CN117452305A - Distributed gradient magnetic field coil and movable magnetic resonance imaging device - Google Patents
Distributed gradient magnetic field coil and movable magnetic resonance imaging device Download PDFInfo
- Publication number
- CN117452305A CN117452305A CN202311357520.3A CN202311357520A CN117452305A CN 117452305 A CN117452305 A CN 117452305A CN 202311357520 A CN202311357520 A CN 202311357520A CN 117452305 A CN117452305 A CN 117452305A
- Authority
- CN
- China
- Prior art keywords
- power supply
- resonance imaging
- magnetic field
- magnetic resonance
- coil
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 238000002595 magnetic resonance imaging Methods 0.000 title claims abstract description 57
- XEEYBQQBJWHFJM-UHFFFAOYSA-N Iron Chemical compound [Fe] XEEYBQQBJWHFJM-UHFFFAOYSA-N 0.000 claims abstract description 28
- 229910052742 iron Inorganic materials 0.000 claims abstract description 14
- 238000003384 imaging method Methods 0.000 claims abstract description 10
- 230000002401 inhibitory effect Effects 0.000 claims abstract description 4
- 238000001208 nuclear magnetic resonance pulse sequence Methods 0.000 claims description 9
- 238000012545 processing Methods 0.000 claims description 7
- UFHFLCQGNIYNRP-UHFFFAOYSA-N Hydrogen Chemical compound [H][H] UFHFLCQGNIYNRP-UHFFFAOYSA-N 0.000 claims description 4
- 229910052739 hydrogen Inorganic materials 0.000 claims description 4
- 239000001257 hydrogen Substances 0.000 claims description 4
- 230000009286 beneficial effect Effects 0.000 abstract description 3
- 230000000694 effects Effects 0.000 abstract description 3
- 238000012360 testing method Methods 0.000 abstract description 3
- 238000010586 diagram Methods 0.000 description 4
- 230000000670 limiting effect Effects 0.000 description 3
- 238000000034 method Methods 0.000 description 3
- 238000004804 winding Methods 0.000 description 3
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 238000012984 biological imaging Methods 0.000 description 1
- 238000004891 communication Methods 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 230000002441 reversible effect Effects 0.000 description 1
- 230000003068 static effect Effects 0.000 description 1
- 238000006467 substitution reaction Methods 0.000 description 1
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]
- G01R33/48—NMR imaging systems
- G01R33/58—Calibration of imaging systems, e.g. using test probes, Phantoms; Calibration objects or fiducial markers such as active or passive RF coils surrounding an MR active material
-
- 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
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
Landscapes
- Physics & Mathematics (AREA)
- Condensed Matter Physics & Semiconductors (AREA)
- General Physics & Mathematics (AREA)
- High Energy & Nuclear Physics (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
The invention provides a distributed gradient magnetic field coil and a movable magnetic resonance imaging device, which comprises: a magnetic pole; configured to generate a strong constant magnetic field; the horizontal iron yoke is arranged on the lower end face of the magnetic pole; the main longitudinal gradient coil is arranged on the upper end face of the magnetic pole; the second longitudinal gradient coil is fixedly arranged on the side wall of the magnetic pole and is used for inhibiting eddy currents generated by the main longitudinal gradient coil in the iron yoke; the main longitudinal gradient coil and the second longitudinal gradient coil jointly generate a gradient magnetic field in the Y-axis direction in the MRI imaging space, so that the spatial coding of signals in the Y-axis direction is realized. The invention has the beneficial effects that: the second longitudinal gradient coil is used for inhibiting eddy current generated by the main longitudinal gradient coil in the iron yoke, generating a required gradient magnetic field, and simultaneously, has better magnetic leakage control of the gradient magnetic field, improves the magnetic resonance imaging effect and improves the accuracy of the test result.
Description
Technical Field
The invention belongs to the technical field of magnetic resonance imaging, and particularly relates to a distributed gradient magnetic field coil and a movable magnetic resonance imaging device.
Background
Magnetic Resonance Imaging (MRI) provides an attractive imaging mode for biological imaging, and can generate non-invasive imaging, so that the power supply system can provide the power required by imaging, when the magnetic resonance imaging system works, a human body is placed in a strong static magnetic field, the nuclei of a part of the human body are excited by transmitting radio frequency pulses to the human body, after the radio frequency field is removed, the excited nuclei radiate radio frequency signals which are received by an antenna, and when a gradient magnetic field is added in the process, the spatial distribution information of the human body can be obtained through the radio frequency signals, so that a two-dimensional or three-dimensional image of the human body can be reconstructed.
