figure 1 IF, when an appendage (e.g., knee) is the région scanned, the patient can also be situated in a latéral position. As ilîustrated, for the appendage scan, a patient can be positioned to lay sideways facing the bore, with the leg of interest bent and the other leg resting on the table and extended out. The patient’s knee can be placed such that it is directly in front of the bore.

As ilîustrated in Figure 1 IG, when an appendage (e.g., foot) is the région scanned, the patient can also be situated in a latéral position. As ilîustrated, for the appendage scan, a patient can be positioned to lay sideways facing away from the bore, with the leg of interest bent and resting on the table and the other leg extended out. The patient’s foot can be placed such that it is directly in front of the bore.

As ilîustrated in Figure 11H, when an appendage (e.g., foot) is the région scanned, the patient can also be situated in a seated position. As ilîustrated, for the appendage scan, a patient can be positioned to be seated facing the bore, with the leg of interest extended out toward the bore and the other leg resting comfortably. The patient’s foot can be placed such that it is directly in front of the bore.

As illustrated in Figure 1II, when an appendage (e.g., wrist) is the région scanned, the patient can be situated in a seated position. As illustrated, for the appendage scan, a patient can be positioned to be seated parallel to the system, such that the wrist of interest is directly in front of the bore with and the other arm is resting comfortably to the side.

As illustrated in Figure 1 U, when the breast is the région scanned, the patient can be laid on a surface in a latéral position. As illustrated, for the breast scan, a patient can be positioned to lay sideways facing the bore, with one arm extended out above the head and the other hand resting to the side of the body. The breast région can be positioned to be directly in front of the bore.

As illustrated in Figure 1IK, when the breast is the région scanned, the patient can also be placed at a seated position. As illustrated, for the breast scan, a patient can be positioned to be seated and facing the bore such that anns are extended out and resting on the top of the system. The breast région can be positioned to be directly in front of the bore.

As illustrated in Figure 1 IL, when the breast is the région scanned, the patient can also be placed at a kneeling position. As illustrated, for the breast scan, a patient can be positioned to be kneeling and facing the bore such that anns are extended out and resting on the top of the system. The breast région can be positioned to be directly in front of the bore.

As illustrated in Figure l IM, when the head is the région scanned, the patient can be laid on a surface at a latéral position. As illustrated, for the head scan, a patient can be positioned to lay sideways facing away from the bore, with the head placed directly in front of the bore.

As illustrated in Figure UN, when the head is the région scanned, the patient can also be laid on a surface at a supine position. As illustrated, for the head scan, a patient can be positioned to lay down face up, with the top of the head against the system, such that it is situated directly in front of the bore.

As illustrated in Figure 110, when the heart is the région scanned, the patient can be placed at a seated or standing position. As illustrated, for the heart scan, a patient can be positioned to be seated facing the bore such that the heart région is situated directly in front of the bore.

As illustrated in Figure 1 IP, when the kidney is the région scanned, the patient can be laid on a surface at a latéral position. As illustrated, for the kidney scan, a patient can be positioned to lay sideways facing the bore, with the arm closest to the table stretched out and the other at the side of the body. The kidney région can be positioned such that it is directly in front of the bore.

As illustrated in Figure 11Q, when the liver is the région scanned, the patient can be laid on a surface at a latéral position. As illustrated, for the liver scan, a patient can be positioned to lay sideways facing the bore, with the arm closest to the table stretched out or bent to rest the head, and the other at the side of the body. The liver région can be positioned such that it is directly in front of the bore.

As illustrated in Figure 1 IR, when the lung is the région scanned, the patient can be placed at a seated position. As illustrated, for the lung scan, a patient can be positioned to be seated facing away from the bore such that the lung région is situated directly in front of the bore.

As illustrated in Figure HS, when the neck is the région scanned, the patient can be laid on a surface at a latéral position. As illustrated, for the neck scan, a patient can be positioned to lay sideways and face away from the bore. The neck région can be positioned to be directly in front of the bore.

