WO2022016029A1 - Système d'irm portable à champ non homogène - Google Patents

Système d'irm portable à champ non homogène Download PDF

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Publication number
WO2022016029A1
WO2022016029A1 PCT/US2021/041916 US2021041916W WO2022016029A1 WO 2022016029 A1 WO2022016029 A1 WO 2022016029A1 US 2021041916 W US2021041916 W US 2021041916W WO 2022016029 A1 WO2022016029 A1 WO 2022016029A1
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WO
WIPO (PCT)
Prior art keywords
coils
magnetic field
mri system
portable mri
coil
Prior art date
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Ceased
Application number
PCT/US2021/041916
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English (en)
Inventor
Xun Jia
Robert Timmerman
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
University of Texas System
University of Texas at Austin
Original Assignee
University of Texas System
University of Texas at Austin
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Publication of WO2022016029A1 publication Critical patent/WO2022016029A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/445—MR involving a non-standard magnetic field B0, e.g. of low magnitude as in the earth's magnetic field or in nanoTesla spectroscopy, comprising a polarizing magnetic field for pre-polarisation, B0 with a temporal variation of its magnitude or direction such as field cycling of B0 or rotation of the direction of B0, or spatially inhomogeneous B0 like in fringe-field MR or in stray-field imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
    • A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
    • G01R33/3802—Manufacture or installation of magnet assemblies; Additional hardware for transportation or installation of the magnet assembly or for providing mechanical support to components of the magnet assembly
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
    • G01R33/3808—Magnet assemblies for single-sided MR wherein the magnet assembly is located on one side of a subject only; Magnet assemblies for inside-out MR, e.g. for MR in a borehole or in a blood vessel, or magnet assemblies for fringe-field MR
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
    • G01R33/383—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using permanent magnets
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00—Arrangements or instruments for measuring magnetic variables
    • G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
    • G01R33/48—NMR imaging systems
    • G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
    • G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
    • G01R33/565—Correction of image distortions, e.g. due to magnetic field inhomogeneities
    • G01R33/56563—Correction of image distortions, e.g. due to magnetic field inhomogeneities caused by a distortion of the main magnetic field B0, e.g. temporal variation of the magnitude or spatial inhomogeneity of B0

