CN103576109A - RF coil cooling device for nuclear magnetic resonance imaging - Google Patents
RF coil cooling device for nuclear magnetic resonance imaging Download PDFInfo
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- CN103576109A CN103576109A CN201310578968.8A CN201310578968A CN103576109A CN 103576109 A CN103576109 A CN 103576109A CN 201310578968 A CN201310578968 A CN 201310578968A CN 103576109 A CN103576109 A CN 103576109A
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Abstract
An RF coil cooling device for nuclear magnetic resonance imaging comprises a vacuum conveying pipe, a vacuum container and a vacuum base. The vacuum conveying pipe comprises an inner pipe and an outer pipe, a vacuum layer is arranged between the inner pipe and the outer pipe, and the inner pipe is divided into an input pipe and an output pipe. The vacuum container is connected with the input pipe and the output pipe; the vacuum container is placed in the vacuum base. A groove is formed in the vacuum base and combined with edges of a groove of the vacuum container in a seamless mode. Cooling RF coils are placed in the groove of the vacuum base, and the RF coils are placed on the outer bottom of the vacuum base and used for coupling signals of the cooling RF coils. Refrigerants are conveyed to the groove of the vacuum container through the input pipe, one end of the output pipe is connected with the groove of the vacuum container, and the refrigerants are recycled to a refrigerant storage device through the output pipe.
Description
Technical field
The present invention relates to a kind of magnetic resonance imaging radio-frequency coil cooling device.Relate in particular to a kind of protection by vacuum layer, can stablize for a long time the magnetic resonance radiography radio-frequency coil cooling device using.The present invention will be applicable to every magnetic resonance applications.
Background technology
Magnetic resonance radio frequency (also claiming the magnetic radiography that shakes, magnetic resonance imaging, MRI) is a kind of very important diagnostic imaging instrument clinically.The magnetic radiography that shakes utilizes powerful main field, and most of hydrogen atoms in body are arranged according to main field direction.By instrument, produce the rotary rowed column direction that pulse changes hydrogen atom in body, atomic nucleus will discharge the energy of absorption, the signal that generates electromagnetic waves, then via Computer Analysis, described signal is converted to image, be exactly the magnetic resonance image (MRI) of generally seeing.
In like manner, human body contains a lot of hydrogen nucleis, and itself has again magnetic signature these hydrogen nucleis.Human body is placed in to powerful and uniform nuclear magnetic resonance static magnetic field, recycles specific radio-frequency (RF) radio wave impulse, the in-house hydrogen nuclei of exciting human.
Magnetic resonance system configuration comprises magnet system and radio system.Described magnet system is for generation of magnetic field and the generation gradient fields of high evenness, and described gradient fields realizes NMR signal space coding.Described system configuration comprises three groups of coils, produces respectively the gradient fields of x, y, z direction, by the magnetic field superposition of described coil groups, can obtain the gradient fields of any direction.
Radio system comprises radio frequency (RF) generator and radio frequency (RF) receiver.Radio frequency (RF) generator, for generation of short and strong radio-frequency field, makes the proton in sample produce magnetic resonance (nuclear magnetic resonance is called for short NMR) phenomenon; Radio frequency (RF) receiver gathers NMR signal.
Radio-frequency coil is the shake significant components of transmitting and received RF signal in angiography system of magnetic, and radio-frequency coil performance directly affects the accuracy of quality and the reconstructed results of image.According to magnetic resonance signal to noise ratio and radio-frequency coil temperature, radio-frequency coil resistance, tested object temperature and tested object resistance (Hoult and Richards[1 is shown below]), from document [2]-[6], we can know that reduction radio-frequency coil temperature and resistance can promote the signal to noise ratio of Magnetic resonance imaging effectively.But most document of past all adopts highdensity foam box to do Cryo Equipment.Through the regular hour, foam box is outer can freeze, thereby freezing determinand.So we have proposed the Cryo Equipment design that this novelty can be used for a long time.
