CN106908746B - Head magnetic resonance imaging apparatus and head gradient coil assembly thereof - Google Patents
Head magnetic resonance imaging apparatus and head gradient coil assembly thereof Download PDFInfo
- Publication number
- CN106908746B CN106908746B CN201510971932.5A CN201510971932A CN106908746B CN 106908746 B CN106908746 B CN 106908746B CN 201510971932 A CN201510971932 A CN 201510971932A CN 106908746 B CN106908746 B CN 106908746B
- Authority
- CN
- China
- Prior art keywords
- head
- gradient
- insulating support
- coil layer
- main
- 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.)
- Active
Links
Images
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
- G01R33/28—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
- G01R33/385—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils
Landscapes
- Physics & Mathematics (AREA)
- Condensed Matter Physics & Semiconductors (AREA)
- General Physics & Mathematics (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
The invention discloses a head magnetic resonance imaging device. The head magnetic resonance imaging apparatus includes: a main magnet having a central bore; and a head gradient coil assembly located in the central cavity and including a head-sized main coil layer for generating a main gradient field to generate a head-sized imaging field of view, a shield coil layer for generating a shield gradient field to cancel the main gradient field outside the head gradient coil assembly, and an insulating support for supporting the main coil layer and the shield coil layer, the shield coil layer being sized to wrap around the shoulders of a patient. The invention also discloses a head gradient coil assembly of the head magnetic resonance imaging device, which is used for scanning and examining the head of a patient.
Description
Technical Field
The invention relates to a magnetic resonance imaging device, in particular to a head magnetic resonance imaging device.
Background
Head gradient coil assemblies are widely used to image the head of a patient. Existing head gradient coil assemblies are inserted into a whole-body magnetic resonance imaging apparatus while scanning a patient's head. The head gradient coil assembly mainly comprises a main gradient coil, a shielding gradient coil and a support for supporting the main gradient coil and the shielding gradient coil. The primary gradient coils are used to generate primary gradient fields to produce an imaging field of view of the head. The shield gradient coils are used to generate shield gradient fields to cancel the main gradient fields outside the head gradient coil assembly.
The support is small in size so as to be accommodated in the whole-body magnetic resonance imaging apparatus, and the main gradient coil and the shield gradient coil are wound on the support at a short distance. Thus, the main gradient field outside the head gradient coil assembly is stronger, and therefore the shielding gradient coil needs to be wound around the support for more turns to generate a stronger shielding gradient field, thereby completely offsetting the main gradient field outside the head gradient coil assembly. The shield gradient field generated by the shield gradient coil is spread to the imaging field of view, canceling out the main gradient field in the imaging field of view, so that the maximum gradient strength is weakened. In order to compensate for the offset main gradient field, the number of turns of the main gradient coil needs to be increased, which increases the overall inductance, and the number of turns of the shielding gradient coil needs to be increased to offset the main gradient field generated by the main gradient coil. This in turn weakens the maximum gradient strength of the main gradient field within the imaging field of view.
Therefore, there is a need to provide a solution to at least one of the above mentioned problems.
Disclosure of Invention
One aspect of the present invention is to provide a head magnetic resonance imaging apparatus. The head magnetic resonance imaging apparatus includes: a main magnet having a central bore; and a head gradient coil assembly located in the central cavity and including a head-sized main coil layer for generating a main gradient field to generate a head-sized imaging field of view, a shield coil layer for generating a shield gradient field to cancel the main gradient field outside the head gradient coil assembly, and an insulating support for supporting the main coil layer and the shield coil layer, the shield coil layer being sized to wrap around the shoulders of a patient.
It is another aspect of the present invention to provide for a head gradient coil assembly. The head gradient coil assembly includes: a head-sized primary coil layer to generate a primary gradient field to produce a head-sized imaging field of view; a shield coil layer for generating a shield gradient field to counteract the primary gradient field outside the head gradient coil assembly, the shield coil layer being sized to encircle a patient's shoulders; and an insulating support for supporting the main coil layer and the shield coil layer.