Definitions

  • the present disclosure generally relates to a portable magnetic resonance imaging system and, more specifically, to a portable inhomogeneous-field magnetic resonance imaging system.
  • Magnetic resonance imaging is one of the major medical imaging modalities for disease diagnosis and image guidance of therapeutic procedures.
  • MRI systems are often bulky and expensive.
  • facilities that house these MRI systems typically require a lot of space for the system itself, and also requires patients to physically come to the location in which the MRI system is located.
  • Such a stationary system suffers from a series of limitations, most notably of which is the difficulty in travelling with an injured to sick patient from their respective care room to a location in the care facility where the MRI system is located.
  • a portable magnetic resonance imaging (MRI) system includes a mechanical arm and a scanner.
  • the mechanical arm is configurable between a plurality of positions.
  • the scanner is coupled to the mechanical arm.
  • the scanner is configurable between a plurality of positions.
  • the scanner includes a magnet, one or more gradient coils, and one or more radio frequency (RF) coils.
  • the magnet is configured to generate an inhomogeneous magnetic field.
  • the one or more gradient coils are configured to generate one or more magnetic fields to distort the inhomogeneous magnetic field.
  • the one or more RF coils are configured to send and receive RF electromagnetic wave for imaging purposes.
  • the portable MRI system further includes a structure and an electronic motor system.
  • the structure defines an interior volume.
  • the electronic motor system is configured to direct the portable MRI system to a location.
  • the structure further includes one or more wheels coupled thereto.
  • the one or more wheels are controlled by the electronic motor system.
  • the portable MRI system includes a controller disposed in an interior volume of the structure. The controller is configured to control an amount of power delivered to at least one of the one or more gradient coils or the one or more RF coils.
  • a first gradient coil of the one or more gradient coils is configured to generate a first spatially varying magnetic field along a first direction.
  • a second gradient coil of the one or more gradient coils is configured to generate a second spatially varying magnetic field along a second direction.
  • magnet is configured to generate a third spatially varying magnetic field along a third direction.
  • the one or more RF coils are configured to facilitate MRI data acquisition by performing a number of two-dimensional scans, with varying RF frequencies.
  • the portable MRI system may include RF shielding.
  • Figure 1 A is a block diagram illustrating a portable inhomogeneous-field MRI system, according to example embodiments.
  • Figure IB is a block diagram illustrating a scanner of the portable inhomogeneous-field MRI system of Figure 1A, according to example embodiments.
  • Figure 2 illustrates a chart representing an illustration of image reconstruction on a set of two-dimensional surfaces, according to example embodiments
  • Figure 3A is a block diagram illustrating scanner positioned in a first exemplary position, according to example embodiments.
  • Figure 3B is a block diagram illustrating scanner positioned in a second exemplary position, according to example embodiments.
  • Figure 4 is a flow diagram illustrating a method of operating system, according to example embodiments
  • Figure 5A illustrates an example system configuration for implementing various embodiments of the present technology, according to example embodiments.
  • Figure 5B illustrates an example system configuration for implementing various embodiments of the present technology, according to example embodiments.
  • Figure 6A illustrates an exemplary view magnet assembly that utilize permanent magnets to assemble the main magnet, according to example embodiments.
  • Figure 6B illustrates an exemplary view magnet assembly, according to example embodiments.
  • Magnetic resonance imaging is one of the major medical imaging modalities for disease diagnosis and image guidance of therapeutic procedures, e.g., image guided radiation therapy or image guided surgery.
  • existing MRI technology mostly employs a highly homogenous high magnetic field.
  • inhomogeneous-field MRI technology, low field strength, and small field of view (FOV) are typically not favored in diagnostic radiology due to the low image quality and small FOV associated therewith.
  • Homogeneity/inhomogeneity may refer to the uniformity of a magnetic field generated by the MRI system.
  • Existing MRI technology suffers from a variety of limitations. For example, the cost of system development and manufacture of traditional MRIs is very high. Existing MRI technology also takes up a large footprint due to the weight and large size of the MRI scanner. This results in the MRI scanner impeding its application in certain scenarios, such as, but not limited to, point-of-care imaging to scan a patient without moving the patient to the scanner, or when using MRI scanners in an operation room where space is limited and electromagnetic or geometric interference with other medical devices is a concern.
  • FIG. 1A is a block diagram illustrating a portable inhomogeneous field MRI system 100 (hereinafter “system 100”), according to example embodiments.
  • system 100 may include at least a body 102.
  • Body 102 may include a mechanical arm 104, a scanner 106, and a controller 108.
  • Body 102 may be adapted for movement of system 100 to a location at which an MRI is needed.
  • body 102 may include an electronic motor system 110 and wheels 112.
  • Electronic motor system 110 may be configured to direct system 100 to a desired location.