As illustrated in Figure HT, when the pelvis is the région scanned, the patient can be laid on a surface at a lithotomy position. As illustrated, for the pelvic scan, a patient can be positioned to hâve their back resting on the table and legs raised up to be resting against the top of the system. The pelvic région can be positioned to be directly in front of the bore.

As illustrated in Figure H U, when the pelvis is the région scanned, the patient can also be laid on a surface at a latéral position. As illustrated, for the pelvic scan, a patient can be positioned to lay sideways and face away from the bore, The pelvic région of the body can be positioned to be directly in front of the bore.

As illustrated in Figure 1IV, when the pelvis is the région scanned, the patient can also be placed at a prone position. As illustrated, for the pelvic scan, a patient can be positioned to rest with the chest against a surface, facing away from the bore, The pelvic région can be positioned such that it is directly in front of the bore.

As illustrated în Figure HW, when the shoulder is the région scanned, the patient can be placed at a seated position. As illustrated, for the shoulder scan, a patient can be positioned to be seated next to the system with the shoulder to be scanned situated directly in front of the bore.

As illustrated in Figure 1IX, when the spine is the région scanned, the patient can be placed at a seated position. As illustrated, for the spine scan, a patient can be positioned to be seated with back facing away from the bore and spine situated directly in view of the bore.

It should be understood that any use of subheadings herein are for organizational purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the varions embodiments discussed herein and that ail features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

BIOPSY GUIDANCE

As discussed herein, and in accordance with various embodiments, the varions workflows or methods, and various combinations of steps that make up the various workflow or method embodiments, can also include biopsy guidance using the disclosed MRI System.

In accordance with various embodiments, the procedure for biopsy guidance using the disclosed MRI System may include one from the list of medical procedures consisting of transperineal biopsy, transperineal LDR brachytherapy, transperineal H DR brachytherapy, transperineal laser ablation, transperineal cryoablation, transrectal HIFU, breast biopsies, deep brain stimulation (DBS), brain biopsy, liver biopsy, kidney biopsy, lung biopsy, coronary stent insertion, brain stent insertion, and intensity modulated radiation treatment guidance.

It should be understood that any use of subheadings herein are for organizational purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used în any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not în any way to limit the design, subfeature, and functionality of the specifically described feature.

CALIBRATION

As discussed herein, and in accordance with various embodiments, the various workflows or methods, and various combinations of steps that make up the various workflow or method embodiments, can also include a calibration step.

Calibration can take many forms of processes. Generally, calibration involves running a ftill scan, similar to the scan run on a patient, in order to ensure image quality. In accordance with various embodiments, after a predetermined period, a user can be prompted to initiate a calibration routine such as, for example, a RF calibration routine. As part of initiating a calibration, a calibration phantom is posîtioned to allow calibration to advance. A calibration phantom can take many forms. Generally, a calibration phantom can be an object (usually an artîficial object) of known size and composition that is imaged to test, adjust or monitor an MRI systems homogeneity, imaging performance and orientation aspects. A phantom can be a fluidfilled container or bottle often fiiled with a plastic structure of various sizes and shapes.

RF Calibration routine, in particular, optimizes RF puise parameters such as, for example, signal power, signal duration and signal bandwidth to ensure image quality. The calibration routine acquires signal data from a calibration phantom using a predetermined set of parameters and sequence. Calibration data can be processed to déterminé the parameter set that should be used during imaging scans.

It should be understood that any use of subheadings herein are for organizatîonal purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein can be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to limit the design, subfeature, and functionality of the specifically described feature.

PRE-POLARIZER

As discussed herein, and in accordance with various embodiments, the various workflows or methods, and various combinations of steps that make up the various workflow or method embodiments, can also include a pre-polarzation step.

In some emobodiments, the prepolarizer can be charged by a system power supply. The powering of this polarizer would temporarily change the magnetic field within the field of view either by increasing or decreasing the main magnetic field strength. This change in the magnetic field then créâtes a change in the total number of nuclear spins that are alîgned within the field of view and it changes the time constants by which the nuclear spins relax. An increase in the field allows for more nuclear spins to be aligned with the field, thus temporarily increasing the signal from a given voxel. A decrease in the field changes the relaxation properties of the objects and could allow for increased contrast within the field of view.

