CN209929075U - Magnetic resonance magnet structure - Google Patents
Magnetic resonance magnet structure Download PDFInfo
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- CN209929075U CN209929075U CN201920454361.1U CN201920454361U CN209929075U CN 209929075 U CN209929075 U CN 209929075U CN 201920454361 U CN201920454361 U CN 201920454361U CN 209929075 U CN209929075 U CN 209929075U
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Abstract
The utility model relates to the technical field of superconducting magnets, and discloses a magnetic resonance magnet structure which comprises two superconducting magnets and a supporting body which are symmetrically arranged, wherein each superconducting magnet comprises a cryostat, a liquid helium container is arranged in the cryostat, the liquid helium containers in the two superconducting magnets are provided with a main coil, a compensation magnetic pole and a shielding coil which are symmetrically arranged from inside to outside as a whole, and the main coil and the shielding coil are superconducting coils; the support body is arranged between the two superconducting magnets and is of a hollow structure, and the two superconducting magnets are communicated with the support body. The utility model discloses a magnetic resonance magnet structure open degree is big to can produce the imaging region of high degree of consistency in open space, be used for carrying out the quick formation of image of magnetic resonance, and the formation of image high quality helps the doctor to intervene the treatment according to the formation of image result.
Description
Technical Field
The utility model relates to a superconducting magnet technical field especially relates to a magnetic resonance magnet structure.
Background
Interventional therapy is an emerging therapeutic means combining image diagnosis and clinical therapy which is rapidly developed in recent years. Under the guidance and monitoring of digital subtraction angiography machine, CT, ultrasonic and magnetic resonance imaging equipment, puncture needle, catheter and other interventional devices are used to introduce specific instrument into the pathological change part of human body via natural pore canal or small wound for minimally invasive treatment. The current interventional therapy is a clinical three-major branch discipline which is parallel to the traditional internal medicine and surgery.
The more mature interventional treatment schemes at present are ultrasound interventional treatment and CT interventional treatment.
The ultrasonic interventional therapy is to complete various operations such as puncture biopsy, X-ray radiography, suction, intubation, drug injection treatment and the like under the monitoring or guidance of real-time ultrasonic waves, replaces certain surgical operations and achieves the effect which is comparable to or even better than the surgical operations.
The ultrasonic interventional therapy technology has the advantages of real-time performance, micro-wound performance, safety, no toxic or side effect, good inactivation effect, small damage to normal tissues and the like. However, limitations in certain aspects have limited further development of this technology. Firstly, the technology has high requirements on the experience of doctors, and the rapid popularization and the promotion of the technology are restricted; secondly, the ultrasonic image has poor display effect on hollow organs such as lung and the like, and cannot be used for surgical guidance of relevant parts; when the operation is performed under the guidance of the ultrasonic image, the visual field provided by the two-dimensional image to a doctor is limited, and the spatial position and shape information of the tumor are difficult to accurately display, so that an interventional tool is difficult to accurately place according to an operation planned path, and the condition that part of cancer cells are not dead or part of normal cells are dead is easily caused, thereby affecting the treatment effect.
The CT interventional therapy has high density resolution and spatial resolution, can accurately locate the pathological changes, and can clearly know the conditions of soft tissues inside and around the pathological changes, thereby avoiding important structures or necrotic tissues, providing exact needle insertion angle and depth, being capable of being adjusted at any time under scanning monitoring, accurately obtaining materials and creating a foundation for clearly diagnosing the pathological changes. In the operation based on CT image guidance, the image resolution and the display effect are better than those of ultrasonic images, but the method has the defect that the CT radioactive irradiation has great damage to patients and doctors. The risk of cancer for doctors and patients increases due to radioactive radiation, the probability of carcinogenesis is proportional to the radioactive dose to which they are subjected, and the plan for CT interventional therapy is even less acceptable for doctors, since the radiation accumulation over the years inevitably leads to serious physical damage to the doctor, which is even far greater than the radiation dose to which the patient is subjected.