  • electronic motor system 110 may be responsive to a remote (or controller) that instructs electronic motor system 110 where to navigate.
  • Electronic motor system 110 may be in communication with wheels 112. For example, when remote or controller instructs electronic motor system 110 to navigate to a location, electronic motor system 110 may instruct wheels 112 to turn a desired direction in order to navigate to a specific location.
  • Electronic motor system 110 may include a battery system, configured to provide power thereto.
  • body 102 may only include wheels 112.
  • system 100 may be moved manually, relying on wheels 112.
  • mechanical arm 104 may be coupled with scanner 106.
  • Mechanical arm 104 may be movable among a variety of positions. In this manner, operators can position system 100 such that target areas of a patient may be imaged.
  • mechanical arm 104 may be physically moved into a variety of positions by an operator.
  • mechanical arm 104 may be in communication with electronic motor system 110.
  • electronic motor system 110 may be configured to move mechanical arm 104 into a variety of positions based on instructions from controller 108 or remote.
  • scanner 106 may be moved into a desired position with respect to the patient.
  • mechanical arm 104 may be further configured to tilt or rotate scanner 106 at various angles with respect to the patient. In this manner, mechanical arm 104 may position scanner 106 to ensure that scanner 106 sufficiently images a patient.
  • Scanner 106 may include main magnet 114, one or more gradient coils 116, and one or more radio frequency (RF) coils 118.
  • Main magnet 114 may be configured to generate an inhomogeneous magnetic field about scanner 106.
  • the inhomogeneous magnetic field may be generated such that the magnetic field may decay when moving away from main magnet 114 (e.g., in the positive z-direction).
  • Magnet 114 may be representative of a single magnet or multiple magnets.
  • magnet 114 may be representative of a simple magnet design, opposed to more complex magnet designs utilized to achieve field homogeneity.
  • system 100 may use other components to generate an inhomogeneous magnetic field.
  • system 100 may include one or more of a resistive magnet, a superconducting magnet, or other components to generate an inhomogeneous magnetic field.
  • FIG. 6A and 6B illustrates exemplary views magnet assembly 600, according to example embodiments.
  • Magnet assembly 600 may be an exemplary arrangement of magnets configured to act as main magnet 114.
  • magnet assembly 600 may include a plurality of permanent magnets 602.
  • Plurality of permanent magnets 602 may be placed on a curved surface with their orientations and positions determined by solving an optimization problem to achieve desired magnetic field properties in the imaging regions of interest.
  • the curved shape may allow for placement of magnet 114 on the patient’ body surface.
  • Figures 6A and 6B provide an exemplary magnet assembly 600, those skilled in the art understand that, when designing magnet 114, other considerations, such as reducing a fringe field to avoid electromagnetic interference with surrounding other medical devices, may be taken into considerations.
  • main magnet 114 may take on other forms.
  • main magnet 114 may be installed into a patient couch or support.
  • gradient coils 116 may be positioned adjacent to main magnet 114.
  • Gradient coils can be designed using various methods, such as, target field method, on specific given surfaces, e.g. the front surface of the main magnet 114.
  • Gradient coils 116 may be positioned between main magnet 114 and a target patient.
  • Gradient coils 116 may be representative of two or more gradient coils configured to create spatially varying magnetic fields along the x- and y-directions (or other non-trivial directions) for spatial encoding.
  • spatial encoding along the third axis may be achieved in system 100 using the inhomogeneous magnetic field created by main magnet 114.
  • one gradient coil 116 can generate a spatially dependent magnetic field, based on which location information can be inferred in MR imaging process.
  • Different techniques may be used to encode three directions (x-, y-, or z- directions) for three-dimensional imaging purpose.
  • gradient coils 116 may include at least one coil configured to encode one of three directions (e.g., one of the x-, y-, or z-direction).
  • RF coils 118 may be configured to send and receive RF electromagnetic waves for MRI data acquisition.
  • RF coils 118 may be configured in standard MRI coil forms, e.g. body coil, surface coil, birdcage coil, or coil array. In some embodiments, it is also possible to have separate transmit and receive RF coils 118 to position the receive RF coil closer to the imaging region of interest to increase signal to noise ratio.
  • each RF coil 118 may cover a narrow bandwidth.
  • RF coils 118 may cover a wide bandwidth needed to scan the imaging field of view. The use of narrow bandwidth for each RF coil 118 may help reducing image noise.
  • MRI data acquisition may be achieved by performing a number of two-dimensional scans, each with a given RF frequency.
  • Figure 2 illustrates a chart 200 representing an illustration of image reconstruction on a set of two-dimensional surfaces, according to example embodiments.
  • image pixel values at the intersection between vertical lines 202 and iso-magnetic field surface 204 may be reconstructed by controller 108 or a computing system in communication with controller 108. Repeating this procedure for a different frequency f 0 may yield a set of images defined on a set of iso-magnetic field surfaces.
  • controller 108 or a computing system in communication with controller 108 may apply numerical interpolation to obtain a volumetric image defined by a cartesian coordinate for clinical use.