In accordance with various embodiments, the prepolarizer might be first charged to increase the field strength and therefore the signal strength. Then after waitîng an appropriate amount of time for the nuclear spins to align (as dictated b y the Tl time of the desired spins), the prepolarizer can be removed. As this prepolarizer is depowered, the spins that are aligned will begin to relax and loose energy but can still be imaged by the magnetic résonance system at an increased signal level than when the system did not apply a prepolarizing puise.

It should be understood that any use of subheadings herein are for organizational purposes, and should not be read to limit the application of those subheaded features to the various embodiments herein. Each and every feature described herein is applicable and usable in ail the various embodiments discussed herein and that ail features described herein ean be used in any contemplated combination, regardless of the spécifie example embodiments that are described herein. It should further be noted that exemplary description of spécifie features are used, largely for informational purposes, and not in any way to lîmit the design, sub feature, and functionality of the specifically described feature

RECITATION OF EMBODIMENTS

1. A magnetic résonance imaging System comprising: a housing comprising: a front surface, a permanent magnet for providing a static magnetic field, a radio frequency transmit coil, and a single-sided gradient coil set, wherein the radio frequency transmit coil and the single-sided gradient coil set are positioned proximate to the front surface; an electromagnet; a radio frequency receive coil; and a power source, wherein the power source is configured to flow current through ai least one of the radio frequency transmit coil, the single-sided gradient coil set, or the electromagnet to generate an electromagnetic field in a région of interest, wherein the région of interest résides outside the front surface.

2. The system of embodiment 1, wherein the radio frequency transmit coil and the single-sided gradient coil set are Iocated on the front surface.

3. The system of anyone of embodiments 1-2, wherein the front surface is a concave surface.

4. The system of anyone of embodiments 1-3, wherein the permanent magnet has an aperture through center of the permanent magnet.

5. The system of anyone of embodiments 1-4, wherein the static magnetic field of the pennanent magnet ranges from 1 mT to 1 T.

5- 1. The system of anyone of embodiments 1-4, wherein the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

6. The system of anyone of embodiments 1-5, wherein the radio frequency transmit coil comprises a first ring and a second ring that are connected via one or more capacitors and/or one or more rangs.

7. The system of anyone of embodiments 1-6, wherein the radio frequency transmit coil is non-planar and oriented to partially surround the région of interest.

8. The System of anyone of embodiments 1-7, wherein the single-sided gradient coil set is non-planar and oriented to partially surround the région of interest, and wherein the singlesided gradient coil set is configured to project a magnetic field gradient to the région of interest.

9. The System of anyone of embodiments 1-8, wherein the single-sided gradient coil set comprises 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 located opposite each other about a center région of the single-sided gradient coil set.

10. The System of anyone of embodiments 1 -9, wherein the single-sided gradient coil set has a rise time less than 10 ps.

11. The System of anyone of embodiments 1-10, wherein the electromagnet is configured to alter the static magnetic field of the permanent magnet within the région of interest.

12. The System of anyone of embodiments 1-11, wherein the electromagnet has a magnetic field strength from 10 mT to 1 T.

13. The System of anyone of embodiments 1-12, wherein the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest.

14. The System of anyone of embodiments 1-13, wherein the radio frequency receive coil îs in one of a single-loop coil configuration, figure-8 coil configuration, or butterfly coil configuration, wherein the coil is smaller than the région of interest.

15. The System of anyone of embodiments 1-14, wherein the radio frequency transmit coil and the single-sided gradient coil set are concentric about the région of interest.

16. The System of anyone of embodiments 1-15, wherein the magnetic résonance imaging System is a single-sided magnetic résonance imaging System that comprises a bore having an opening positioned about a center région of the front surface.

17. A magnetic résonance imaging system comprising: a housing comprising: a concave front surface, a permanent magnet for providing a static magnetic field, a radio frequency transmit coil, and at least one gradient coil set, wherein the radio frequency transmit coil and the at least one gradient coil set are positioned proximate to the concave front surface, wherein the radio frequency transmit coil and the at least one gradient coil set are configured to generate an electromagnetic field in a région of interest, wherein the région of interest résides outside the concave front surface; and a radio frequency receive coil for detecting signal in the région of interest.