The prior art relevant to this patent is described below: High-Tc superconducting receiving coils for nuclear magnetic resonance imaging[7]: take Poly Foam box to be used as Cryo Equipment, but through certain hour, Poly Foam box is outer can freeze, and then freezing determinand.The coil system of taking comprises: high-temperature superconductor receiving coil, signals collecting coil, frequency modulation coil.High-temperature superconductor receiving coil position is fixed, and the relative position that changes signals collecting coil and frequency modulation coil is adjusted frequency.But tuning range is limited, and complicated operation, Q value are not high, thereby cannot accurately adjust to the loss that Energy maximum value causes energy.
United States Patent (USP), the patent No. 5258710, Cryogenic probe for NMR microscopy[8]: use cryogenic liquid to reduce coil temperature, take the direct immersion type of high-temperature superconducting thin film.Sample is positioned in tubule and passes into nitrogen, and it is not frozen.Coil adopts inductance type coupling scheme collection signal, and transmission of signal pattern is: RF signal causes that through signals collecting is coil-induced high-temperature superconducting thin film transmission of signal is to sample.Reception signal mode is: the signal of reception sees through inductive coupling mode and produces image.But the mode of directly soaking meeting loss superconduction self character, and volume is limited, can only make undersized sample.In addition this patent be designed to the design of a plurality of complicated cavities, be difficult for assembling.
United States Patent (USP), the patent No. 7003963, Cooling of receive coil in MRI scanners[9], the currently used Cryo Equipment design in France laboratory, front end is that cold machine is for cooling, stage casing is placed and is transmitted temperature object, uses indirect cooling method to make high-temperature superconducting thin film reach critical temperature.This United States Patent (USP) has designed two vacuum chambers, and shortcoming is that operating aspect need to be lowered the temperature four hours and stage casing placement transmission temperature is the monocrystalline sapphire that cost is high, and Cryo Equipment can only be placed the film that is of a size of 12mm size.
The paper that France laboratory proposes: (a) Development, manufacture and installation of a cryo-cooled HTS coil system for high-resolution in-vivo imaging of the mouse at1.5T, Methods[10] (b) Performance of a Miniature High-Temperature Superconducting (HTS) Surface Coil for In Vivo Microimaging of the Mouse in a Standard1.5T Clinical Whole-Body Scanner[11], the advantage of the high temperature superconductor coil proposing in these two pieces of papers is to protect sample not freeze, and be not immersed in liquid nitrogen, therefore can protect superconducting thin film.The coil system framework of taking is three: superconducting thin film, a matched coil and frequency modulation coil.This device signals collecting mode is complicated, by three coil relative positions, is adjusted.Shortcoming is to need just can reach critical temperature in 4 hours.
From the above mentioned, existing refrigeration plant have that refrigerating efficiency is not high, complex structure, the high shortcoming of cost.
Summary of the invention
The technical problem to be solved in the present invention is to provide quick, simple in structure, the lower-cost magnetic resonance imaging radio-frequency coil of a kind of refrigeration cooling device.
In order to solve above-mentioned technical matters, a kind of magnetic resonance imaging radio-frequency coil cooling device provided by the invention comprises vacuum transmission pipe, vacuum tank, vacuum base.Described vacuum transmission pipe comprises inner and outer tubes, between described inner tube and described outer tube, is vacuum layer, and described inner tube is divided into again input pipe and efferent duct.Described vacuum tank is connected with efferent duct with described input pipe; Described vacuum tank is placed in described vacuum base.Described vacuum base inside is provided with a groove, with the recess edge seamless combination of described vacuum tank.Cooled RF coil is positioned in the groove of described vacuum base, and radio-frequency coil is positioned over described vacuum base outer bottom, and for the signal of the cooled RF coil that is coupled, this mode is called inductance type coupling process (Inductivecoupling).Cold-producing medium is transferred to by described input pipe in the groove of described vacuum tank, and described efferent duct one end connects the groove of described vacuum tank, and cold-producing medium is recycled to cold-producing medium storage device via described efferent duct.
As preferably, described input pipe and efferent duct are connected to form by a spiral pipe and a connecting pipe respectively.
As preferably, described cooled RF coil is body coil.
As preferably, described cooled RF coil is surface coils.
As preferably, described cooled RF coil is birdcage coil.
As preferably, described cooled RF coil is array coil.
As preferably, described vacuum base, vacuum tank, input pipe and efferent duct are made by high rigidity heat-barrier material.
As preferably, described radio-frequency coil is cooling high-temperature superconducting radio-frequency coil.
In sum, a kind of magnetic resonance imaging radio-frequency coil cooling device provided by the invention, simple in structure, by the mode with radio-frequency coil thermo-contact, improve refrigerating efficiency, can have been foreshortened to about 40 minutes cool time, obtained reducing noise, signal to noise ratio improves, and then reaches high image resolution.By the protection of vacuum layer, can extend the life-span of high-temperature superconductor radio-frequency coil simultaneously.
Accompanying drawing explanation
Fig. 1 is that magnetic resonance imaging radio-frequency coil cooling device of the present invention and NMR system are related to schematic diagram;
Fig. 2 A is the stereographic map of magnetic resonance imaging radio-frequency coil cooling device of the present invention;
Fig. 2 B is the sectional axonometric drawing of magnetic resonance imaging radio-frequency coil cooling device of the present invention;
Fig. 3 is the input pipe sectional view of magnetic resonance imaging radio-frequency coil cooling device of the present invention;
Fig. 4 is the efferent duct sectional view of magnetic resonance imaging radio-frequency coil cooling device of the present invention;
Embodiment
Below enumerate in conjunction with the drawings a specific embodiment, in order to describe content of the present invention and details in detail.
With reference to figure 1,2, it is nuclear magnetic resonance image image-forming principle, one determinand 2 is placed in to static magnetic field 5, coordinate that coil 3 excites all nuclear excitations (Excitation) in determinand 2 regions, (Relaxation) signal relaxes, and add gradient (Gradient) magnetic field, then be nuclear magnetic resonance image by coil 3 reception aftertreatments.If understand structure or the functional variation of this region diverse location, change gradient magnetic 4 to determine obtaining cross section in that position.When superconductor temperature, be down to certain critical temperature when following, the motion of electronics in structure is not subject to the impact of lattice completely, and resistance is zero.This external electric field can produce magnetic field, and superconductor temperature is during lower than critical temperature, and the magnetic field in superconductor is discharged completely, forms zero magnetic field state, is diamagnetism.So the object of magnetic resonance imaging radio-frequency coil cooling device 1 is the temperature of coil 3 to be cooled to below critical temperature, thereby effectively utilize zero resistance and the diamagnetism characteristic of superconductor.
With reference to figure 2A, 2B, magnetic resonance imaging radio-frequency coil cooling device is combined by vacuum base 21, vacuum cup 22, vacuum transmission pipe 23,24.Negative pressure when utilization is bled produces vacuum, thereby described vacuum base 21 is closely held with vacuum cup 22, and vacuum chamber is combined as a whole.Utilize the protection of vacuum layer, can block the conduction of low temperature.Described vacuum base 21, vacuum cup 22, vacuum transmission pipe 23,24 can utilize the heat-barrier material of high rigidity to be made, as the glass fibre of high rigidity, glass, quartz glass etc.
With reference to figure 1 and Fig. 3, the feature of described magnetic resonance imaging radio-frequency coil cooling device is to utilize high vacuum insulation, is also called simple vacuum heat-insulation.The vacuum tightness of General Requirements insulated space pressure below 1.33mPa, could eliminate gaseous exchange and conduct heat and most residual gas heat conduction, thereby reach good effect of heat insulation and fast cooling and rewarming effect.This double-walled interlayer keeps pipeline and the container of high vacuum low temperature to be called Dewar pipe (Dewer).In this class heat insulation structural, the heat of the low-temperature space of bleeding is mainly radiation heat, is secondly the heat conduction of a small amount of residual gas and solid element.
Liquid nitrogen is imported the inlet end of spiral input pipe 31 via pipeline 7 by liquid nitrogen storage device 6.The other end of this spiral input pipe 31 connects input connecting pipe 32.Vacuum cup 22 is provided with a groove 33, and the groove 33 that this input connecting pipe 32 connects in vacuum cup 22 can be transferred in the groove 33 of vacuum cup 22 via input connecting pipe 32 liquid nitrogen.Spiral input pipe 31 is the winding of spiral kenel, glass tube can not shunk rapidly because of the temperature decline of moment and cause rupturing.
In vacuum base 21, have a groove 34, utilize the method vacuumizing to be used in conjunction with O-Ring, O-Ring is positioned in ring-like groove 35, and the space in its groove is vacuumized, and makes vacuum base 21 and vacuum cup 22 combinations.Liquid nitrogen is transferred in the groove 33 of vacuum cup 22 through input connecting pipe 32.Because cooled RF coil 8 is positioned in the groove 34 of vacuum base 21, the groove 34 of this vacuum base 21 is interior can place multi-form cooled RF coil 8, for example planar coil, body coil, birdcage coil, array coil.When cooled RF coil 8 is during at working at high speed, can produce high temperature heat conduction occurs, heat is delivered to lower part from the higher part of temperature.Because the temperature of the surfaces externally and internally of heat-barrier material is different, the mode of the heat of working at high speed coil by conduction sees through heat-barrier material and is delivered to the liquid nitrogen in the groove 33 that is temporary in vacuum cup 22, reaches the object of heat radiation.Radio-frequency coil 9 is positioned over the outer bottom of described vacuum base, and for the signal of the cooled RF coil 8 that is coupled, this mode is called inductance type coupling process (Inductive coupling), adopts in this way, can effectively improve the sensitivity of coil.
With reference to figure 1 and Fig. 4, the liquid nitrogen that absorbs heat energy is transferred to outside through efferent duct 24.Efferent duct 24 includes spiral efferent duct 41, output connecting pipe 42.Described spiral efferent duct 41 and described output connecting pipe 42 are in vacuum layer 43.Output connecting pipe 42 one end connect the groove 33 of vacuum cup 22, and the other end is connected with spiral efferent duct 41.After the liquid nitrogen of absorption heat energy is interior via output connecting pipe 42 inflow spiral efferent ducts 41, be discharged to liquid nitrogen storage device 6.Liquid nitrogen storage device 6 is provided with waste material accumulator tank, for storing the liquid nitrogen after use.This liquid nitrogen storage device can arrange retracting device for reclaiming liquid nitrogen to reuse.
Above embodiment is only used for the explanation principle of the invention, not the only embodiment of the present invention.Above-described embodiment should not be considered as limiting the scope of the invention.Those skilled in the art, when reading and having understood aforementioned detailed description, can modify and change.Concrete protection domain should be as the criterion with claims.
Claims (8)
1. a magnetic resonance imaging radio-frequency coil cooling device, comprising:
Vacuum transmission pipe, described vacuum transmission pipe comprises inner and outer tubes, between described inner tube and described outer tube, is vacuum layer, described inner tube is divided into again input pipe and efferent duct;
Vacuum tank, described vacuum tank is connected with described efferent duct with described input pipe;
Vacuum base, described vacuum tank is positioned in described vacuum base, and described vacuum base inside is provided with a groove, with the recess edge seamless combination of described vacuum tank;
Cold-producing medium is transferred to by described input pipe in the groove of vacuum tank, and described efferent duct one end connects the groove of described vacuum tank, and cold-producing medium is recycled to cold-producing medium storage device via the described pipe that spreads out of;
Cooled RF coil is positioned in the groove of described vacuum base, and radio-frequency coil is positioned over the outer bottom of described vacuum base for the signal of the described cooled RF coil that is coupled.
2. magnetic resonance imaging radio-frequency coil cooling device according to claim 1, is characterized in that, described input pipe and efferent duct are connected to form by a spiral pipe and a connecting pipe respectively.
3. magnetic resonance imaging radio-frequency coil cooling device according to claim 1, is characterized in that, described cooled RF coil is surface coils.
4. magnetic resonance imaging radio-frequency coil cooling device according to claim 1, is characterized in that, described cooled RF coil is body coil.
5. magnetic resonance imaging radio-frequency coil cooling device according to claim 1, is characterized in that, described cooled RF coil is birdcage coil.
6. magnetic resonance imaging radio-frequency coil cooling device according to claim 1, is characterized in that, described cooled RF coil is array coil.
7. magnetic resonance imaging radio-frequency coil cooling device according to claim 1, is characterized in that, described vacuum base, vacuum tank, input pipe and efferent duct are made by high rigidity heat-barrier material respectively.
8. magnetic resonance imaging radio-frequency coil cooling device according to claim 1, is characterized in that, described radio-frequency coil is cooling high-temperature superconducting radio-frequency coil.
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| CN201310578968.8A CN103576109A (en) | 2013-11-15 | 2013-11-15 | RF coil cooling device for nuclear magnetic resonance imaging |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106772160A (en) * | 2017-03-13 | 2017-05-31 | 上海纽迈电子科技有限公司 | high temperature radio frequency coil with cooling structure |
| CN107110928A (en) * | 2014-12-31 | 2017-08-29 | 通用电气公司 | System and method for cooling down MR imaging apparatus |
| CN116559743A (en) * | 2023-06-13 | 2023-08-08 | 中国科学院深圳先进技术研究院 | Radio frequency signal receiving system for magnetic resonance imaging |
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| TW201109702A (en) * | 2009-09-10 | 2011-03-16 | Zhi-Hong Chen | Cooling device for magnetic resonance imaging RF coil |
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| CN103116146A (en) * | 2013-02-26 | 2013-05-22 | 江苏美时医疗技术有限公司 | Head radiofrequency coil for magnetic resonance imaging system |
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2013
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Patent Citations (5)
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| CN101191827A (en) * | 2006-11-30 | 2008-06-04 | 通用电气公司 | Low eddy current vacuum vessel and method of making same |
| US7772842B2 (en) * | 2008-09-17 | 2010-08-10 | Time Medical Holdings Company Limited | Dedicated superconductor MRI imaging system |
| TW201109702A (en) * | 2009-09-10 | 2011-03-16 | Zhi-Hong Chen | Cooling device for magnetic resonance imaging RF coil |
| CN102096052A (en) * | 2010-12-17 | 2011-06-15 | 哈尔滨工业大学 | Device and method for testing superconductivity of three-dimensional low-temperature superconducting thin film coil |
| CN103116146A (en) * | 2013-02-26 | 2013-05-22 | 江苏美时医疗技术有限公司 | Head radiofrequency coil for magnetic resonance imaging system |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN107110928A (en) * | 2014-12-31 | 2017-08-29 | 通用电气公司 | System and method for cooling down MR imaging apparatus |
| CN106772160A (en) * | 2017-03-13 | 2017-05-31 | 上海纽迈电子科技有限公司 | high temperature radio frequency coil with cooling structure |
| CN106772160B (en) * | 2017-03-13 | 2023-04-18 | 上海纽迈电子科技有限公司 | High-temperature radio frequency coil with cooling structure |
| CN116559743A (en) * | 2023-06-13 | 2023-08-08 | 中国科学院深圳先进技术研究院 | Radio frequency signal receiving system for magnetic resonance imaging |
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