  • main magnet 114 may generate an inhomogeneous magnetic field extending from the front surface of scanner 106.
  • the magnetic field may decay as it moves away from a front surface of main magnet 114 (e.g., positive z-direction).
  • the magnetic field may be rotationally symmetric in space, about the z-axis.
  • Such general principles may not be limited to rotationally a symmetric magnet and magnetic field.
  • system 100 may further include RF shielding (not shown).
  • RF shielding may be used to reduce interference of RF signals in the patient room to the RF acquisition system of system 100.
  • standard RF shielding techniques may be applied, such as a copper sheet (or other metal sheets) to block interfering RF signals from the RF coil and patient body.
  • system 100 may further include magnetic shielding (not shown). Magnetic shielding may be applied to shield the magnetic field of scanner 106 from reaching the environment, thus reducing its impact on other nearby medical devices. Magnetic shielding may be achieved by using magnetic shielding materials, e.g. mu-metal, positioned around scanner 106 and the patient body.
  • Controller 108 may be configured to control electronic motor system 110 and an amount of power provided to one or more of gradient coils 116 and/or RF coils 118. The power needed by the gradient coils and RF coils for imaging purpose may be obtained via standard power supply system. As illustrated, controller 108 may be in communication with computing system 150.
  • Computing system 150 may be a separate computer system 150 in communication with controller 108.
  • Computing system 150 may be an option component.
  • all processes performed by computing system 150 may be performed by controller 108.
  • Computing system 150 may be configured to reconstruct an image on a surface of an object.
  • computing system 150 may define a reconstruction surface given the RF f 0 signal and magnetic field B 0 .
  • controller 108 may define a two-dimensional surface in space.
  • Computing system 150 may reconstruct the image based on the defined reconstruction surface and an acquired RF signal. Additional operations performed by computing system 150 and/or controller 108 may be found below in conjunction with Figure 4.
  • FIG. IB is a block diagram illustrating scanner 106, according to exemplary embodiments.
  • scanner 106 may include main magnet 114 and gradient coils 116. Coordinates are shown on top of scanner 106 for illustration purposes.
  • Figure 3 A is a block diagram illustrating scanner 106 positioned in a first exemplary position, according to example embodiments. As shown, scanner 106 may be positioned directly over a sternum of patient 302.
  • Figure 3B is a block diagram illustrating scanner 106 positioned in a second exemplary position, according to example embodiments.
  • scanner 106 may be positioned adjacent to patient 302.
  • mechanical arm 104 may move scanner 106 away from first position illustrated in Figure 3A, to a second position.
  • moving scanner from the first position to the second position may include tilting scanner 106 at an angle with respect to the surface of the patient.
  • Figure 4 is a flow diagram illustrating a method 400 of operating system 100, according to example embodiments. Method 400 may begin at step 402.
  • system 100 may transmit an RF signal.
  • controller 108 may transmit an RF signal having a frequency, f 0 .
  • the signal may be sent through an RF coil 118.
  • RF signal may induce magnetic nuclear resonance in the imaging region.
  • system 100 may input the known magnetic field distribution B 0 to the system.
  • the 3D distribution of the field B 0 may depend on the specific magnet design and construction. For a given magnet, the distribution can be known, for example by performing a measurement.
  • system 100 may define a reconstruction surface given the RF f 0 signal and magnetic field B 0 .
  • controller 108 may define a two-dimensional surface in space.
  • system 100 may acquire an RF signal.
  • the RF signal in the imaging region after the resonance may be received by the RF coil 118.
  • system 100 may reconstruct an image on a surface of an object given the defined reconstruction surface and the acquired RF signal. For example, once the RF signal is sent to the field of view, it may excite spins on this two-dimensional surface.
  • the signal received by RF coil 118 may contain excitation information in this surface, which can be used to reconstruct the image of this surface. For example, image pixel values at the intersection between the vertical lines and an iso-magnetic field surface can be reconstructed.
  • system 100 may reconstruct an image using a Fourier transform based method.
  • system 100 may reconstruct an image using advance iterative reconstruction methods.
  • each scan with frequency f 0 may provide an image on one surface.
  • the scan may be repeated with different frequencies to acquire images for different surfaces.
  • system 100 may determine whether all frequencies have been considered. If, at step, 412, system determines that not all frequencies were considered, then method 400 reverts to step 402 and a new f 0 is selected. If, however, at step 412, system 100 determines that all frequencies were considered, then method 400 proceeds to step 414.
  • Figure 5A illustrates a system bus computing system architecture 500, according to example embodiments. One or more components of system 500 may be in electrical communication with each other using a bus 505.
  • System 500 may include a processor (e.g., one or more CPUs, GPUs or other types of processors) 510 and a system bus 505 that couples various system components including the system memory 515, such as read only memory (ROM) 520 and random access memory (RAM) 525, to processor 510.