18. The System of embodiment 17, wherein the radio frequency transmît coil and the at least one gradient coil set are located on the concave front surface.

19. The sysiem of anyone of embodiments 17-18, wherein the static magnetic fieid of the permanent magnet ranges from 1 mT to 1 T.

20. The System of anyone of embodiments 17-19, wherein the static magnetic fieid of the permanent magnet ranges from 10 mT to 195 mT.

21. The System of anyone of embodiments 17-20, wherein the radio frequency transmit coil comprises a first ring and a second ring that are connected via one or more capacitors and/or one or more rangs.

22. The System of anyone of embodiments 17-21, wherein the radio frequency transmit coil is non-planar and oriented to partially surround the région of interest.

23. The System of anyone of embodiments 17-22, wherein the at least one gradient coil set is non-planar, single-sided, and oriented to partially surround the région of interest, and wherein the at least one gradient coil set is configured to project magnetic fieid gradient in the région of interest.

24. The system of anyone of embodiments 17-23, wherein the at least one gradient coil set comprises 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 located opposite each other about a center région of the at least one gradient coil set.

25. The system of anyone of embodiments 17-24, wherein the at least one gradient coil set has a rise time less than 10 ps.

26. The system of anyone of embodiments 17-25, wherein the permanent magnet has an aperture through center of the permanent magnet.

27. The system of anyone of embodiments 17-26, further comprising: an electromagnet configured to alter the static magnetic fieid of the permanent magnet withm the région of interest.

28. The system of anyone of embodiments 17-27, wherein the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest.

29. The system of anyone of embodiments 17-28, wherein the radio frequency receive coil is in one of a single-loop coil configuration, figure-8 coil configuration, or butterfly coil configuration, where the coil is smaller than the région of interest.

30. The system of anyone of embodiments 17-29, wherein the radio frequency transmit coil and the at least one gradient coil set are concentric about the région of interest.

31. The System of embodiment 27, wherein the electromagnet has a magnetic field strength from 10 mT to 1 T.

32. The System of anyone of embodiments 17-31, wherein the magnetic résonance imaging System is a single-sided magnetic résonance imaging System that comprises a magnetic résonance imaging scanner or a magnetic résonance imaging spectrometer.

33. A method of performing magnetic résonance imaging comprising: inputting patient parameters into a magnetic résonance imaging System, the System comprising: a housing comprising: a front surface, a permanent magnet for providing a static magnetic field, a radio frequency transmit coil, and a single-sided gradient coil set, wherein the radio frequency transmit coil and the single-sided gradient coil set are posîtîoned proximate to the front surface; an electromagnet; a radio frequency receive coil; and a power source, wherein the power source is configured to flow current through at least one of the radio frequency transmit coil, the singlesided gradient coil set, or the electromagnet to generate an electromagnetic field in a région of interest, wherein the région of interest résides outside the front surface; executing a patient positioning protocol comprising running at least one first scan; running at least one second scan; reviewing the at least one second scan; and determining at least one path for conducting a biopsy based on review of the at least one second sean.

34. The method of embodiment 33, wherein the radio frequency transmit coil and the single-sided gradient coil set are located on the front surface.

35. The method of anyone of embodiments 33-34, wherein the front surface is a concave surface.

36. The method of anyone of embodiments 33-35, wherein the permanent magnet has an aperture through center of the permanent magnet.

37. The method of anyone of embodiments 33-36, wherein the static magnetic field of the permanent magnet ranges from I mT to 1 T.

37-1. The method of anyone of embodiments 33-36, wherein the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

38. The method of anyone of embodiments 33-37, wherein the radio frequency transmît coil comprises a first ring and a second ring that are connected via one or more capacitors and/or one or more rangs.

39. The method of anyone of embodiments 33-38, wherein the radio frequency transmit coil is non-planar and oriented to partially surround the région of interest.

40. The method of anyone of embodiments 33-39, wherein the single-sided gradient coil set is non-planar and oriented to partially surround the région of interest, and wherein the single-sided gradient coil set is configured to project a magnetic field gradient to the région of interest.

41. The method of anyone of embodiments 33-40, wherein the single-sided gradient coil set comprises 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 located opposite each other about a center région of the single-sided gradient coil set.

42. The method of anyone of embodiments 33-41, wherein the single-sided gradient coil set has a rise time less than 10 ps.

43. The method of anyone of embodiments 33-42, wherein the electromagnet is configured to alter the static magnetic field of the permanent magnet within the région of interest.

44. The method of anyone of embodiments 33-43, wherein the electromagnet has a magnetic field strength from 10 mT to 1 T.

45. The method of anyone of embodiments 33-44, wherein the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest.

46. The method of anyone of embodiments 33-45, wherein the radio frequency receive coil is in one of a single-loop coil configuration, figure-8 coil configuration, or butterfiy coil configuration, wherein the coil is smaller than the région of interest.

47. The method of anyone of embodiments 33-46, wherein the radio frequency transmit coil and the single-sided gradient coil set are concentric about the région of interest.

48. The method of anyone of embodiments 33-47, wherein the magnetic résonance imaging System is a single-sided magnetic résonance imaging System that comprises a bore having an opening positîoned about a center région of tire front surface.

49. A method of performing magnetic résonance imaging comprising: inputting patient parameters into a magnetic résonance imaging System, the System comprising: a housing comprising; a concave front surface, a permanent magnet for providing a static magnetic field, a radio frequency transmit coil, and at least one gradient coil set, wherein the radio frequency transmit coil and the at least one gradient coil set are positîoned proximate to the concave front surface, wherein the radio frequency transmit coil and the at least one gradient coil set are configured to generate an electromagnetic field in a région of interest, wherein the région of interest résides outside the concave front surface; and a radio frequency receive coil for detecting signal m the région of interest; executing a patient positionîng protocol comprising running at least one first scan; running at least one second scan; reviewing the at least one second scan; and determining at least one path for conducting a biopsy based on review of the at least one second scan.

50. The method of embodiment 49, wherein the radio frequency transmit coil and the at least one gradient coil set are located on the concave front surface.

51. The method of anyone of embodiments 49-50, wherein the static magnetic field of the permanent magnet ranges from 1 mT to 1 T.

52. The method of anyone of embodiments 49-51, wherein the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

53. The method of anyone of embodiments 49-52, wherein the radio frequency transmit coil comprises a first ring and a second ring that are connected via one or more capacitors and/or one or more rangs.

54. The method of anyone of embodiments 49-53, wherein the radio frequency transmit coil is non-planar and oriented to partially surround the région of interest.

55. The method of anyone of embodiments 49-54, wherein the at least one gradient coil set is non-planar, single-sided, and oriented to partially surround the région of interest, and wherein the at least one gradient coil set is configured to project magnetic field gradient in the région of interest.

56. The method of anyone of embodiments 49-55, wherein the at least one gradient coil set comprises 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 located opposite each other about a center région of the at least one gradient coil set.

57. The method of anyone of embodiments 49-56, wherein the at least one gradient coil set has a rise time less than 10 ps.

58. The method of anyone of embodiments 49-57, wherein the permanent magnet has an aperture through center of the permanent magnet.

59. The method of anyone of embodiments 49-58, further comprising: an electromagnet configured to alter the static magnetic field of the permanent magnet within the région of interest.

60. The method of anyone of embodiments 49-59, wherein the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest.

61. The method of anyone of embodiments 49-60, wherein the radio frequency receive coil is in one of a single-loop coil configuration, figure-8 coil configuration, or butterfly coil configuration, where the coil is smaller than the région of interest.

62. The method of anyone of embodiments 49-61, wherein the radio frequency transmit coil and the at least one gradient coil set are concentric about the région of interest.

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

64. The method of anyone of embodiments 49-63, wherein the magnetic résonance imaging system is a single-sided magnetic résonance imaging system that comprises a magnetic résonance imaging scanner or a magnetic résonance imaging spectrometer.