Based on the defects of unclear image, large application limitation and large radiation damage in CT interventional therapy, the magnetic resonance interventional therapy is a new technology developed in recent years, and the purpose of diagnosing or treating diseases can be achieved by applying a magnetic resonance guide instrument. As an interventional guidance tool, the magnetic resonance has incomparable advantages compared with other imaging methods, the tissue contrast is excellent, the spatial resolution reaches submillimeter level, the magnetic resonance is beneficial to lesion location and interventional guidance, more importantly, the magnetic resonance has the capacity of multi-plane and three-dimensional volume reconstruction, and the important anatomical relation between an interventional target focus and adjacent tissues can be comprehensively evaluated.
The most important condition for performing a magnetic resonance interventional procedure is that the magnet system allows the physician to access the patient and perform the interventional procedure. The easier it is to reach the patient's system, the better its interventional performance. The existing open type magnetic resonance system can meet the requirement of magnetic resonance interventional therapy. A disadvantage of magnetic resonance interventions compared to ultrasound interventions and CT interventions is their inadequate openness.
In addition, most of the early magnetic resonance systems for interventional therapy are C-type or frame-type permanent magnetic resonance systems, the imaging quality is often not ideal enough, and the real-time performance of interventional therapy is difficult to meet. The imaging quality of the magnetic resonance system is often related to the magnetic field of the imaging area, and the larger the magnetic field is, the higher the imaging quality is, and the implementation of the real-time imaging technology is facilitated. Therefore, the high-field open magnetic resonance system becomes a development hotspot and trend of magnetic resonance interventional therapy.
SUMMERY OF THE UTILITY MODEL
Based on the above, an object of the utility model is to provide a magnetic resonance magnet structure to it is little to solve among the prior art magnetic resonance magnet structure openness, the poor scheduling problem of imaging quality in open space.
In order to achieve the purpose, the utility model adopts the following technical proposal:
a magnetic resonance magnet structure comprising:
the superconducting magnets are symmetrically arranged, each superconducting magnet comprises a cryostat, a liquid helium container is arranged in the cryostat, a main coil, a compensation magnetic pole and a shielding coil which are symmetrically arranged are arranged in the two superconducting magnets from inside to outside as a whole, and the main coil and the shielding coil are superconducting coils; and
the supporting body is arranged between the two superconducting magnets and is of a hollow structure, and the two superconducting magnets are communicated with the supporting body.
Preferably, the two superconducting magnets are arranged in a vertically symmetrical manner, the supporting bodies are supporting columns, and the two superconducting magnets are communicated with each other through at least one supporting column.
Preferably, the periphery of the cryostat is circular, two support columns are arranged along the circumferential direction of the cryostat, and the included angle between the two support columns is 130-160 degrees.
Preferably, each cryostat is communicated with the supporting upright post, and the communicated space is in a vacuum environment.
Preferably, each of the liquid helium vessels is in communication with the support column.
Preferably, the compensation magnetic pole is made of a ferromagnetic material.
Preferably, two of the cryostats are internally provided with symmetrically arranged shimming modules, and the shimming modules are positioned between the main coils.
The utility model discloses a magnetic resonance magnet structure, its open degree is big to produce the imaging region of high degree of consistency in the open space between the superconducting magnet, be used for carrying out the quick formation of image of magnetic resonance, thereby realize the real-time formation of image when interveneeing the treatment, and the high quality of formation of image helps the doctor to intervene the treatment according to the formation of image result.
Drawings
In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the drawings required to be used in the description of the embodiments of the present invention will be briefly described below, and it is obvious that the drawings in the following description are only some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to the contents of the embodiments of the present invention and the drawings without creative efforts.
Fig. 1 is a schematic structural diagram of a magnetic resonance magnet structure according to an embodiment of the present invention;
fig. 2 is a schematic cross-sectional view of a magnetic resonance magnet structure according to an embodiment of the present invention;
fig. 3 is a flowchart of a coil and compensation magnetic pole size optimization algorithm according to an embodiment of the present invention;
fig. 4 is a schematic diagram of feasible region division of a coil and compensation magnetic pole size optimization algorithm provided by the embodiment of the present invention;
fig. 5 is a schematic diagram of a calculation result of an optimization algorithm for coil and compensation magnetic pole sizes according to an embodiment of the present invention.
In the figure:
1-a superconducting magnet; 11-a cryostat; 12-liquid helium vessel; 13-a primary coil; 14-compensation magnetic pole; 15-a shield coil; 16-a shimming module; 2-a support; 3-feasible area of the main coil; 4-compensating the feasible area of the magnetic pole; 5-shielding the feasible area of the coil; 6-an imaging region; 7-grid clustering.
Detailed Description
In order to make the technical problems, technical solutions and technical effects achieved by the present invention more clear, the embodiments of the present invention will be described in further detail with reference to the accompanying drawings, and obviously, the described embodiments are only some embodiments, not all embodiments of the present invention. Based on the embodiments in the present invention, all other embodiments obtained by those skilled in the art without creative efforts belong to the protection scope of the present invention.
As shown in fig. 1 to 2, the present embodiment provides a magnetic resonance magnet structure including two superconducting magnets 1 and a support body 2, which are symmetrically arranged. Each superconducting magnet 1 comprises a cryostat 11, a liquid helium container 12 is arranged in the cryostat 11, the liquid helium containers 12 in the two superconducting magnets 1 are integrally provided with a main coil 13, a compensation magnetic pole 14 and a shielding coil 15 which are symmetrically arranged from inside to outside, and the main coil 13 and the shielding coil 15 are superconducting coils; the supporting body 2 is arranged between the two superconducting magnets 1 and is of a hollow structure, and the two superconducting magnets 1 are communicated with the supporting body 2. It should be noted that the shielding coil 15 is opposite to the current direction in the main coil 3 to reduce the external leakage magnetic field of the superconducting magnet 1, so as to reduce the electromagnetic interference to other external detection equipment and office equipment, so that the layout of the whole interventional therapy equipment is more compact, while the existing open magnet structure usually uses pure iron to shield the leakage magnetic field, and the weight of the existing open magnet structure is generally more than 20 tons, whereas the superconducting magnet 1 of the present embodiment has only 4-5 tons, and is smaller in weight and lower in cost.
Compared with the prior art, the magnetic resonance magnet structure provided by the utility model has the advantages that the two superconducting magnets 1 and the support body 2 form an open space, the degree of openness is large, and a doctor can conveniently enter the magnet structure from multiple angles to perform interventional therapy; secondly, by arranging the main coil 13, the compensation magnetic pole 14 and the shielding coil 15 which are symmetrically arranged in the liquid helium container 12, the main coil 13 and the shielding coil 15 are superconducting coils which are in a superconducting state in an extremely low temperature liquid helium environment and can bear larger current than a normal temperature copper wire, so that a magnetic field larger than a permanent magnet and the normal temperature copper wire can be generated, and an imaging area 6 with high uniformity of a certain size is generated in an open space between the superconducting magnets 1 for carrying out magnetic resonance fast imaging, so that real-time imaging during interventional therapy is realized, the imaging quality is high, and a doctor is helped to carry out interventional therapy according to an imaging result. It should be noted that the imaging region 6 is a spherical region with a diameter of 30-50cm and a magnetic field strength greater than 1T.
In this embodiment, the two superconducting magnets 1 are symmetrically arranged up and down, the supporting body 2 is a supporting column, and connects the two superconducting magnets 1 up and down, and the two superconducting magnets 1 are communicated with each other through at least one supporting column. Preferably, the cryostat 11 is formed by combining a cylinder and a circular truncated cone, two support columns are arranged along the circumferential direction of the cryostat 11, and the included angle between the two support columns is 130 degrees and 160 degrees. It should be noted that a certain included angle exists between the two supporting columns to form a double channel, so that a doctor can conveniently arrange the position of a sickbed or perform interventional therapy operation from the front and back or the left and right directions. The included angle of the supporting columns is set to 130 degrees and 160 degrees so as to balance the structural stability of the superconducting magnet 1.
Further, the superconducting magnet 1 includes two cryostats 11 disposed in an up-down symmetrical manner, each cryostats 11 is communicated with the support column, and the communication space is a vacuum environment. Each cryostat 11 includes a liquid helium vessel 12 therein, and the liquid helium vessel 12 is disposed in a vacuum environment to reduce external heat leakage to the liquid helium vessel 12 and achieve zero volatilization of liquid helium. The two liquid helium containers 12 which are symmetrically arranged up and down are communicated with the inside of the supporting upright column to form a whole, so that a single refrigerating machine can be used for providing refrigerating capacity for the liquid helium containers 12, the manufacturing cost of the superconducting magnet 1 is saved, and the power consumption during use is reduced.
Further, the cryostat 11 is provided with symmetrically arranged shimming modules 16 therein, in this embodiment, a pair of symmetric shimming modules 16 are arranged above and below, and the shimming modules 16 are located between the upper and lower main coils 13. The shimming module 16 is used to further improve the magnetic field uniformity of the imaging region 6 and improve the imaging quality, so as to facilitate the implementation of a fast scanning imaging sequence and meet the real-time imaging requirements of interventional therapy. The shimming module 16 is positioned in a groove outside the cryostat 11, and leaves enough space for installing the slab gradient without exceeding the groove plane of the cryostat 11, so that the openness of the superconducting magnet 1 is not influenced, thereby providing enough intervention space for doctors and improving the convenience of doctor intervention operation.
The compensation magnetic pole 14 can be made of ferromagnetic materials such as pure iron and silicon steel sheets, and is used for increasing the magnetic field intensity of the imaging area 6, reducing the wire amount for the superconducting coil and reducing the manufacturing cost of the superconducting magnet 1. The compensation magnetic pole 14 is positioned in the liquid helium environment in the liquid helium container 12, so that the magnetic conductivity of the compensation magnetic pole 14 is not influenced by the temperature change of the external environment, the stability of magnetic resonance imaging is enhanced, and the operation quality of a doctor in interventional therapy is ensured.
As shown in fig. 3 to 5, the present embodiment further provides a coil and compensation magnetic pole size optimization algorithm, which specifically includes the following steps:
1) according to the symmetry, the coil solution area can be set as a quarter model, and the feasible areas of the main coil 13, the shielding coil 15 and the compensation magnetic pole 14 are determined according to the boundary area of the superconducting magnet 1.
2) The initial number and the initial size of the compensation magnetic poles 14 are preset in the compensation magnetic pole possible area 4, and optionally, the number of the compensation magnetic poles 14 is 3-5, so that the processing and the manufacturing are convenient.
3) And (3) carrying out grid division on the feasible region 3 of the main coil and the feasible region 5 of the shielding coil, dividing the feasible regions into M multiplied by N grids, wherein each grid can be equivalent to a current loop.
4) And calculating the magnetic field contribution of the compensation magnetic poles 14 to the imaging region 6 through a finite element algorithm, establishing a linear relation between the current in each grid and the magnetic field intensity of the imaging region 6, and performing linear programming on the optimization model to obtain a global optimal solution with the least superconducting wire consumption.
5) Through linear programming calculation, if the calculation result is converged, a grid current distribution diagram in a feasible region of the main coil 13 and a feasible region of the shielding coil 15 can be obtained, the coil current is split into a plurality of grid clusters 7, each grid cluster 7 can be equivalent to a superconducting coil, and then the initial sizes of the main coil 13 and the shielding coil 15 are determined according to the size of the grid cluster 7; and if the calculation result is not converged, returning to the step 1) for recalculation.
6) The nonlinear programming calculation is performed with the initial dimensions of each of the compensation magnetic pole 14, the main coil 13, and the shield coil 15 as arguments, and with the amount of wire for the superconducting coil or the magnetic field uniformity of the imaging region 6 as an objective function.
7) If the convergence value obtained by the nonlinear programming calculation meets the preset convergence condition, the optimal sizes of the compensation magnetic pole 14, the main coil 13 and the shielding coil 15 are obtained; and if the convergence value obtained by the nonlinear programming calculation does not meet the preset convergence condition, returning to the step 1) for recalculation.
It should be noted that the linear programming may adopt various algorithms, such as inner product point, simplex method, and the like. The nonlinear programming may employ a variety of algorithms, such as genetic algorithms, sequential quadratic programming algorithms, simulated annealing algorithms, and the like.
The utility model discloses a magnetic resonance magnet structure that provides, open degree is big to produce the imaging region 6 of high degree of consistency in the open space between superconducting magnet 1, be used for carrying out the quick formation of image of magnetic resonance, thereby realize the real-time formation of image when interveneeing the treatment, and the high quality of formation of image helps the doctor to intervene the treatment according to the formation of image result.
The utility model discloses a coil, compensation magnetic pole size optimization algorithm that provide optimize main coil 13 and shield coil 14 with the line volume for this magnet structure is more compact, and the installation of being convenient for reduces its manufacturing cost.
It should be noted that the foregoing is only a preferred embodiment of the present invention and the technical principles applied. It will be understood by those skilled in the art that the present invention is not limited to the particular embodiments described herein, but is capable of various obvious changes, rearrangements and substitutions as will now become apparent to those skilled in the art without departing from the scope of the invention. Therefore, although the present invention has been described in greater detail with reference to the above embodiments, the present invention is not limited to the above embodiments, and may include other equivalent embodiments without departing from the scope of the present invention.
Claims (5)
1. A magnetic resonance magnet structure, comprising:
the superconducting magnet comprises two superconducting magnets (1) which are symmetrically arranged, each superconducting magnet (1) comprises a cryostat (11), a liquid helium container (12) is arranged in each cryostat (11), main coils (13), compensation magnetic poles (14) and shielding coils (15) which are symmetrically arranged are arranged on the liquid helium containers (12) in the two superconducting magnets (1) from inside to outside as a whole, and the main coils (13) and the shielding coils (15) are superconducting coils; and
the supporting body (2) is arranged between the two superconducting magnets (1), the supporting body (2) is of a hollow structure, and the two superconducting magnets (1) are communicated with the supporting body (2); the two superconducting magnets (1) are arranged in an up-down symmetrical mode, the supporting bodies (2) are supporting upright columns, and the two superconducting magnets (1) are communicated through at least one supporting upright column;
the periphery of the cryostat (11) is circular, the two support columns are arranged along the circumferential direction of the cryostat (11), and the included angle between the two support columns is 130 degrees and 160 degrees.
2. A magnetic resonance magnet structure according to claim 1, characterized in that each cryostat (11) is in communication with the support column, the communication space being a vacuum environment.
3. A magnetic resonance magnet structure according to claim 2, characterized in that each liquid helium vessel (12) communicates with the support column.
4. A magnetic resonance magnet structure according to claim 1, characterized in that the compensation pole (14) is made of a ferromagnetic material.
5. A magnetic resonance magnet structure according to claim 1, characterized in that symmetrically arranged shim modules (16) are provided within both cryostats (11), the shim modules (16) being located between the main coils (13).
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| CN201920454361.1U CN209929075U (en) | 2019-04-04 | 2019-04-04 | Magnetic resonance magnet structure |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109859924A (en) * | 2019-04-04 | 2019-06-07 | 苏州八匹马超导科技有限公司 | A kind of magnetic resonance magnet structure and the dimensionally-optimised algorithm of coil, compensating pole |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
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| CN109859924A (en) * | 2019-04-04 | 2019-06-07 | 苏州八匹马超导科技有限公司 | A kind of magnetic resonance magnet structure and the dimensionally-optimised algorithm of coil, compensating pole |
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