  • System 500 can include a cache of high-speed memory connected directly with, in close proximity to, or integrated as part of processor 510.
  • System 500 can copy data from memory 515 and/or storage device 530 to cache 512 for quick access by processor 510. In this way, cache 512 may provide a performance boost that avoids processor 510 delays while waiting for data.
  • These and other modules can control or be configured to control processor 510 to perform various actions.
  • Other system memory 515 may be available for use as well.
  • Memory 515 may include multiple different types of memory with different performance characteristics.
  • Processor 510 may be representative of a single processor or multiple processors.
  • Processor 510 can include one or more of a general purpose processor or a hardware module or software module, such as service 1 532, service 2 534, and service 3 536 stored in storage device 530, configured to control processor 510, as well as a special-purpose processor where software instructions are incorporated into the actual processor design.
  • Processor 510 may essentially be a completely self-contained computing system, containing multiple cores or processors, a bus, memory controller, cache, etc.
  • a multi-core processor may be symmetric or asymmetric.
  • an input device 545 which can be any number of input mechanisms, such as a microphone for speech, a touch-sensitive screen for gesture or graphical input, keyboard, mouse, motion input, speech and so forth.
  • An output device 535 can also be one or more of a number of output mechanisms known to those of skill in the art.
  • multimodal systems can enable a user to provide multiple types of input to communicate with computing device 500.
  • Communications interface 540 can generally govern and manage the user input and system output. There is no restriction on operating on any particular hardware arrangement and therefore the basic features here may easily be substituted for improved hardware or firmware arrangements as they are developed.
  • Storage device 530 may be a non-volatile memory and can be a hard disk or other types of computer readable media that can store data that are accessible by a computer, such as magnetic cassettes, flash memory cards, solid state memory devices, digital versatile disks, cartridges, random access memories (RAMs) 525, read only memory (ROM) 520, and hybrids thereof.
  • RAMs random access memories
  • ROM read only memory
  • Storage device 530 can include services 532, 534, and 536 for controlling the processor 510. Other hardware or software modules are contemplated. Storage device 530 can be connected to system bus 505. In one aspect, a hardware module that performs a particular function can include the software component stored in a computer-readable medium in connection with the necessary hardware components, such as processor 510, bus 505, display 535, and so forth, to carry out the function.
  • Figure 5B illustrates a computer system 550 having a chipset architecture that can be used in operating system 100.
  • Computer system 550 may be an example of computer hardware, software, and firmware that can be used to implement the disclosed technology.
  • System 550 can include one or more processors 555, representative of any number of physically and/or logically distinct resources capable of executing software, firmware, and hardware configured to perform identified computations.
  • processors 555 can communicate with a chipset 560 that can control input to and output from one or more processors 555.
  • chipset 560 outputs information to output 565, such as a display, and can read and write information to storage device 570, which can include magnetic media, and solid state media, for example.
  • Chipset 560 can also read data from and write data to RAM 575.
  • a bridge 580 for interfacing with a variety of user interface components 585 can be provided for interfacing with chipset 560.
  • Such user interface components 585 can include a keyboard, a microphone, touch detection and processing circuitry, a pointing device, such as a mouse, and so on.
  • inputs to system 550 can come from any of a variety of sources, machine generated and/or human generated.
  • Chipset 560 can also interface with one or more communication interfaces 590 that can have different physical interfaces.
  • Such communication interfaces can include interfaces for wired and wireless local area networks, for broadband wireless networks, as well as personal area networks.
  • Some applications of the methods for generating, displaying, and using the GUI disclosed herein can include receiving ordered datasets over the physical interface or be generated by the machine itself by one or more processors 555 analyzing data stored in storage 570 or 575. Further, the machine can receive inputs from a user through user interface components 585 and execute appropriate functions, such as browsing functions by interpreting these inputs using one or more processors 555.
  • example systems 500 and 550 can have more than one processor 510 or be part of a group or cluster of computing devices networked together to provide greater processing capability.
  • Illustrative computer-readable storage media include, but are not limited to: (i) non-writable storage media (e.g., read-only memory (ROM) devices within a computer, such as CD-ROM disks readably by a CD-ROM drive, flash memory, ROM chips, or any type of solid-state non-volatile memory) on which information is permanently stored; and (ii) writable storage media (e.g., floppy disks within a diskette drive or hard-disk drive or any type of solid state random-access memory) on which alterable information is stored.
  • ROM read-only memory
  • writable storage media e.g., floppy disks within a diskette drive or hard-disk drive or any type of solid state random-access memory