It is yet another aspect of the present invention to provide for a head gradient coil assembly. The head gradient coil assembly includes: an insulating support comprising an outer diameter and an inner diameter; a main coil layer located at an inner diameter of the insulating support for generating a main gradient field, the main coil layer being sized to encircle a head of a patient with shoulders of the patient outside the main coil layer; and a shield coil layer located on the outer diameter of the insulating support for generating a shield gradient field to counteract the primary gradient field outside the head gradient coil assembly, the shield coil layer being sized to wrap around the shoulders of the patient.
Drawings
The invention may be better understood by describing embodiments thereof in conjunction with the following drawings, in which:
figure 1 shows a schematic cross-sectional view of an embodiment of a head mri apparatus of the invention;
FIG. 2 is a schematic diagram of one embodiment of gradient fields generated by main coil layers and shield coil layers of a head MRI apparatus;
figure 3 shows a schematic cross-sectional view of another embodiment of a head mri apparatus of the invention;
figure 4 shows a schematic cross-sectional view of another embodiment of a head mri apparatus of the invention;
figure 5 is a schematic cross-sectional view of another embodiment of a head mri apparatus of the present invention;
figure 6 shows a schematic cross-sectional view of another embodiment of a head mri apparatus of the invention;
figure 7 shows a schematic cross-sectional view of another embodiment of a head mri apparatus of the invention.
Detailed Description
Unless defined otherwise, technical or scientific terms used herein shall have the ordinary meaning as understood by one of ordinary skill in the art to which this invention belongs. The use of "first," "second," and similar terms in the description and claims of the present application do not denote any order, quantity, or importance, but rather the terms are used to distinguish one element from another. Also, the use of the terms "a" or "an" and the like do not denote a limitation of quantity, but rather denote the presence of at least one. Unless otherwise indicated, the terms "front," "back," "lower," and/or "upper" and the like are used for convenience of description and are not limited to one position or one spatial orientation. Furthermore, the use of the terms "connected" or "coupled" and the like are not intended to distinguish between direct and indirect connections between two elements. Of course, unless otherwise stated, such elements may be directly or indirectly connected.
Fig. 1 is a cross-sectional schematic view of a head magnetic resonance imaging apparatus 10 according to an embodiment. The head magnetic resonance imaging apparatus 10 is used to scan or examine a patient's head 100. In the present embodiment, the head mri apparatus 10 can operate independently without being inserted into the whole-body mri apparatus. The head magnetic resonance imaging device 10 includes a main magnet 12, magnet coils 14, and a head gradient coil assembly 16.
The main magnet 12 supports magnet coils 14 and has a central bore 18 that can receive a head gradient coil assembly 16. The main magnet 12 is more typically cylindrical. The magnet coils 14 are used to generate a magnetic field along the length of the central cavity 18 and in the Z-axis direction. The magnet coils 14 may be housed in cryogenic tanks to maintain the magnet coils 14 at superconducting temperatures.
The head gradient coil assembly 16 is located within the central bore 18. In one embodiment, the head gradient coil assembly 16 is secured within the central bore 18, and the head gradient coil assembly 16 is not easily removable from the central bore 18. In another embodiment, the head gradient coil assembly 16 is removably inserted within the central cavity 18. The head gradient coil assembly 16 is sized such that the head gradient coil assembly 16 may occupy substantially all of the space of the central bore 18.
The gradient coil assembly 16 includes Head-sized (Head-sized) main coil layers 22, shield coil layers 24, and insulating supports 26 for supporting the main coil layers 22 and the shield coil layers 24. The main coil layer 22 is used to generate a main gradient Field to produce a head-sized imaging Field of View (FOV) 30. "head size" means a dimension slightly larger than the head. The primary coil layer 22 is sized such that the primary coil layer 22 may wrap around the head 100 of the patient with the shoulders 200 of the patient outside the primary coil layer 22. The primary coil layer 22 is as close to the patient's head 100 as possible, the diameter of the primary coil layer 22 being slightly larger than the width of the patient's head 100. The imaging field of view of the sphere is slightly larger than that of the head 100.
The main coil layer 22 includes an X-axis gradient main coil (not shown), a Y-axis gradient main coil (not shown), and a Z-axis gradient main coil (not shown) wound around an insulating support 26. The Z-axis gradient main coil may be of a symmetrical or asymmetrical configuration. The primary coil may be formed by winding or cutting a conductive wire, rod or plate into a coil shape. The primary coil layer 22 is located at the inner diameter of the insulating support 26. In one embodiment, the main coil layer 22 may include a multi-layer X-axis gradient main coil (not shown), Y-axis gradient main coil (not shown), and/or Z-axis gradient main coil.
