CN202189138U - Radio-frequency coil device for magnetic resonance imaging - Google Patents
Radio-frequency coil device for magnetic resonance imaging Download PDFInfo
- Publication number
- CN202189138U CN202189138U CN2011203252167U CN201120325216U CN202189138U CN 202189138 U CN202189138 U CN 202189138U CN 2011203252167 U CN2011203252167 U CN 2011203252167U CN 201120325216 U CN201120325216 U CN 201120325216U CN 202189138 U CN202189138 U CN 202189138U
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- coil
- backbone transport
- magnetic resonance
- leads
- resonance imaging
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Abstract
The utility model belongs to the technical field of the magnetic resonance imaging and particularly relates to a radio-frequency coil device for magnetic resonance imaging, comprising two main transmission wires and a coil group. The coil group is formed by arraying a plurality of same ring-like coils in parallel; as a received signal antenna, each ring-like coil is made of conductive alloy or metal; the upper part of each ring-like coil is provided with an opening; the two main transmission wires are made of high conductive alloy or metal and arranged on one side of the coil group; the two main transmission wires are separated from the coil group by insulating material; the bottom of each ring-like coil is provided with a resonant capacitor; and the lower part of the outer side of each ring-like coil is provided with a mutual-inductance decoupling capacitor and a coupling capacitor. The radio-frequency coil device for magnetic resonance imaging has the advantages of low attenuation, high sensitivity, simple structure and low cost.
Description
Technical field
The utility model belongs to the mr imaging technique field, is specifically related to a kind of coil device that is used for magnetic resonance imaging.
Background technology
Nuclear magnetic resonance image system (MRI) uses the uniform strong magnetic field of autonomous magnetic system to excite magnetic moment to produce nuclear magnetic resonance (NMR) signal through uniform radio frequency (RF) magnetic field (be called and excite magnetic field or B1 magnetic field).The power of this radio-frequency sending coil is by computer control.In excitation process, the nuclear spin system absorbs energy.After exciting, the magnetic moment of precession will experience free induction decay (FID) and discharge the energy of its absorption and return stable state.In free induction decay (FID), use to be placed near the received RF coil that sample (human body) is excited the part and to survey nuclear magnetic resonance (NMR) signal.
In nuclear magnetic resonance image system (MRI), the sensitivity of receiving coil is a key factor of high quality graphic.The sensitivity that influences receiving coil is caused with absorption of sample by the lead decay, and the long resistance decrement that brings of winding wire is the main cause of no-load decay, and it is the reason that has load to decay that the signal of reception returns through coil that sample (human body) is absorbed.Usually adopt two big types of whole-body radio frequency coil and phased coils at present.Decay of whole coil lead and human body decay are very serious, and sensitivity is low, and phased coil solves two problems basically but the complicated cost of external circuit is high.The utility model combines both advantages, and phased coil effectively is combined into whole coil.
Summary of the invention
The purpose of the utility model is to provide a kind of decay little, highly sensitive, simple in structure, the coil device that is used for magnetic resonance imaging that cost is low.
The coil device that is used for magnetic resonance imaging that the utility model provides comprises two backbone transport leads 1 and coil groups 2.Wherein, said coil groups 2 is made up of the coil parallel arranged that several are similarly annular, and as receiving signal antenna, each toroid winding is processed by electrical conductivity alloy or metal, and each toroid winding top is provided with opening; Said two backbone transport leads 1 are processed by high electrical conductivity alloy or metal; Dimensions length is any, has the characteristic of low decay, and two backbone transport leads 1 discharge side by side; And be arranged at a side of coil groups 2, isolate through insulating material between backbone transport lead 1 and the coil groups 2; The width of backbone transport lead 1, thickness, and distance between two backbone transport leads 1, the triadic relation satisfy the transfer impedance set (as among the embodiment 50 ohm) be advisable; Bottom in each toroid winding is provided with resonant capacitance 3, makes each toroidal resonance frequency and frequency of operation equate, to obtain the highest sensitivity; Bottom in each toroid winding outside is provided with mutual inductance decoupling capacitance 4 near center position; Toroid winding connects mutually through mutual inductance decoupling capacitance 4; And for easy for installation and minimizing intercoupling; This mutual inductance decoupling capacitance 4 is installed in backbone transport lead 1 top; The effect of said mutual inductance decoupling capacitance 4 is the mutual inductances between bucking coil and the coil, realizes being independent of each other between the coil less than being coupled, making between coil and the coil and realizing that the energy of a coil is not delivered to another coil; Also be provided with a coupling capacitance 5 in coil groups 2 outer lower portion, this coupling capacitance 5 also is installed in backbone transport lead 1 top, and parallel connection access backbone transport lead 1, and principle is as shown in Figure 2; Be connected with circuit as IO interface through connecting line 6 on the backbone transport lead 1, connecting line 6 adopts coaxial (50 ohm) transmission line, and the outer conductor of coaxial transmission line and inside conductor connect two leads of backbone transport lead 1 respectively.
The advantage of the utility model is to decay little, and is highly sensitive, simple in structure, and cost is low.
Description of drawings
Fig. 1 is the apparatus structure synoptic diagram.
Fig. 2 is the apparatus structure circuit theory diagrams.