65. A method of performing a scan on a magnetic résonance imaging system comprising: providing a housing comprising: a front surface, a permanent magnet for providing a static magnetic field, a radio frequency transmit coil, and a single-sided gradient coi! set, wherein the radio frequency transmit coil and the single-sided gradient coil set are positioned proximate to the front surface; providing an electromagnet; activating at least one of the radio frequency transmit coil, the single-sided gradient coil set, or the electromagnet to generate an electromagnetic field in a région of interest, wherein the région of interest résides outside the front surface; activating a radio frequency receive coil to obtain imaging data; reconstructing obtained imaging data to produce an output image for analysis; and displaying the output image for user review and annotation.

66. The method of embodiment 65, wherein the radio frequency transmit coil and the single-sided gradient coil set are located on the front surface.

67. The method of anyone of embodiments 65-66, wherein the front surface is a concave surface.

68. The method of anyone of embodiments 65-67, wherein the permanent magnet has an aperture through center of the permanent magnet.

69. The method of anyone of embodiments 65-68, wherein the static magnetic field of the permanent magnet ranges from 1 mT to 1 T.

69-1. The method of anyone of embodiments 65-68, wherein the static magnetic field of the permanent magnet ranges from 10 mT to 195 mT.

70. The method of anyone of embodiments 65-69, wherein the radio frequency transmit coil comprises a first ring and a second ring that are connected via one or more capacitors and/or one or more rangs.

71. The method of anyone of embodiments 65-70, wherein the radio frequency transmit coil is non-planar and oriented to partially surround the région of interest.

72. The method of anyone of embodiments 65-71, wherein the single-sided gradient coil set is non-planar and oriented to partially surround the région of interest, and wherein the single-sided gradient coil set is configured to project a magnetîc field gradient to the région of interest.

73. The method of anyone of embodiments 65-72, wherein the single-sided gradient coil set comprises one or more first spiral coils at a first position and one or more second spiral coîls at a second position, the first position and the second position being located opposite each other about a center région of the single-sided gradient coil set.

74. The method of anyone of embodiments 65-73, wherein the single-sided gradient coil set has a rise time less than 10 ps.

75. The method of anyone of embodiments 65-74, wherein the electromagnet is configured to alter the static magnetîc field of the permanent magnet within the région of interest.

76. The method of anyone of embodiments 65-75, wherein the electromagnet has a magnetîc field strength from 10 mT to 1 T.

77. The method of anyone of embodiments 65-76, wherein the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest.

78. The method of anyone of embodiments 65-77, wherein the radio frequency receive coil is in one of a single-loop coil configuration, figure-8 coil configuration, or butterfly coil configuration, wherein the coil is smaller than the région of interest.

79. The method of anyone of embodiments 65-78, wherein the radio frequency transmit coil and the single-sided gradient coil set are concentric about the région of interest.

80. The method of anyone of embodiments 65-79, wherein the magnetîc résonance imaging system is a single-sided magnetîc résonance imaging system that comprises a bore having an opening positioned about a center région of the front surface.

81. A method of performing a scan on a magnetîc résonance imaging system comprising: providing a housing comprising: a concave front surface, a pennanent magnet for providing a static magnetîc field, a radio frequency transmît coil, and at least one gradient coil set, wherein the radio frequency transmit coil and the ai least one gradient coil set are positioned proximate to the front surface; activating at least one of the radio frequency transmit coil and the at least one gradient coil set to generate an electromagnetic field in a région of interest, wherein the région of interest résides outside the concave front surface; activating a radio frequency receive coil to obtaîn imaging data; reconstructing obtained imaging data to produce an output image for analysis; and displaying the output image for user review and annotation.

82. The method of embodiment 81, wherein the radio frequency transmit coil and the at least one gradient coil set are located on the concave front surface.

83. The method of anyone of embodiments 81-82, wherein the static magnetic field of the pennanent magnet ranges from 1 mT to 1 T.

84. The method of anyone of embodiments 81-83, wherein the static magnetic field of the pennanent magnet ranges from 10 mT to 195 mT.

85. The method of anyone of embodiments 81-84, wherein the radio frequency transmit coil comprises a first ring and a second ring that are connected via one or more capacitors and/or one or more rungs.

86. The method of anyone of embodiments 81-85, wherein the radio frequency transmit coil is non-planar and orîented to partially surround the région of interest.

87. The method of anyone of embodiments 81-86, wherein the at least one gradient coil set is non-planar, single-sided, and oriented to partially surround the région of interest, and wherein the at least one gradient coil set is configured to project magnetic field gradient in the région of interest.

88. The method of anyone of embodiments 81-87, wherein the at least one gradient coil set comprises 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 located opposite each other about a center région of the at least one gradient coil set.

89. The method of anyone of embodiments 81-88, wherein the at least one gradient coil set has a rise time less than 10 gs.

90. The method of anyone of embodiments 81-89, wherein the permanent magnet has an aperture through center of the pennanent magnet.

91. The method of anyone of embodiments 81 -90, further comprising: an electromagnet configured to alter the static magnetic field of the pennanent magnet within the région of interest.

92. The method of anyone of embodiments 81-91, wherein the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest.

93. The method of anyone of embodiments 81-92, wherein the radio frequency receive coil is in one of a single-loop coil configuration, figure-8 coil configuration, or butterfly coil configuration, where the coil is smaller than the région of interest.

94. The method of anyone of embodiments 81-93, wherein the radio frequency transmit coil and the at least one gradient coil set are concentric about the région of interest.

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

96. The method of anyone of embodiments 81-95, wherein the magnetic résonance imaging system is a single-sided magnetic résonance imaging system that comprises a magnetic 5 résonance imaging scanner or a magnetic résonance imaging spectrometer.

Whîle this spécification coniains many spécifie implémentation details, these should not be construed as limitations on the scope of any embodiments or of what may be claimed, but rather as descriptions of features spécifie to particular implémentations of particular embodiments. Certain features that are described in this spécification in the context of separate 10 implémentations can also be implemented in combination in a single implémentation.

Conversely, various features that are described in the context of a single implémentation can also be implemented in multiple implémentations separately or in any suitable sub-combination.

Moreover, although features may be described above as acting in certain combinations and even initially claimed as such, one or more features from a claimed combination can in some cases be 15 excised from the combination, and the claimed combination may be directed to a subcombination or variation of a sub-combination.

Similarly, while operations are depicted in the drawings in a particular order, this should not be understood as requiring that such operations be performed in the particular order shown or in sequential order, or that ail illustrated operations be performed, to achîeve désirable results. In 20 certain circumstances, multitasking and parallel processing may be advantageous. Moreover, the séparation of various System components in the implémentations described above should not be understood as requiring such séparation in ail implémentations, and it should be understood that the described program components and Systems can generally be integrated together in a single software product or packaged into multiple software products.

Référencés to “or” may be construed as inclusive so that any tenus described using “or” may indicate any of a single, more than one, and ail of the described tenus. The labels “first,” “second,” “third,” and so forth are not necessarily meant to indicate an ordering and are generally used merely to distinguish between like or similar items or éléments.

Various modifications to the implémentations described in this disclosure may be 30 readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other implémentations without departing from the spirit or scope of this disclosure. Thus, the claims are not intended to be limited to the implémentations shown herein, but are to be accorded the widest scope consistent with this disclosure, the principles and the novel features disclosed herein.

Claims

1. A magnetic résonance imaging system comprising:

a housing comprising:

a front surface, a permanent magnet for providing a static magnetic fieid, a radio frequency transmit coil, and a single-sided gradient coil set, wherein the radio frequency transmit coil and the single-sided gradient coil set are positioned proximate to the front surface;

an electromagnet;

a radio frequency receive coil; and a power source, wherein the power source is confîgured to flow current through at least one of the radio frequency transmit coil, the single-sided gradient coil set, or the electromagnet to generate an electromagnetic fieid in a région of interest, wherein the région of interest résides outside the front surface.

2. The system of claim 1, wherein the radio frequency transmit coil and the single-sided gradient coil set are located on the front surface.

3. The System of claim 1, wherein the front surface is a concave surface.

4. The system of claim 1, wherein the permanent magnet has an aperture through center of the permanent magnet.

2®

5. The system of claim 1, wherein the static magnetic fieid of the permanent magnet ranges from 1 mT to 1 T.

6. The system of claim 1, wherein the radio frequency transmit coil comprises a first ring and a second ring that are connected via one or more capacitors and/or one or more rungs.

7. The system of claim 1, wherein the radio frequency transmit coil is non-planar and

25 oriented to partially surround the région of interest.

8. The system of claim 1, wherein the single-sided gradient coil set is non-planar and oriented to partially surround the région of interest, and wherein the single-sided gradient coil set is confîgured to project a magnetic fieid gradient to the région of interest.

9. The system of claim 1, wherein the single-sided gradient coil set comprises one or more first spiral colis at a first position and one or more second spiral coils at a second position, the first position and the second position being located opposite each other about a center région of the single-sided gradient coil set.

10. The system of claim 1, wherein the single-sided gradient coil set has a rise time less than 10 ps.

11. The system of claim 1, wherein the electromagnet is configured to alter the static magnetic field of the permanent magnet within the région of interest.

12. The system of claim 1, wherein the electromagnet has a magnetic field strength from 10 mT to 1 T.

13. The System of claim 1, wherein the radio frequency receive coil is a flexible coil configured to be affixed to an anatomical portion of a patient for imaging within the région of interest.

14. The system of claim 1, wherein the radio frequency receive coil is in one of a single-loop coil configuration, figure-8 coil configuration, or butterfly coil configuration, wherein the coil is smaller than the région of interest.

15. The System of claim 1, wherein the radio frequency transmit coil and the single-sided gradient coil set are concentric about the région of interest.

16. The System of claim 1, wherein the magnetic résonance imaging system is a singlesided magnetic résonance imaging system that comprises a bore having an opening positioned about a center région of the front surface.

17. A magnetic résonance imaging system comprising:

a housing comprising:

a concave front surface, a permanent magnet for providîng a static magnetic field, a radio frequency transmit coil, and at least one gradient coil set, wherein the radio frequency transmit coil and the at least one gradient coil set are positioned proximate to the concave front surface, wherein the radio frequency transmit coil and the at least one gradient coil set are configured to generate an electromagnetic fieid in a région of interest, wherein the région of interest résides outside the concave front surface; and a radio frequency receive coil for detecting signal in the région of interest.

18. The system of claim 17, wherein the radio frequency transmit coil and the at least one gradient coil set are. located on the concave front surface.

19. The system of claim 17, wherein the static magnetic fieid of the permanent magnet ranges from 1 mT to 1 T.

20. The system of claim 17, wherein the static magnetic fieid of the permanent magnet ranges from 10 mT to 195 mT.

21. A method of performing a scan on a magnetic résonance imaging System comprising: provîding a housing comprising:

a front surface, a permanent magnet for provîding a static magnetic fieid, a radio frequency transmit coil, and a single-sided gradient coil set, wherein the radio frequency transmit coil and the single-sided gradient coil set are positioned proximate to the front surface;

provîding an electromagnet;

activating at least one of the radio frequency transmit coil, the single-sided gradient coil set, or the electromagnet to generate an electromagnetic fieid in a région of interest, wherein the région of interest resides outside the front surface;

activating a radio frequency receive coil to obtain imaging data;

reconstructing obtained imaging data to produce an output image for analysis; and displaying the output image for user review and annotation.

22. A method of performing a scan on a magnetic résonance imaging system comprising: provîding a housing comprising:

a concave front surface, a permanent magnet for provîding a static magnetic fieid, a radio frequency transmit coil, and at least one gradient coil set, wherein the radio frequency transmit coil and the at least one gradient coil set are positioned proximate to the front surface;

activating at least one of the radio frequency transmit coil and the at least one gradient coil set to generate an electromagnetic fieid in a région of interest, wherein the région of interest résides outside the concave front surface;

activating a radio frequency receive coil to obtain imaging data;