The shield coil layer 24 is used to generate a shield gradient field to cancel the main gradient field outside the head gradient coil assembly 16. The shield coil layer 24 is sized to wrap around the patient's shoulders 200. The diameter of the shield coil layer 24 is greater than the diameter of the main coil layer 22 and the patient's shoulder width. The shield coil layer 24 is longer than the main coil layer 22 in the length direction of the insulating support 26. In one embodiment, the shield coil layer 24 is as long as the main magnet 12 in the length direction to mitigate or avoid the effect of the main gradient field generated by the main coil layer 22 on the main magnet 12 and the magnet coils 14. The shield coil layer 24 may extend lengthwise to the patient's head and shoulders, and in one embodiment, to the entire body. The shield coil layer 24 forms a shield between the main magnet 12 and the main coil layer 22.
In this embodiment, the shield coil layer 24 is located at the outer diameter of the insulating support 26 and the main coil layer is located at the inner diameter of the insulating support 26. The shield coil layer 24 and the main coil layer 22 are spaced apart by a large distance in the diametrical direction. In one embodiment, the spacing between the shield coil layer 24 and the primary coil layer 22 is no less than 8 centimeters. In an exemplary embodiment, the spacing is between about 8 centimeters and about 28 centimeters. Typically, the diameter of the main coil layer 22 is about 44 cm, the diameter of the shield coil layer 24 is about 74 cm, and the spacing between the shield coil layer 24 and the main coil layer 22 is about 15 cm. The spacing between the shield coil layer 24 and the main coil layer 22, the diameter of the main coil layer 22, and the diameter of the shield coil layer 24 may be adjusted according to the user's needs.
The shield coil layer 24 includes an X-axis gradient shield coil (not shown), a Y-axis gradient shield coil (not shown), and a Z-axis gradient shield coil (not shown) wound around the insulating support 26. The Z-axis gradient shield coil may be of a symmetrical or asymmetrical configuration. The shield coil may be formed from a conductive wire, rod or plate wound or cut into a coil shape. In one embodiment, the X-axis gradient coil folds form an X-axis gradient main coil and an X-axis gradient shield coil, and/or the Y-axis gradient coil folds form a Y-axis gradient main coil and a Y-axis gradient shield coil.
An insulating support 26 supports the main coil layer 22 and the shield coil layer 24. The insulating support 26 is mounted in the central bore 18 of the main magnet 12, the insulating support 26 having an outer diameter that conforms to the central bore 18 such that the insulating support 26 can occupy substantially all of the space of the central bore 18. The insulating support 26 is sized to receive the head 100 and shoulders 200 of a patient, and in one embodiment, even the entire body. In one embodiment, the length of the insulating support 26 is substantially equal to the length of the main magnet 12. In one embodiment, the insulating support 26 is cylindrical. In one embodiment, the insulating support 26 includes a lumen 28, the lumen 28 having a first inner diameter 36 configured to receive a head 100 of a patient and a second inner diameter 38 larger than the first inner diameter 36 configured to receive a shoulder 200 of the patient. The first inner diameter 36 is the head size, which is slightly larger than the head 100, and the primary coil layer 22 is formed on the first inner diameter 36 of the insulating holder 26. In the illustrated embodiment, the insulating support 26 has a cut-out 32 formed in a patient end 34 of the insulating support 26 to form a second inner diameter 38 and a stepped configuration between the first inner diameter 36 and the second inner diameter 38 to accommodate the shape of the shoulder 200. In another embodiment, a plurality of stepped structures are formed at the patient end 34 to accommodate the shape of the shoulder 200.
The insulating support 26 comprises one or more insulating materials, such as fiberglass. In one embodiment, the insulating support 26 further contains at least one of a sound damping material and a vibration damping material. In one embodiment, the insulating support 26 contains sound damping material, such as some foam-like material and flexible resin, to absorb the noise generated by the coil. In another embodiment, the insulating support 26 contains vibration damping materials, such as some foam-like materials and flexible resins, that absorb vibrations and reduce the amplitude of the vibrations. In yet another embodiment, the insulating support 26 contains sound and vibration damping materials, which may be two materials or one material having both sound and vibration damping, such as rubber, some foamed materials, and flexible resins. In one embodiment, the acoustic damping material and/or the vibration damping material may be mixed in particulate form in the insulating material.