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Abstract

L'invention concerne un système d'imagerie par résonance magnétique (IRM) portable. Le système IRM portable comprend un bras mécanique et un scanner. Le bras mécanique peut être configuré entre une pluralité de positions. Le scanner est couplé au bras mécanique. Le scanner peut être configuré entre une pluralité de positions. Le scanner comprend un aimant, une ou plusieurs bobines de gradient et une ou plusieurs bobines radiofréquence (RF). L'aimant est configuré pour générer un champ magnétique non homogène. L'au moins une bobine de gradient est configurée pour générer un ou plusieurs champs magnétiques afin de déformer le champ magnétique non homogène. L'au moins une bobine RF est configurée pour envoyer et recevoir une onde électromagnétique RF à des fins d'imagerie.
PCT/US2021/041916 2020-07-16 2021-07-16 Système d'irm portable à champ non homogène Ceased WO2022016029A1 (fr)

Applications Claiming Priority (2)

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US202063052650P 2020-07-16 2020-07-16
US63/052,650 2020-07-16

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WO2022016029A1 true WO2022016029A1 (fr) 2022-01-20

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Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20010009974A1 (en) * 1998-07-24 2001-07-26 Daniel Reisfeld Three-dimensional reconstruction of intrabody organs
US20150217136A1 (en) * 2012-07-27 2015-08-06 University Health Network Radiotherapy system integrating a radiation source with a magnetic resonance imaging apparatus with movable magnet components
US20180143274A1 (en) * 2016-11-22 2018-05-24 Hyperfine Research, Inc. Low-field magnetic resonance imaging methods and apparatus

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20010009974A1 (en) * 1998-07-24 2001-07-26 Daniel Reisfeld Three-dimensional reconstruction of intrabody organs
US20150217136A1 (en) * 2012-07-27 2015-08-06 University Health Network Radiotherapy system integrating a radiation source with a magnetic resonance imaging apparatus with movable magnet components
US20180143274A1 (en) * 2016-11-22 2018-05-24 Hyperfine Research, Inc. Low-field magnetic resonance imaging methods and apparatus

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