The double-plane gradient coil of the traditional magnetic resonance imaging device consists of two gradient plates, which are respectively arranged near the upper pole face and the lower pole face of the upper magnet, and a required gradient magnetic field is generated in the space between the two gradient plates.
Disclosure of Invention
In view of the above, the present invention is directed to a distributed gradient magnetic field coil and a mobile magnetic resonance imaging apparatus, so as to solve at least one of the above-mentioned problems.
In order to achieve the above purpose, the technical scheme of the invention is realized as follows:
the first aspect of the invention provides a distributed gradient magnetic field coil comprising:
a magnetic pole; configured to generate a strong constant magnetic field;
the horizontal iron yoke is arranged on the lower end face of the magnetic pole;
the main longitudinal gradient coil is arranged on the upper end face of the magnetic pole;
the second longitudinal gradient coil is fixedly arranged on the side wall of the magnetic pole and is used for inhibiting eddy currents generated by the main longitudinal gradient coil in the iron yoke;
the main longitudinal gradient coil and the second longitudinal gradient coil jointly generate a gradient magnetic field in the Y-axis direction in an MRI imaging space, so that spatial encoding of signals in the Y-axis direction is realized.
Further, the distributed gradient magnetic field coil further includes:
and the transverse gradient coil generates a gradient magnetic field in the X-axis direction in the MRI imaging space, so that the spatial coding of signals in the X-axis direction is realized.
The radio frequency coil is used for generating radio frequency pulses, exciting hydrogen atomic nuclei in the sample and receiving radio frequency signals emitted by the radio frequency coils.
A second aspect of the invention provides a mobile magnetic resonance imaging apparatus comprising:
a gradient magnetic field coil, the gradient magnetic field coil being the distributed gradient magnetic field coil of the first aspect;
a control module configured to control the pulse sequence and acquire MR data;
a power module configured to power the gradient magnetic field coils and the control module.
Further, the mobile magnetic resonance imaging apparatus further comprises a base configured for mounting to the control module, the power module, the gradient magnetic field coil.
Furthermore, the lower end of the base is fixedly provided with a universal roller.
Further, the movable magnetic resonance imaging device further comprises a display module, and the display module is connected with the control module and used for displaying the magnetic resonance imaging acquired by the magnetic resonance imaging equipment.
Further, the power supply module comprises a first power supply, a second power supply and a third power supply;
the power supply end of the first power supply is a storage battery;
the power supply end of the second power supply source is a portable generator;
the power supply end of the third power supply is an alternating current power supply.
Further, the mobile magnetic resonance imaging device further comprises a power supply selection module, wherein the power supply selection module is used for selecting a power supply of the power supply module.
Further, the mobile magnetic resonance imaging device further comprises a power supply processing module, wherein the power supply processing module is used for converting the voltage and the current provided by the power supply into the voltage and the current applied by the gradient magnetic field coil and the control module.
Further, the mobile magnetic resonance imaging apparatus further comprises a calculation module configured to receive the MR data acquired by the control module and generate an MR image from the MR data.
Compared with the prior art, the distributed gradient magnetic field coil and the movable magnetic resonance imaging device have the following beneficial effects:
(1) The distributed gradient magnetic field coil provided by the invention has the advantages that the second longitudinal gradient coil is used for generating eddy currents in the iron yoke by the main longitudinal gradient coil, and the required gradient magnetic field is generated, meanwhile, the magnetic leakage control of the gradient magnetic field is better, the magnetic resonance imaging effect is improved, and the accuracy of a test result is improved.
Drawings
The accompanying drawings, which are included to provide a further understanding of the invention and are incorporated in and constitute a part of this specification, illustrate embodiments of the invention and together with the description serve to explain the invention. In the drawings:
FIG. 1 is a schematic diagram of a three-dimensional structure of a distributed gradient magnetic field coil according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of the magnetic field of a conventional gradient coil according to an embodiment of the present invention;
FIG. 3 is a schematic diagram of a distributed gradient magnetic field coil according to an embodiment of the present invention;
fig. 4 is a schematic perspective view of a movable magnetic resonance imaging apparatus according to an embodiment of the present invention.
Reference numerals illustrate:
1. a horizontal iron yoke; 2. a magnetic pole; 3. a main longitudinal gradient coil; 4. a second longitudinal gradient coil.
Detailed Description
It should be noted that, without conflict, the embodiments of the present invention and features of the embodiments may be combined with each other.
In the description of the present invention, it should be understood that the terms "center", "longitudinal", "lateral", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc. indicate orientations or positional relationships based on the orientations or positional relationships shown in the drawings, are merely for convenience in describing the present invention and simplifying the description, and do not indicate or imply that the devices or elements referred to must have a specific orientation, be configured and operated in a specific orientation, and thus should not be construed as limiting the present invention. Furthermore, the terms "first," "second," and the like, are used for descriptive purposes only and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first", "a second", etc. may explicitly or implicitly include one or more such feature. In the description of the present invention, unless otherwise indicated, the meaning of "a plurality" is two or more.
In the description of the present invention, it should be noted that, unless explicitly specified and limited otherwise, the terms "mounted," "connected," and "connected" are to be construed broadly, and may be either fixedly connected, detachably connected, or integrally connected, for example; can be mechanically or electrically connected; can be directly connected or indirectly connected through an intermediate medium, and can be communication between two elements. The specific meaning of the above terms in the present invention can be understood by those of ordinary skill in the art in a specific case.
The invention will be described in detail below with reference to the drawings in connection with embodiments.
Embodiment one:
as shown in fig. 1, a distributed gradient magnetic field coil includes:
a magnetic pole 2; configured to generate a strong constant magnetic field;
a horizontal iron yoke 1, wherein the horizontal iron yoke 1 is arranged on the lower end surface of the magnetic pole 2;
a main longitudinal gradient coil 3, the main longitudinal gradient coil 3 being mounted on the upper end face of the magnetic pole 2;
the second longitudinal gradient coil 4 is fixedly arranged on the side wall of the magnetic pole 2, and the second longitudinal gradient coil 4 is used for generating eddy currents in the iron yoke by the main longitudinal gradient coil 3;
the main longitudinal gradient coil 3 and the second longitudinal gradient coil 4 jointly generate a gradient magnetic field in the Y-axis direction in the MRI imaging space, so that the spatial coding of signals in the Y-axis direction is realized.
The distributed gradient magnetic field coil further includes:
and the transverse gradient coil generates a gradient magnetic field in the X-axis direction in the MRI imaging space, so that the spatial coding of signals in the X-axis direction is realized.
The radio frequency coil is used for generating radio frequency pulses, exciting hydrogen atomic nuclei in the sample and receiving radio frequency signals emitted by the hydrogen atomic nuclei.
As shown in fig. 2, in the magnetic field schematic diagram of the conventional gradient coil, a longitudinal gradient coil winding is arranged in an elliptical circle, and the winding is fixed on an insulating plate to form a gradient plate, and the gradient plate is fixed near the surface of a magnetic pole. The disadvantage of this gradient coil structure is that its leakage is difficult to control, wherein the longitudinal gradient coil is prone to generate eddy currents on the yoke of the magnet, as in fig. 2 the elliptical area is the winding position of the conventional longitudinal gradient coil, affecting the image quality.
As shown in fig. 3, in addition to the main gradient plates attached near the upper and lower two magnetic poles, a second longitudinal gradient coil 4 is installed at the side of the magnetic poles, which generates a magnetic field that interacts with the magnetic field generated by the main longitudinal gradient coil 3 turns in the main gradient plates to collectively form a longitudinal gradient magnetic field, and effectively suppresses eddy currents generated in the yoke by the main longitudinal gradient coil 3.
As shown in fig. 3, the elliptical ring is a second longitudinal gradient coil 4, the second longitudinal gradient coil 4 and the main longitudinal gradient coil 3 form a distributed gradient coil structure, and a reverse magnetic field generated by the second longitudinal gradient coil and the main longitudinal gradient coil 3 counteracts a magnetic field generated by the main gradient coil in the horizontal yoke 1, so that eddy currents generated in the horizontal yoke 1 are restrained, and magnetic resonance imaging is improved.
The second longitudinal gradient coil 4 is used for generating eddy current in the iron yoke by the main longitudinal gradient coil 3, generating a required gradient magnetic field, and simultaneously has better magnetic leakage control of the gradient magnetic field, thereby improving the magnetic resonance imaging effect and improving the accuracy of the test result.