Label among the figure: 1 is the backbone transport lead, and 2 is coil groups, and 3 is resonant capacitance, and 4 are mutual inductance uncoupling electric capacity, and 5 is coupling capacitance.
Embodiment
Further specifically describe the utility model below in conjunction with accompanying drawing and embodiment.
As depicted in figs. 1 and 2.With internal orifice footpath diameter is that 400mm, wall thickness are that the copper pipe of 2mm cuts into 4 high rings of 50mm.Then each loop wire is cut into crescent as shown in Figure 1, make crescent coil groups 2, its line width is 5mm.Resonant capacitance (3) adopts 300pF not have magnetocapacitance, and coupling capacitance (5) adopts 10pF not have magnetocapacitance, and mutual inductance uncoupling electric capacity (4) adopts 30pF not have magnetocapacitance.The live width of backbone 1 is 3mm, and thickness is 1mm, and the spacing of two backbones 1 is 10mm, and its impedance is 50 ohm.The double-layer coaxial shielding line of connecting line 6 usefulness 5mm50 ohms.Install to be connected with Fig. 1 by schematic diagram 2 and get final product.
Claims (1)
1. a coil device that is used for magnetic resonance imaging is characterized in that comprising two backbone transport leads (1) and coil groups (2); Wherein, said coil groups (2) is made up of the coil parallel arranged that several are similarly annular, and as receiving signal antenna, each toroid winding is also processed by electrical conductivity alloy or metal, and each toroid winding top is provided with opening; Said two backbone transport leads (1) are processed by electrical conductivity alloy or metal, discharge side by side, and are arranged at a side of coil groups (2), isolate through insulating material between backbone transport lead (1) and the coil groups (2); Width, the thickness of backbone transport lead (1), and distance between two backbone transport leads (1), the triadic relation satisfies the transfer impedance of setting; In each toroid winding, be provided with resonant capacitance (3), make each toroidal resonance frequency and frequency of operation equal corresponding to the bottom of openend; Be respectively arranged with mutual inductance decoupling capacitance (4) corresponding to each toroidal bottom near center position, toroid winding connects mutually through mutual inductance decoupling capacitance (4); Also be provided with a coupling capacitance (5) in coil groups (2) outer lower portion, this coupling capacitance (5) is installed on the backbone transport lead (1), and parallel connection inserts backbone transport lead (1); Backbone transport lead (1) is connected with circuit as IO interface through connecting line (6), and connecting line (6) adopts coaxial transmission line, and the outer conductor of coaxial transmission line and inside conductor connect two leads of two backbone transport leads (1) respectively.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN2011203252167U CN202189138U (en) | 2011-09-01 | 2011-09-01 | Radio-frequency coil device for magnetic resonance imaging |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN2011203252167U CN202189138U (en) | 2011-09-01 | 2011-09-01 | Radio-frequency coil device for magnetic resonance imaging |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN202189138U true CN202189138U (en) | 2012-04-11 |
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Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN2011203252167U Expired - Lifetime CN202189138U (en) | 2011-09-01 | 2011-09-01 | Radio-frequency coil device for magnetic resonance imaging |
Country Status (1)
| Country | Link |
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| CN (1) | CN202189138U (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| TWI572880B (en) * | 2012-10-04 | 2017-03-01 | Aichi Steel Corp | Magnetic impedance element and manufacturing method thereof |
| CN106821500A (en) * | 2017-03-21 | 2017-06-13 | 大连锐谱科技有限责任公司 | One kind is used for minimally invasive operation navigating system and method |
| CN111157929A (en) * | 2018-11-08 | 2020-05-15 | 西门子医疗有限公司 | Local coil with integrated pilot tone transmitter |
| CN115371538A (en) * | 2022-09-22 | 2022-11-22 | 中国工程物理研究院材料研究所 | Eddy film thickness sensor |
-
2011
- 2011-09-01 CN CN2011203252167U patent/CN202189138U/en not_active Expired - Lifetime
Cited By (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| TWI572880B (en) * | 2012-10-04 | 2017-03-01 | Aichi Steel Corp | Magnetic impedance element and manufacturing method thereof |
| CN106821500A (en) * | 2017-03-21 | 2017-06-13 | 大连锐谱科技有限责任公司 | One kind is used for minimally invasive operation navigating system and method |
| CN106821500B (en) * | 2017-03-21 | 2023-11-17 | 南京拓谱医疗科技有限公司 | Navigation system for minimally invasive surgery |
| CN111157929A (en) * | 2018-11-08 | 2020-05-15 | 西门子医疗有限公司 | Local coil with integrated pilot tone transmitter |
| US11340322B2 (en) | 2018-11-08 | 2022-05-24 | Siemens Healthcare Gmbh | Local coil with integrated pilot tone transmitter |
| CN111157929B (en) * | 2018-11-08 | 2022-07-08 | 西门子医疗有限公司 | Local coil with integrated pilot tone transmitter |
| CN115371538A (en) * | 2022-09-22 | 2022-11-22 | 中国工程物理研究院材料研究所 | Eddy film thickness sensor |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CX01 | Expiry of patent term | ||
| CX01 | Expiry of patent term |
Granted publication date: 20120411 |