Figure 1 shows only one example of a head magnetic resonance imaging apparatus 10. Fig. 1 shows only some of the elements of the head mri apparatus 10, and the head mri apparatus 10 may further include other elements than the elements shown in fig. 1, such as a Radio Frequency (RF) coil. The radio frequency coils are mounted inside the head gradient coil assembly 16 to generate radio frequency pulses.
Fig. 2 is a schematic diagram of one embodiment of the gradient fields generated by the main coil layers 22 and the shield coil layers 24 of the head magnetic resonance imaging apparatus 10. The main gradient field 40 is shown as a gradient coil produced by the main gradient coil layer 22 and the shield gradient field 42 is shown as a gradient coil produced by the shield coil layer 24. The magnitude of the main gradient field 40 decreases substantially further away from the main coil layer 22. The magnitude of the shield gradient field 42 is significantly reduced the further away from the shield coil layer 24. Due to the larger spacing between the main coil layers 22 and the shield coil layers 24, the main gradient fields 40 generated by the main coil layers 22 near the shield coils 24 and the main magnetic field 12 are weaker, such that the shield coil layers 24 are designed to generate correspondingly weaker shield gradient fields 42 to cancel the main gradient fields 40 at the main magnet 12 to minimize the effect of the main coil layers 22 on the main magnet 12. The shield coil layer 24 may have fewer turns to produce a weaker shield gradient field 42. Moreover, the shielding gradient field 42 is significantly reduced at the imaging field of view 30, where the shielding gradient field 42 is cancelled by the main gradient field 40, so that the main coil layer 22 is increased by a smaller number of turns to cancel the shielding gradient field 42 at the imaging field of view 30. Thus, the overall inductance of the head gradient coil assembly 16 is reduced, reducing the negative impact on the imaging field of view 30. In this way, the gradient field strength and slew rate of the main gradient field 42 are increased.
Fig. 3 is a cross-sectional schematic view of a head magnetic resonance imaging apparatus 10 according to another embodiment. The head magnetic resonance imaging apparatus 10 shown in fig. 3 is similar to the head magnetic resonance imaging apparatus 10 shown in fig. 1. In contrast to the head mri apparatus 10 shown in fig. 1, the insulating support 26 of the head mri apparatus 10 shown in fig. 3 has a frustum-shaped cut-out 44 at the patient end 34, and the opening outside the insulating support 26 is larger than the opening inside the insulating support 26, so that the insulating support 26 has a larger receiving space to accommodate the shoulder and arm of the patient. Fig. 1 and 3 illustrate only non-limiting examples of the structure of the insulating support 26, and in some embodiments, the insulating support 26 may have other structures to provide large space for the patient's shoulders, arms, or even the entire body.
Fig. 4 is a cross-sectional schematic view of a head magnetic resonance imaging apparatus 10 according to another embodiment. The head magnetic resonance imaging apparatus 10 shown in fig. 4 is similar to the head magnetic resonance imaging apparatus 10 shown in fig. 1. The head magnetic resonance imaging apparatus 10 shown in fig. 4 has more one main coil layer 50 than the head magnetic resonance imaging apparatus 10 shown in fig. 1. The primary coil layer 50 is supported by the insulating support 26 for generating the primary gradient field. The primary coil layers 22 and 50 together generate the primary gradient field, increasing the strength of the primary gradient field. The main coil layer 50 is adjacent to the main coil layer 22 and is spaced from the shield coil layer 24. In one embodiment, the spacing is not less than 8 centimeters. The shielding gradient field generated by the shielding coil layer 24 also cancels the main gradient field generated by the main coil layer 50 outside the head magnetic resonance imaging device 10. In one embodiment, the main coil layer 50 may have a similar structure to the main coil layer 22. In one embodiment, three or more main coil layers are used to generate the main gradient field.