Embodiment two:
a mobile magnetic resonance imaging apparatus comprising:
gradient magnetic field coils, which are distributed gradient magnetic field coils of the first embodiment;
a control module configured to control the pulse sequence and acquire MR data; the control module may provide information about the one or more pulse sequences to the computing device for processing of the data by the computing device.
The control module is used for sending instructions to the power supply system and receiving information from the power supply system. The control module may be configured to run a control module that implements one or more pulse sequences for determining instructions to send to the power module to operate magnetic field components, such as gradient coils and radio frequency coils, in a desired sequence.
The control module implements the pulse sequence by obtaining information about the pulse sequence from a pulse sequence program in which data for each of one or more parameters of the pulse sequence, such as a radio frequency pulse waveform, a gradient waveform, a duration, etc., are stored. The control module also interacts with a computing module programmed to process the received MR data.
A power module configured to power the gradient magnetic field coils and the control module.
The mobile magnetic resonance imaging apparatus further includes a base configured to be mounted to the control module, the power module, and the gradient magnetic field coil.
The lower end of the base is fixedly provided with a universal roller.
The movable magnetic resonance imaging device further comprises a display module, wherein the display module is connected with the control module and used for displaying the magnetic resonance imaging acquired by the magnetic resonance imaging equipment.
The power supply module comprises a first power supply, a second power supply and a third power supply;
the power supply end of the first power supply is a storage battery;
the power supply end of the second power supply is a portable generator;
the power supply end of the third power supply is an alternating current power supply.
The movable magnetic resonance imaging device further comprises a power supply selection module, wherein the power supply selection module is used for selecting the power supply of the power supply module.
The movable magnetic resonance imaging device also comprises a power supply processing module, wherein the power supply processing module is used for converting the voltage and the current provided by the power supply into the voltage and the current applied by the gradient magnetic field coil and the control module.
The mobile magnetic resonance imaging apparatus further comprises a calculation module configured to receive the MR data acquired by the control module and to generate an MR image from the MR data.
In some embodiments, the computing module may be a stationary electronic device, such as a desktop computer, a server, a rack-mounted computer, or any other suitable stationary electronic device that may be configured to process MR data and generate one or more images of the imaged subject.
In other embodiments, the computing device may be a portable device, such as a smart phone, personal digital assistant, tablet computer, or the like, according to some embodiments of the low-field MRI system.
A base configured for mounting to the control module, the power module, the gradient magnetic field coil.
The lower end of the base is fixedly provided with a universal roller. The roller facilitates moving the device to a designated position.
Conventional magnetic resonance imaging systems have a high power and are therefore made up of special power device electronics cabinets and placed in a specific machine room, during which power is not suitable for use in low power portable magnetic resonance systems. The invention has low-noise and low-power gradient and radio frequency system, and the three-axis gradient coil can be driven by adopting a 2 kW-level power amplifier through the optimal design and system configuration of the gradient coil, thereby being beneficial to low-power configuration to operate by using the commercial power provided by a wall socket.
When the movable magnetic resonance imaging device works, a gradient magnetic field is generated through the distributed gradient magnetic field coils, the power supply module can supply power to the distributed gradient magnetic field coils according to a desired pulse sequence, and the control of current through the coils is realized through control signals sent by the control module. The control signals of the control module may generate power pulses that control the MRI system to power the distributed gradient magnetic field coils of the magnetic resonance imaging system.
Finally, it should be noted that: the above embodiments are only for illustrating the technical solution of the present invention, and not for limiting the same; although the invention has been described in detail with reference to the foregoing embodiments, it will be understood by those of ordinary skill in the art that: the technical scheme described in the foregoing embodiments can be modified or some or all of the technical features thereof can be replaced by equivalents; such modifications and substitutions do not depart from the spirit of the invention, and are intended to be included within the scope of the claims and description.
The foregoing description of the preferred embodiments of the invention is not intended to be limiting, but rather is intended to cover all modifications, equivalents, alternatives, and improvements that fall within the spirit and scope of the invention.
Claims (10)
1. A distributed gradient magnetic field coil, comprising:
a magnetic pole (2); configured to generate a strong constant magnetic field;
a horizontal iron yoke (1), wherein the horizontal iron yoke (1) is arranged on the lower end surface of the magnetic pole (2);
a main longitudinal gradient coil (3), wherein the main longitudinal gradient coil (3) is arranged on the upper end surface of the magnetic pole (2);
the second longitudinal gradient coil (4) is fixedly arranged on the side wall of the magnetic pole (2), and the second longitudinal gradient coil (4) is used for inhibiting eddy current generated by the main longitudinal gradient coil (3) in the iron yoke;
the main longitudinal gradient coil (3) and the second longitudinal gradient coil (4) jointly generate a gradient magnetic field in the Y-axis direction in an MRI imaging space, so that spatial encoding of signals in the Y-axis direction is realized.
2. The distributed gradient magnetic field coil of claim 1, further comprising:
the transverse gradient coil generates a gradient magnetic field in the X-axis direction in the MRI imaging space, so that the spatial coding of signals in the X-axis direction is realized;
the radio frequency coil is used for generating radio frequency pulses, exciting hydrogen atomic nuclei in the sample and receiving radio frequency signals emitted by the radio frequency coils.
3. A mobile magnetic resonance imaging apparatus, comprising:
gradient magnetic field coil, which is a distributed gradient magnetic field coil according to any one of claims 1-2;
a control module configured to control the pulse sequence and acquire MR data;
a power module configured to power the gradient magnetic field coils and the control module.
4. A mobile magnetic resonance imaging apparatus according to claim 3, further comprising a base configured for mounting to the control module, the power module, the gradient magnetic field coil.
5. The mobile magnetic resonance imaging apparatus of claim 4, wherein: the universal roller is fixedly arranged at the lower end of the base.
6. A mobile magnetic resonance imaging apparatus according to claim 3, characterized in that: the movable magnetic resonance imaging device further comprises a display module, wherein the display module is connected with the control module and used for displaying the magnetic resonance imaging acquired by the magnetic resonance imaging equipment.
7. A mobile magnetic resonance imaging apparatus according to claim 3, characterized in that: the power supply module comprises a first power supply, a second power supply and a third power supply;
the power supply end of the first power supply is a storage battery;
the power supply end of the second power supply source is a portable generator;
the power supply end of the third power supply is an alternating current power supply.
8. The mobile magnetic resonance imaging apparatus of claim 7, wherein: the movable magnetic resonance imaging device further comprises a power supply selection module, wherein the power supply selection module is used for selecting a power supply of the power supply module.
9. The mobile magnetic resonance imaging apparatus of claim 7, wherein: the movable magnetic resonance imaging device further comprises a power supply processing module, wherein the power supply processing module is used for converting voltage and current provided by the power supply into voltage and current applied by the gradient magnetic field coil and the control module.
10. A mobile magnetic resonance imaging apparatus according to claim 3, characterized in that: the mobile magnetic resonance imaging apparatus further comprises a calculation module configured to receive the MR data acquired by the control module and to generate an MR image from the MR data.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311357520.3A CN117452305A (en) | 2023-10-19 | 2023-10-19 | Distributed gradient magnetic field coil and movable magnetic resonance imaging device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202311357520.3A CN117452305A (en) | 2023-10-19 | 2023-10-19 | Distributed gradient magnetic field coil and movable magnetic resonance imaging device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN117452305A true CN117452305A (en) | 2024-01-26 |
Family
ID=89592136
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202311357520.3A Pending CN117452305A (en) | 2023-10-19 | 2023-10-19 | Distributed gradient magnetic field coil and movable magnetic resonance imaging device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN117452305A (en) |
Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2000342551A (en) * | 1999-06-04 | 2000-12-12 | Ge Yokogawa Medical Systems Ltd | Mri equipment |
| CN101191829A (en) * | 2006-11-29 | 2008-06-04 | 北京万东医疗装备股份有限公司 | Fabrication method of planar active shielded gradient coil |
| CN106291422A (en) * | 2016-09-29 | 2017-01-04 | 中国科学院苏州生物医学工程技术研究所 | A kind of magnetic resonance imaging system and parameter determination method thereof |
| CN110087538A (en) * | 2016-11-22 | 2019-08-02 | 海珀菲纳研究股份有限公司 | Portable Low-field magnetic resonance imaging method and apparatus |
| CN209418235U (en) * | 2019-04-01 | 2019-09-20 | 惠仁望都医疗设备科技有限公司 | Four column type magnets |
| CN113640723A (en) * | 2021-07-20 | 2021-11-12 | 中国科学院电工研究所 | A system and method for improving the signal-to-noise ratio of immediate monitoring type magnetic resonance imaging |
| CN114259221A (en) * | 2021-11-29 | 2022-04-01 | 深圳航天科技创新研究院 | Mobile magnetic resonance imaging device without electromagnetic shielding |
-
2023
- 2023-10-19 CN CN202311357520.3A patent/CN117452305A/en active Pending
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2000342551A (en) * | 1999-06-04 | 2000-12-12 | Ge Yokogawa Medical Systems Ltd | Mri equipment |
| CN101191829A (en) * | 2006-11-29 | 2008-06-04 | 北京万东医疗装备股份有限公司 | Fabrication method of planar active shielded gradient coil |
| CN106291422A (en) * | 2016-09-29 | 2017-01-04 | 中国科学院苏州生物医学工程技术研究所 | A kind of magnetic resonance imaging system and parameter determination method thereof |
| CN110087538A (en) * | 2016-11-22 | 2019-08-02 | 海珀菲纳研究股份有限公司 | Portable Low-field magnetic resonance imaging method and apparatus |
| CN209418235U (en) * | 2019-04-01 | 2019-09-20 | 惠仁望都医疗设备科技有限公司 | Four column type magnets |
| CN113640723A (en) * | 2021-07-20 | 2021-11-12 | 中国科学院电工研究所 | A system and method for improving the signal-to-noise ratio of immediate monitoring type magnetic resonance imaging |
| CN114259221A (en) * | 2021-11-29 | 2022-04-01 | 深圳航天科技创新研究院 | Mobile magnetic resonance imaging device without electromagnetic shielding |
Non-Patent Citations (1)
| Title |
|---|
| 沈杰 等: "一种减小梯度线圈产生的涡流的方法", 《物理学报》, vol. 55, no. 6, 12 June 2006 (2006-06-12), pages 3060 - 3066 * |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US20220043094A1 (en) | Correcting for hysteresis in magnetic resonance imaging | |
| US20230358833A1 (en) | B0 magnet methods and apparatus for a magnetic resonance imaging system | |
| CN102830377B (en) | local coil for imaging system | |
| US20070096739A1 (en) | Magnetic resonance imaging apparatus | |
| US7589530B2 (en) | Coil device and nuclear magnetic resonance imaging apparatus using the same | |
| US6850065B1 (en) | MRI coil system for breast imaging | |
| JP2014136003A (en) | Magnetic resonance imaging apparatus and rf coil device | |
| US5646530A (en) | Surface coil for high resolution imaging using a magnetic resonance imaging apparatus | |
| KR101600886B1 (en) | Magnetic resonance imaging apparatus | |
| CN203468608U (en) | Open-type superconducting magnetic resonance imaging system | |
| EP0913699B1 (en) | Planar gradient coil system for MRI positioned on only one side of the subject to be examined | |
| US10247794B2 (en) | Magnetic field monitoring probe, magnetic resonance imaging apparatus including the same, and method for controlling the same | |
| US7199585B2 (en) | Method for shimming a main magnetic field in magnetic resonance | |
| JP5238156B2 (en) | Magnetic resonance imaging apparatus and high frequency coil selection method in the apparatus | |
| CN103239229A (en) | Magnetic resonance imaging apparatus | |
| CN117452305A (en) | Distributed gradient magnetic field coil and movable magnetic resonance imaging device | |
| US20240345192A1 (en) | Counter rotating current coil for magnetic resonance imaging | |
| US7432709B2 (en) | Planar RF resonator for open MRI systems | |
| CN117597593A (en) | Interventional localization guide and method for MRI-guided pelvic interventions | |
| CN216317600U (en) | Scanning bed and ultralow field magnetic resonance imaging system | |
| CN117872240A (en) | Gradient coil-free vertical magnetic resonance imaging equipment, imaging system and imaging method | |
| JP2005261806A (en) | Magnetic resonance imaging apparatus | |
| EP4278199A1 (en) | Radio frequency coil magnetic resonance imaging | |
| US20170234947A1 (en) | Radio frequency coil and magnetic resonance imaging system comprising the same | |
| CN117872241A (en) | Gradient coil-free vertical magnetic particle imaging equipment, imaging system and imaging method |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination |