CN108398657B - Magnetic resonance transmitting coil - Google Patents
Magnetic resonance transmitting coil Download PDFInfo
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- CN108398657B CN108398657B CN201810031958.5A CN201810031958A CN108398657B CN 108398657 B CN108398657 B CN 108398657B CN 201810031958 A CN201810031958 A CN 201810031958A CN 108398657 B CN108398657 B CN 108398657B
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- 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
- G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
- G01R33/34007—Manufacture of RF coils, e.g. using printed circuit board technology; additional hardware for providing mechanical support to the RF coil assembly or to part thereof, e.g. a support for moving the coil assembly relative to the remainder of the MR system
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Abstract
The invention discloses a magnetic resonance transmitting coil, which comprises a coil body and a shielding layer sleeved outside the coil body; the coil body comprises a body middle section and body end sections positioned on two sides of the body middle section, wherein the radial distance between at least one of the body end sections and the shielding layer is greater than the radial distance between the body middle section and the shielding layer. The magnetic resonance transmitting coil provided by the invention adopts a mode of reducing the distance between the middle part of the coil and the shielding layer to balance the field distribution of the central area and the edge area, thereby improving the uniformity of a transmitting field, ensuring that the B1 field in the FOV area has better uniformity, avoiding the mode of prolonging the length of the transmitting coil in the background technology and ensuring the transmitting efficiency.
Description
Technical Field
The invention relates to the technical field of magnetic resonance, in particular to a magnetic resonance transmitting coil.
Background
A magnetic resonance transmit coil is a device that excites an object under test with radio frequency signals to obtain magnetic resonance signals.
Referring to fig. 1, fig. 1 is a schematic structural diagram of a conventional magnetic resonance transmit coil.
As shown in fig. 1, the conventional magnetic resonance transmit coil 1A has a cylindrical structure, and the inner aperture thereof is sized to accommodate the entrance and exit of a patient and a patient bed.
The length L of the magnetic resonance transmit coil 1A covers the entire FOV area, and in order to make the field strength in the FOV area more uniform, it is common to lengthen the magnetic resonance transmit coil 1A, even if the length of the magnetic resonance transmit coil 1A exceeds the FOV area.
Referring to fig. 2, fig. 2 is a comparison diagram of the relationship between the length of the transmitting coil and the field strength.
As shown in fig. 2, the dashed lines in fig. 2 represent relatively short length transmit coils and the solid lines represent relatively long length transmit coils, and in contrast, long length transmit coils produce a relatively more uniform field strength distribution, but relatively lower field strengths, within the same FOV area.
In addition, when the coil length is extended, the entire electrical length increases, the volume of the transmission coil increases, and the entire transmission field efficiency decreases.
In view of this, how to improve the structure of the magnetic resonance transmit coil to improve the uniformity of the transmit field while ensuring the efficiency of the transmit field is a technical problem that needs to be solved by those skilled in the art.
Disclosure of Invention
In order to solve the above technical problem, the present invention provides a magnetic resonance transmission coil, which includes a coil body and a shielding layer sleeved on the coil body; the coil body comprises a body middle section and body end sections positioned on two sides of the body middle section, wherein the radial distance between at least one of the body end sections and the shielding layer is greater than the radial distance between the body middle section and the shielding layer.
According to the magnetic resonance transmitting coil provided by the invention, the radial distance between the end section of the coil body and the shielding layer is greater than the radial distance between the middle section of the coil body and the shielding layer; according to research, the distance between the coil body and the shielding layer of the transmitting coil is related to the field intensity, specifically, the smaller the distance, the smaller the field intensity, the larger the distance, and the larger the field intensity, therefore, the magnetic resonance transmitting coil provided by the invention adopts a mode of reducing the distance between the middle part of the coil and the shielding layer so as to balance the field distribution of the central area and the edge area, thereby improving the uniformity of the transmitting field, enabling the B1 field in the FOV area to have better uniformity, avoiding the mode of prolonging the length of the transmitting coil in the background technology, and being capable of ensuring the transmitting efficiency.
Optionally, the radial distance between the body end section and the shielding layer decreases axially inward.
Optionally, the outer diameter of the end section of the body is increased gradually inwards along the axial direction; the inner diameter of the shielding layer is kept consistent along the axial direction.
Optionally, the outer diameter of the body end section continuously increases axially inwards; the inner diameter of the shielding layer is kept consistent along the axial direction.
Optionally, the outer diameter of the coil body is kept consistent along the axial direction; the inner diameter of the layer end part of the shielding layer is gradually reduced inwards along the axial direction.
Optionally, the outer diameter of the coil body is kept consistent along the axial direction; the inner diameter of the layer end part of the shielding layer continuously decreases inwards along the axial direction.
Optionally, the outer diameter of the body end section increases axially inward, and the inner diameter of the layer end of the shielding layer decreases axially inward.
Optionally, the radial distance between the middle section of the body and the shielding layer gradually increases from the axial center to both sides.
Optionally, the outer diameter of the middle section of the body gradually decreases from the axial center to both sides.
Optionally, the inner diameter of the middle part of the shielding layer gradually increases from the axial center to both sides.
Drawings
Fig. 1 is a schematic structural diagram of a conventional magnetic resonance transmit coil;
FIG. 2 is a diagram showing the relationship between the length of the transmitting coil and the field strength;
FIGS. 3a and 3b are schematic diagrams showing the relationship between the coil body and shield spacing of a magnetic resonance transmit coil and the field strength;
figure 4a is a schematic diagram of a structural principle of a magnetic resonance transmitting coil provided by the invention;
figure 4b is a schematic diagram of another configuration of a magnetic resonance transmit coil provided in accordance with the present invention;
FIG. 4c is a schematic diagram of another structure of a magnetic resonance transmit coil according to the present invention;
FIG. 5 is a schematic diagram of a comparison of the B1 field in the FOV region formed by the magnetic resonance transmit coil of the present invention and a conventional transmit coil;
FIG. 6 is a schematic diagram of an embodiment of a magnetic resonance transmit coil according to the present invention;
FIG. 7 is a schematic diagram of an alternative embodiment of a magnetic resonance transmit coil in accordance with the present invention;
FIG. 8a is a schematic view of one shape of the body end section of the coil body;
FIG. 8b is a schematic view of another shape of the body end section of the coil body;
FIG. 9a is a schematic view of one shape of the layer end of the shield layer;
fig. 9b is a schematic view of another shape of the layer end of the shielding layer.
In fig. 1:
a magnetic resonance transmission coil 1A;
in fig. 4 a-9 b:
a magnetic resonance transmitting coil 10, a coil body 11, a shielding layer 12;
a body middle section 111, a body end section 112;
Detailed Description
Referring to fig. 3a and 3b, fig. 3a and 3b are schematic diagrams showing a comparison of the coil body and shield layer spacing of the magnetic resonance transmitting coil with the field strength.
It has been found that the spacing between the coil body and the shield of the magnetic resonance transmit coil is related to the B1 field strength generated in the FOV area.
In fig. 3a, the distance between the coil body and the shielding layer is D1, and in fig. 3b, the distance between the coil body and the shielding layer is D2, as a comparison, D1 is smaller than D2.
As shown in fig. 3a, when the distance between the coil body and the shielding layer is small, the image current generated on the shielding layer is large, so that the field strength of the corresponding B1 field is small; as shown in fig. 3B, when the distance between the coil body and the shielding layer is larger, the image current generated on the shielding layer is smaller, so that the field strength of the corresponding B1 field is larger.
That is, if the distance between the coil body and the shield layer is increased, the field intensity of the corresponding B1 field can be increased.
To this end, the invention improves the structure of the magnetic resonance transmit coil.
In order that those skilled in the art will better understand the disclosure, the invention will be described in further detail with reference to the accompanying drawings and specific embodiments.
Please refer to fig. 4a to 4c together, wherein fig. 4a is a schematic structural diagram of a magnetic resonance transmit coil according to the present invention; figure 4b is a schematic diagram of another configuration of a magnetic resonance transmit coil provided in accordance with the present invention; fig. 4c is a schematic diagram of another structure of the mr transmit coil according to the present invention.
The magnetic resonance transmitting coil 10 provided by the invention comprises a coil body 11 and a shielding layer 12 which is externally sleeved on the coil body 11, wherein the coil body 11 comprises a body middle section 111 and body end sections 112 which are positioned at two sides of the body middle section 111.
At least one of the two body end sections 112 is at a greater radial distance from the shield layer 12 than the radial distance from the body mid-section 111 to the shield layer 12.
It should be noted that the axial and radial directions described herein are referred to the inner bore of the magnetic resonance transmit coil 10, and the left and right directions of the views shown in fig. 4a to 4b are axial directions, and the up and down directions are radial directions. And defines the inside and outside, the direction near the center of the magnetic resonance transmitting coil 10 is the inside, and the direction far away from the center is the outside.
It should be noted that the middle body section 111 of the coil body 11 is a part with a certain length located in the middle, the remaining part of the side surface is the end body section 112, and the specific length of the middle body section 111, that is, the specific area thereof, can be determined according to actual requirements.
As shown in the foregoing analysis, the distance between the coil body 11 and the shielding layer 12 affects the field strength of the corresponding region, and as can be seen from fig. 2, the B1 field strength of the regions corresponding to the two end positions of the magnetic resonance transmitting coil 10 is relatively small, the radial distance between the body end section 112 of the coil body 11 and the shielding layer 12 of the magnetic resonance transmitting coil 10 provided by the present invention is greater than the radial distance between the body middle section 111 and the shielding layer 12, and by this way, the field distribution of the central region and the edge region is balanced, so that the uniformity of the transmitting field is improved, the B1 field in the FOV region has better uniformity, the way of extending the length of the transmitting coil in the background art is avoided, and the transmitting efficiency can be ensured.
In order to improve the uniformity of the B1 field in the FOV, the radial distance between the two body end sections 112 of the coil body 11 and the shield layer 12 is set to be larger in practical settings.
Referring to fig. 5, fig. 5 is a schematic diagram illustrating a comparison of the B1 field in the FOV area formed by the magnetic resonance transmit coil according to the present invention and the conventional transmit coil.
In fig. 5, the dashed lines indicate the B1 field distribution of the conventional magnetic resonance transmit coil 1A with a cylindrical structure in the FOV area, and the solid lines indicate the B1 field distribution of the magnetic resonance transmit coil 10 provided by the present invention in the FOV area, as can be seen from comparison, the B1 field uniformity of the magnetic resonance transmit coil 10 provided by the present invention in the FOV area is better, and the field strength is only slightly reduced, and the structural design can indeed improve the B1 field uniformity while ensuring the transmit efficiency.
As shown in fig. 4a, in actual installation, only the structure of the coil body 11 may be changed, the structure of the shielding layer 12 is not changed, and the inner cavity of the shielding layer 12 is still cylindrical, that is, the inner diameter of the shielding layer 12 is kept unchanged along the axial direction.
The outer diameter of the body end section 112 of the coil body 11 is set smaller than the outer diameter of the body middle section 111, so that the radial distance between the body end section 112 and the shield layer 12 is greater than the radial distance between the body middle section 111 and the shield layer 12.
In a specific embodiment, the body end sections 112 of the coil body 11 may be arranged in an equal diameter manner, the body middle section 111 of the coil body 11 is also arranged in an equal diameter manner, and the outer diameter of the body middle section 111 is larger than that of the body end section 112, so that a step structure is formed between the body end sections 112 and the body middle section 111.
To further optimize the B1 field uniformity in the FOV area, the outer diameter of the body end section 112 is arranged in a stepwise increasing manner axially inwardly, as can be understood with reference to fig. 8a, and fig. 8a shows a schematic view of the fitting structure of only one body end section 112 of the coil body 11 and the shield layer 12, with the view in fig. 8a, the axially inward direction being the direction from left to right.
The outer diameter of the end section 112 of the coil body is increased gradually in the axial direction, which means that the end section 112 of the coil body is divided into a plurality of sections, and the closer to the center of the coil body 11, the larger the outer diameter of the divided sections is, so that the field intensity of the transmitting field at the corresponding positions of the two end parts of the magnetic resonance transmitting coil 10 can be effectively improved.
Further, in order to obtain a more uniform B1 field distribution in the FOV area, the outer diameter of the body end section 112 continuously increases axially inward, as can be understood with reference to fig. 8B, and fig. 8B shows a schematic view of the mating structure of only one body end section 112 of the coil body 11 and the shield layer 12, with the axially inward direction being the left-to-right direction in the perspective view of fig. 8B.
The outer diameter of the body end section 112 is continuously and gradually increased along the axial direction, so that after the arrangement, the outer diameter of the body end section 112 is in a smooth curve form along the axial direction, the transition of the outer wall of the body end section 112 is smooth, and the adverse effect on a transmitting field is avoided.
As shown in fig. 4b, in actual installation, it is also possible to change only the structure of the shielding layer 12, and the structure of the coil body 11 is not changed, and the whole coil body still has a cylindrical structure, that is, the outer diameter of the coil body 11 is kept unchanged along the axial direction.
The inner diameter of the layer end 122 of the shield layer 12 is set larger than the inner diameter of the layer middle 121 so that the radial distance between the body end section 112 and the shield layer 12 is larger than the radial distance between the body middle section 111 and the shield layer 12.
In a specific embodiment, the layer ends 122 of the shielding layer 12 may be arranged in an equal diameter manner, the layer middle portion 121 of the shielding layer 12 is also arranged in an equal diameter manner, and the inner diameter of the layer middle portion 121 is smaller than that of the layer ends 122, so that a stepped structure is formed between the layer ends 122 and the layer middle portion 121.
To further optimize the uniformity of the B1 field in the FOV area, the inner diameters of the layer ends 122 are arranged in a stepwise decreasing manner axially inward, as can be understood with reference to fig. 9a, a schematic diagram of the structure of the shield layer 12 with the coil body 11 is shown in fig. 9a, and the direction axially inward is a direction from left to right in the view of fig. 9 a.
The inner diameter of the layer end 122 decreases stepwise axially inwardly as can be understood: the layer end 122 is divided into several segments, and the inner diameter of the divided segment is smaller as the segment is closer to the center of the shielding layer 12, so that the field intensity of the transmission field at the corresponding position of the two ends of the magnetic resonance transmission coil 10 can be effectively increased.
Further, in order to obtain a more uniform B1 field distribution in the FOV area, the inner diameter of the layer end portion 122 is continuously decreased axially inward, as can be understood with reference to fig. 9B, fig. 9B shows a schematic view of a structure of the shield layer 12 with which the layer end portion 122 is fitted to the coil body 11, and the axially inward direction is a left-to-right direction in the view of fig. 9B.
The inner diameter of the layer end part 122 is continuously and progressively reduced along the axial direction, and after the arrangement, the inner diameter of the layer end part 122 is in a smooth curve form along the axial direction, so that the transition of the inner wall of the layer end part 122 is smooth, and the adverse effect on a transmitting field is avoided.
As shown in fig. 4c, in actual installation, the structures of the coil body 11 and the shielding layer 12 can also be changed at the same time.
Specifically, the outer diameter of the body end section 112 of the coil body 11 is set smaller than the outer diameter of the body middle section 111, and the inner diameter of the layer end 122 of the shield layer 12 is set larger than the inner diameter of the layer middle 121, so that the radial distance between the body end section 112 and the shield layer 12 is larger than the radial distance between the body middle section 111 and the shield layer 12.
It will be appreciated that the arrangement shown in fig. 4c corresponds to a combination of the arrangement shown in fig. 4a and the arrangement shown in fig. 4b, and that in this configuration, the specific arrangement of the body end section 112 of the coil body 11, and the specific arrangement of the layer end 122 of the shield layer 12, can be understood with reference to the foregoing description, and will not be repeated here.
On the basis of the above solutions, the central structure of the magnetic resonance transmit coil 10 can be improved to better optimize the uniformity of its transmit field.
In a specific scheme, the radial distance between the middle body section 111 of the coil body 11 and the shielding layer 12 gradually increases from the axial center to both sides.
Specifically, only the structure of the body middle section 111 of the coil body 11 may be changed, and the structure of the layer middle 121 of the shield layer 12 is maintained, that is, the outer diameter of the body middle section 111 is gradually reduced toward both sides along the center in the axial direction, similarly to the foregoing, and a continuously reduced manner is preferable.
Specifically, it is also possible to change only the structure of the layer middle part 121 of the shield layer 12, and the structure of the body middle section 111 of the coil body 11 is maintained unchanged, that is, the inner diameter of the layer middle part 121 gradually increases toward both sides along the center in the axial direction, similarly to the foregoing, and preferably continuously increases.
Specifically, the structure of the body middle section 111 of the coil body 11 and the structure of the layer middle part 121 of the shielding layer 12 may be changed at the same time, and the specific form is the same as described above.
It should be noted that, because the uniformity of the field strength corresponding to the middle position of the magnetic resonance transmitting coil 10 is relatively good, the dimension variation range of the middle structure can be smaller than that of the end structure along the axial direction when the magnetic resonance transmitting coil is specifically arranged, and of course, the specific variation degree can be set according to actual requirements.
Referring to fig. 6, fig. 6 is a schematic structural diagram of an embodiment of a magnetic resonance transmit coil according to the present invention.
Fig. 6 exemplarily shows a specific structure of the magnetic resonance transmission coil 10, in which the inner diameter of the shielding layer 12 is kept uniform in the axial direction, the outer diameter of the body middle section 111 of the coil body 11 is continuously decreased toward both sides along the center of the axial direction, the outer diameter of the body end section 112 is continuously increased inward along the axial direction, and the overall structure of the coil body 11 of the magnetic resonance transmission coil 10 is substantially football-shaped.
Referring to fig. 7, fig. 7 is a schematic structural diagram of another embodiment of a magnetic resonance transmit coil according to the present invention.
Fig. 7 exemplarily shows another specific structure of the magnetic resonance transmit coil 10, in which the outer diameter of the coil body 11 is kept consistent in the axial direction, the inner diameter of the shielding layer 12 is continuously increased toward both sides along the axial center, the connection between the layer middle portion 121 and the layer end portion 122 is also smoothly transited, and the layer end portion 122 is designed in a shape of a wide-mouthed bottle.
The magnetic resonance transmit coil provided by the present invention is described in detail above. The principles and embodiments of the present invention are explained herein using specific examples, which are presented only to assist in understanding the method and its core concepts. It should be noted that, for those skilled in the art, it is possible to make various improvements and modifications to the present invention without departing from the principle of the present invention, and those improvements and modifications also fall within the scope of the claims of the present invention.
Claims (9)
1. The magnetic resonance transmitting coil comprises a coil body (11) and a shielding layer (12) sleeved outside the coil body (11); the coil body (11) is characterized by comprising a body middle section (111) and body end sections (112) positioned at two sides of the body middle section (111), wherein the radial distance between at least one of the two body end sections (112) and the shielding layer (12) is larger than the radial distance between the body middle section (111) and the shielding layer (12);
the radial distance between the body end section (112) and the shield (12) decreases axially inward.
2. The magnetic resonance transmit coil of claim 1, wherein the outer diameter of the body end section (112) is stepped inwardly in an axial direction; the inner diameter of the shielding layer (12) is kept uniform along the axial direction.
3. The magnetic resonance transmit coil of claim 1, wherein the body end section (112) has an outer diameter that continuously increases axially inwardly; the inner diameter of the shielding layer (12) is kept uniform along the axial direction.
4. The magnetic resonance transmit coil according to claim 1, characterized in that the outer diameter of the coil body (11) is kept uniform in the axial direction; the inner diameter of the layer end (122) of the shielding layer (12) is gradually reduced inwards along the axial direction.
5. The magnetic resonance transmit coil according to claim 1, characterized in that the outer diameter of the coil body (11) is kept uniform in the axial direction; the inner diameter of the layer end (122) of the shielding layer (12) decreases continuously inward in the axial direction.
6. The magnetic resonance transmit coil of claim 1, wherein the body end section (112) has an outer diameter that increases axially inward and the shield layer (12) has a layer end (122) with an inner diameter that decreases axially inward.
7. The magnetic resonance transmit coil according to any one of claims 1 to 6, wherein a radial distance between the body middle section (111) and the shield layer (12) is gradually increased from a center to both sides in an axial direction.
8. The magnetic resonance transmit coil as set forth in claim 7, wherein the outer diameter of the middle body section (111) is gradually reduced toward both sides along the center in the axial direction.
9. The magnetic resonance transmit coil as set forth in claim 7, wherein the inner diameter of the middle layer portion (121) of the shield layer (12) is gradually increased toward both sides from the center in the axial direction.
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| CN201810031958.5A CN108398657B (en) | 2018-01-12 | 2018-01-12 | Magnetic resonance transmitting coil |
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| CN201810031958.5A CN108398657B (en) | 2018-01-12 | 2018-01-12 | Magnetic resonance transmitting coil |
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| CN108398657B true CN108398657B (en) | 2020-12-29 |
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| CN113203968B (en) * | 2021-04-27 | 2024-02-02 | 上海辰光医疗科技股份有限公司 | Magnetic resonance transmitting coil structure with high transmitting efficiency |
| CN117008027A (en) * | 2022-04-29 | 2023-11-07 | 上海联影医疗科技股份有限公司 | Configuration methods of transmitting coil parameters, radio frequency coil components and equipment |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN1009140B (en) * | 1985-04-01 | 1990-08-08 | 菲利浦光灯制造公司 | Produce and/or receive the rf coil system of alternating magnetic field |
| CN1006579B (en) * | 1985-04-01 | 1990-01-24 | N·V·菲利浦光灯制造公司 | Nuclear magnetic resonance apparatus |
| JPH01206607A (en) * | 1988-02-15 | 1989-08-18 | Mitsubishi Electric Corp | Magnet for generating uniform magnetic field |
| JP2767659B2 (en) * | 1991-12-17 | 1998-06-18 | 信越化学工業株式会社 | Magnetic field generator |
| DE102008060757A1 (en) * | 2008-12-05 | 2010-06-17 | Forschungszentrum Jülich GmbH | Device for generating a homogeneous magnetic field and optimization method |
| US9261574B2 (en) * | 2012-05-02 | 2016-02-16 | General Electric Company | Structured RF coil assembly for MRI scanner |
| CN102749599A (en) * | 2012-07-27 | 2012-10-24 | 中国计量学院 | Magnetic resonance radio-frequency coil based on an alternate impedance micro-strip line |
| DE102015225731B3 (en) * | 2015-12-17 | 2017-04-06 | Bruker Biospin Ag | Easily accessible deep-frozen NMR shim arrangement |
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