Fig. 5 is a cross-sectional schematic view of a head magnetic resonance imaging apparatus 10 according to another embodiment. The head magnetic resonance imaging apparatus 10 shown in fig. 5 is similar to the head magnetic resonance imaging apparatus 10 shown in fig. 1. In contrast to the head mri apparatus 10 shown in fig. 1, the head mri apparatus 10 shown in fig. 5 further includes an interposer 52 supported by the insulating support 26 for making the magnetic field uniform. In the embodiment shown in fig. 5, an interposer 52 is located between the primary coil layer 22 and the shield coil layer 24. The interposer 52 includes a number of interposers. The larger spacing between the main coil layer 22 and the shield coil layer 24 allows the interposer 52 to be interposed therebetween without being affected by the heat generated by the main coil layer 22 and the shield coil layer 24.
Fig. 6 is a cross-sectional schematic view of a head magnetic resonance imaging apparatus 10 according to another embodiment. The head magnetic resonance imaging apparatus 10 shown in fig. 6 is similar to the head magnetic resonance imaging apparatus 10 shown in fig. 5. In contrast to the head mri apparatus 10 shown in fig. 5, the interposer 52 shown in fig. 6 is located inside the shield coil layer 24 close thereto.
Fig. 7 is a cross-sectional schematic view of a head magnetic resonance imaging apparatus 10 according to another embodiment. The head magnetic resonance imaging apparatus 10 shown in fig. 7 is similar to the head magnetic resonance imaging apparatus 10 shown in fig. 5. In contrast to the head mri apparatus 10 shown in fig. 5, the interposer 52 shown in fig. 7 is located at the outer diameter of the insulating support 26, and the shield coil layer 24 is located at the inner side of the interposer 52 and close to the interposer 52. Fig. 5-7 illustrate non-limiting examples of interposers 52, and in other embodiments, interposers 52 may be arranged in other ways.
While the invention has been described in conjunction with specific embodiments thereof, it will be understood by those skilled in the art that many modifications and variations may be made to the invention. It is, therefore, to be understood that the appended claims are intended to cover all such modifications and changes as fall within the true spirit and scope of the invention.
Claims (18)
1. A head magnetic resonance imaging apparatus, characterized in that the head magnetic resonance imaging apparatus comprises:
a main magnet having a central bore; and
a head gradient coil assembly located in the central cavity and including a head-sized main coil layer to generate a head-sized imaging field of view, a shield coil layer to generate a shield gradient field to cancel the main gradient field outside the head gradient coil assembly, and an insulating support to support the main coil layer and the shield coil layer, the shield coil layer being sized to wrap around a shoulder of a patient, the shield coil layer being longer than the main coil layer in a length direction of the insulating support.
2. The head magnetic resonance imaging apparatus as claimed in claim 1, characterized in that: the head gradient coil assembly includes a plurality of the primary coil layers supported by the insulating support to generate the primary gradient field.
3. The head magnetic resonance imaging apparatus as claimed in claim 1, characterized in that: the insulating support comprises an outer diameter and an inner diameter, the main coil layer is located on the inner diameter of the insulating support, and the shielding coil layer is located on the outer diameter of the insulating support.
4. The head magnetic resonance imaging apparatus as claimed in claim 1, characterized in that: the insulating support includes a lumen having a first inner diameter that can receive a head of a patient and a second inner diameter that is larger than the first inner diameter that can receive a shoulder of the patient.
5. The head magnetic resonance imaging apparatus as claimed in claim 1, characterized in that: the head gradient coil assembly further includes an interposer supported by the insulating support.
6. The head magnetic resonance imaging apparatus as claimed in claim 1, characterized in that: the insulating support contains at least one of a sound damping material and a vibration damping material.
7. A head gradient coil assembly, comprising:
a head-sized primary coil layer to generate a primary gradient field to produce a head-sized imaging field of view;
a shield coil layer for generating a shield gradient field to counteract the primary gradient field outside the head gradient coil assembly, the shield coil layer being sized to encircle a patient's shoulders; and
an insulating support for supporting the main coil layer and the shield coil layer,
the shield coil layer is longer than the main coil layer in a length direction of the insulating support.
8. The head gradient coil assembly of claim 7, wherein: the head gradient coil assembly includes a plurality of the primary coil layers supported by the insulating support to generate the primary gradient field.
9. The head gradient coil assembly of claim 7, wherein: the insulating support comprises an outer diameter and an inner diameter, the main coil layer is located on the inner diameter of the insulating support, and the shielding coil layer is located on the outer diameter of the insulating support.
10. The head gradient coil assembly of claim 7, wherein: the insulating support includes a lumen having a first inner diameter that can receive a head of a patient and a second inner diameter that is larger than the first inner diameter that can receive a shoulder of the patient.
11. The head gradient coil assembly of claim 7, wherein: the head gradient coil assembly further includes an interposer supported by the insulating support.
12. The head gradient coil assembly of claim 7, wherein: the insulating support contains at least one of a sound damping material and a vibration damping material.
13. A head gradient coil assembly, comprising:
an insulating support comprising an outer diameter and an inner diameter;
a main coil layer located at an inner diameter of the insulating support for generating a main gradient field, the main coil layer being sized to encircle a head of a patient with shoulders of the patient outside the main coil layer; and
a shield coil layer on an outer diameter of the insulating support to generate a shield gradient field to cancel the primary gradient field outside the head gradient coil assembly, the shield coil layer sized to wrap around a shoulder of a patient.
14. The head gradient coil assembly of claim 13, wherein: the head gradient coil assembly includes a plurality of the primary coil layers supported by the insulating support to generate the primary gradient field.
15. The head gradient coil assembly of claim 13, wherein: the shield coil layer is longer than the main coil layer in a length direction of the insulating support.
16. The head gradient coil assembly of claim 13, wherein: the insulating support includes a lumen having a first inner diameter that can receive a head of a patient and a second inner diameter that is larger than the first inner diameter that can receive a shoulder of the patient.
17. The head gradient coil assembly of claim 13, wherein: the head gradient coil assembly further includes an interposer supported by the insulating support.
18. The head gradient coil assembly of claim 13, wherein: the insulating support contains at least one of a sound damping material and a vibration damping material.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201510971932.5A CN106908746B (en) | 2015-12-22 | 2015-12-22 | Head magnetic resonance imaging apparatus and head gradient coil assembly thereof |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201510971932.5A CN106908746B (en) | 2015-12-22 | 2015-12-22 | Head magnetic resonance imaging apparatus and head gradient coil assembly thereof |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN106908746A CN106908746A (en) | 2017-06-30 |
| CN106908746B true CN106908746B (en) | 2020-01-21 |
Family
ID=59200193
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201510971932.5A Active CN106908746B (en) | 2015-12-22 | 2015-12-22 | Head magnetic resonance imaging apparatus and head gradient coil assembly thereof |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN106908746B (en) |
Families Citing this family (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109696645A (en) * | 2018-12-29 | 2019-04-30 | 佛山瑞加图医疗科技有限公司 | A kind of non-planar gradient coil |
| US20200355768A1 (en) * | 2019-05-10 | 2020-11-12 | Geron BINDSEIL | Coil system with different currents driven through the shield and primary coils |
| JP6739589B1 (en) * | 2019-05-10 | 2020-08-12 | ゼネラル・エレクトリック・カンパニイ | Magnetic resonance imaging apparatus and program |
| CN112748380B (en) * | 2019-10-29 | 2024-03-19 | 西门子(深圳)磁共振有限公司 | Gradient coil for magnetic resonance imaging device and magnetic resonance imaging device |
| EP4242681A1 (en) * | 2022-03-10 | 2023-09-13 | Siemens Healthcare GmbH | Gradient coil unit comprising two hollow cylinder areas for a magnetic resonance imaging system |
| CN116087849B (en) * | 2023-02-28 | 2023-11-17 | 江苏力磁医疗设备有限公司 | Gradient coil special for MRI |
Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5416415A (en) * | 1994-08-05 | 1995-05-16 | General Electric Company | Over-shoulder MRI magnet for human brain imaging |
| US5801609A (en) * | 1997-04-25 | 1998-09-01 | General Electric Company | MRI head magnet |
| CN1951322A (en) * | 2006-11-22 | 2007-04-25 | 中国科学院电工研究所 | An apparatus for decreasing magnetic vortex in MRI |
| CN101900795A (en) * | 2009-05-29 | 2010-12-01 | 株式会社东芝 | MR imaging apparatus |
| CN204734481U (en) * | 2015-06-07 | 2015-11-04 | 上海联影医疗科技有限公司 | Special magnetic resonance scanning apparatus of head and special magnetic resonance scanning system of head |
| CN105044635A (en) * | 2015-06-12 | 2015-11-11 | 北京斯派克科技发展有限公司 | Gradient coil for joint magnetic resonance imaging |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP3702022B2 (en) * | 1996-02-09 | 2005-10-05 | 株式会社東芝 | Gradient field coil |
| JP5534713B2 (en) * | 2009-05-20 | 2014-07-02 | 三菱電機株式会社 | Superconducting magnet |
-
2015
- 2015-12-22 CN CN201510971932.5A patent/CN106908746B/en active Active
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5416415A (en) * | 1994-08-05 | 1995-05-16 | General Electric Company | Over-shoulder MRI magnet for human brain imaging |
| US5801609A (en) * | 1997-04-25 | 1998-09-01 | General Electric Company | MRI head magnet |
| CN1951322A (en) * | 2006-11-22 | 2007-04-25 | 中国科学院电工研究所 | An apparatus for decreasing magnetic vortex in MRI |
| CN101900795A (en) * | 2009-05-29 | 2010-12-01 | 株式会社东芝 | MR imaging apparatus |
| CN204734481U (en) * | 2015-06-07 | 2015-11-04 | 上海联影医疗科技有限公司 | Special magnetic resonance scanning apparatus of head and special magnetic resonance scanning system of head |
| CN105044635A (en) * | 2015-06-12 | 2015-11-11 | 北京斯派克科技发展有限公司 | Gradient coil for joint magnetic resonance imaging |
Also Published As
| Publication number | Publication date |
|---|---|
| CN106908746A (en) | 2017-06-30 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN106908746B (en) | Head magnetic resonance imaging apparatus and head gradient coil assembly thereof | |
| JP7073367B2 (en) | Front Radio Frequency (RF) Coil Array for Magnetic Resonance Imaging (MRI) Systems | |
| JP2020510453A (en) | Radio frequency coil system for MR imaging | |
| JP5955642B2 (en) | Method and apparatus for imaging an object using a local surface coil | |
| US8212564B2 (en) | Open magnetic resonance imaging apparatus | |
| US9244141B2 (en) | Integrated sheath current filter in a local coil | |
| WO2002002010A1 (en) | Magnetic resonance imaging device and gradient magnetic field coil used for it | |
| JP2002219112A (en) | Lower noise type mri scanner | |
| KR101625558B1 (en) | Magnetic resonance coil device | |
| US10031192B2 (en) | Antenna apparatus for receiving magnetic resonance signals | |
| JP2015506741A (en) | System and apparatus for compensating for magnetic field distortions caused by mechanical vibration of an MRI system | |
| US11054491B2 (en) | Dipole antenna assembly for capturing images by means of nuclear magnetic resonance methods | |
| JP5932815B2 (en) | Magnetic resonance imaging system | |
| JP6061518B2 (en) | System and apparatus for balancing radial forces in gradient coils | |
| US20210181279A1 (en) | Gradient coil unit for a magnetic resonance device | |
| US10962612B2 (en) | Magnetic resonance imaging apparatus having high frequency coil isolated from gradient coils and a tapered / inclined coil support unit | |
| KR101890261B1 (en) | Magnetic resonance imaging birdcage coil assembly aligned along the z-axis | |
| US11422214B2 (en) | Gradient coil system | |
| JP5069471B2 (en) | Planar RF resonator for open MRI systems | |
| US6667619B2 (en) | Magnetic resonance apparatus with damping of inner mechanical vibrations | |
| WO2021124877A1 (en) | Gradient magnetic field coil apparatus and magnetic resonance imaging apparatus | |
| CN210092324U (en) | High-frequency antenna for a magnetic resonance system | |
| WO2018201001A1 (en) | Adult head-sized coil-based low-field mri | |
| JP2013141504A (en) | Rf coil unit and magnetic resonance imaging apparatus | |
| JP5901561B2 (en) | Magnetic resonance imaging system |
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 | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |