CN109859924A - A kind of magnetic resonance magnet structure and the dimensionally-optimised algorithm of coil, compensating pole - Google Patents
A kind of magnetic resonance magnet structure and the dimensionally-optimised algorithm of coil, compensating pole Download PDFInfo
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Abstract
The present invention relates to superconducting magnet technical fields, a kind of magnetic resonance magnet structure is disclosed, including two symmetrically arranged superconducting magnets and supporter, each superconducting magnet includes cryostat, liquid helium vessel is provided in cryostat, and two intracorporal liquid helium vessels of superconducting magnetic are integral the main coil, compensating pole and shielded coil for being provided be arranged symmetrically from inside to outside, main coil and shielded coil are superconducting coil, supporter is set between two superconducting magnets, and be hollow structure, two superconducting magnets are connected with supporter；The magnet structure degree of opening is big, and the imaging region of high evenness can be generated in open space, and to carry out magnetic resonance fast imaging, and image quality is high, facilitates doctor according to imaging results and carries out interventional therapy；Invention additionally discloses a kind of coil, the dimensionally-optimised algorithm of compensating pole, being easily installed with line amount so that the magnet structure is more compact for main coil and shielded coil is optimized, its manufacturing cost is reduced.
Description
Technical field
The present invention relates to superconducting magnet technical field more particularly to a kind of magnetic resonance magnet structure and coils, compensating pole
Dimensionally-optimised algorithm.
Background technique
Interventional therapy is that one developed rapidly in recent years has merged diagnostic imaging and clinical treatment in the emerging of one
Treatment means.It is the benefit under the guidance and monitoring of the image documentation equipments such as digital subtraction angiography machine, CT, ultrasound and magnetic resonance
With puncture needle, conduit and other interposers materials, specific instrument is imported by human body by human body natural duct or small wound
Diseased region carries out a series of general name for the treatment of technologies of minimally-invasive treatment.At present interventional therapy have become with traditional internal medicine,
The surgery big pillar subject of clinic three arranged side by side.
The percutaneous coronary intervention of comparative maturity is ultrasonic interventional therapy and CT interventional therapy at present.
Ultrasonic interventional therapy is to complete various aspiration biopsies, x-ray radiography and pumping under the monitoring or guidance of real-time ultrasound
The operation such as suction, intubation, drug-injection in treatment, replaces certain surgical operations, reach compare favourably with surgical operation, even more preferably effect.
Ultrasonic interventional therapy technology is with real-time, minimally invasive, safe and free of toxic and side effects, inactivating efficacy is good, normal tissue damage
Hurt the advantages that small.But limitation in some aspects limits the further development of this technology.One, the technology is to doctor
Skill requirement is very high, constrains the quick universal of this technology and promotes；Two, ultrasonic image shows the hollow organs such as lung
Effect is poor, can not carry out the operation guidance of region of interest；Three, when being performed the operation under ultrasonic image guidance, bidimensional image is mentioned
Supply the limited view of doctor, it is difficult to accurate display tumor space location and shape information so that intervention tool is difficult according to hand
The case where art intended path is accurately placed, and be easy to cause part cancer cell not dead or part Normal cell death, to influence
Therapeutic effect.
CT interventional therapy has very high density resolution and spatial resolution, to lesion accurate positioning, and can be clear
Solve lesion and the case where surrounding soft tissue, to avoid important feature or necrotic tissue, provide exact needle angle and
Depth, and can be adjusted at any time under scanning monitoring, accomplish accurately to draw materials, creates basis for the pathological diagnosis of clear lesion.It is based on
In the operation of CT images guidance, image resolution and display effect are better than ultrasonic image, but the shortcomings that this method is
CT radio exposure is larger to the damage of patient and doctor.Radioactive radiation meeting is so that the risk of doctor and patients' cancer increases
Add, and the radio exposure dose proportional that cancerigenic probability is subjected to it, for doctor, the scheme of CT interventional therapy is more not
Acceptable, because radiation accumulation month after month throughout the year necessarily causes doctor's body to be badly damaged, this degree of injury is even much big
In the dose of radiation that patient is born.
It is unintelligible based on ultrasonic interventional therapy image, using the disadvantage that limitation is big and CT interventional therapy radiation injury is big, magnetic
Resonance interventional therapy is the new technology that developed recently gets up, and can reach diagnosis using guided by magnetic resonance instrument or treats the mesh of disease
's.As intervention steering tool, the advantage that magnetic resonance has other Imaging Methods incomparable, tissue contrast is excellent, empty
Between resolution ratio reach submillimeter level, to lesion position and its intervene guidance it is beneficial, it is often more important that magnetic resonance have more planes and
The ability of Multi-slice spiral CT, can thoroughly evaluating intervention target stove and adjacent tissue important anatomy relationship.
It carries out MR-guided interventional and treats most important condition to be that magnet system can allow for doctor to contact patient and be situated between
Enter operation.The system for more readily accessing patient, intervention performance are better.Current open type magnetic resonance system, can satisfy
The needs of MR-guided interventional treatment.MR-guided interventional is that its degree of opening is inadequate compared to Ultrasound intervention and the CT disadvantage intervened.
In addition, early stage is mostly c-type or frame-type permanent magnetism magnetic resonance system for the magnetic resonance system of interventional therapy, at
Image quality amount is often not ideal enough, and the real-time of interventional therapy is difficult to meet.The image quality of magnetic resonance system is often imaged with it
The magnetic field in region is related, and magnetic field is bigger, then its image quality is higher, and is conducive to the implementation of Real Time Imaging Technology.Therefore high field intensity
Open type magnetic resonance system becomes the Hot spots for development and trend of MR-guided interventional treatment.
Summary of the invention
Based on the above, the purpose of the present invention is to provide a kind of magnetic resonance magnet structure and coils, compensating pole ruler
Very little optimization algorithm, with solution, magnetic resonance magnet structure opening degree is small in the prior art, image quality difference etc. in open space
Problem.
In order to achieve the above object, the invention adopts the following technical scheme:
A kind of magnetic resonance magnet structure, comprising:
Two symmetrically arranged superconducting magnets, each superconducting magnet includes cryostat, the cryogenic thermostat
Liquid helium vessel is provided in device, and two intracorporal liquid helium vessels of superconducting magnetic are integral and are provided with from inside to outside
Main coil, compensating pole and the shielded coil being arranged symmetrically, the main coil and the shielded coil are superconducting coil；And
Supporter is set between two superconducting magnets, and the supporter is hollow structure, two superconducting magnetics
Body is connected with the supporter.
Preferably, two superconducting magnet settings symmetrical above and below, the supporter is support post, and two described super
Pass through at least one support post connection between magnetizer.
Preferably, the cryostat periphery is circle, two institutes are set along cryostat circumferential direction direction
Support post is stated, the angle between two support posts is 130-160 °.
Preferably, each cryostat is connected to the support post, connected space is vacuum environment.
Preferably, each liquid helium vessel is connected to the support post.
Preferably, the compensating pole is made of ferrimagnet.
Preferably, the shimming module being arranged symmetrically is provided in two cryostats, shimming module position
Between the main coil.
A kind of coil, the dimensionally-optimised algorithm of compensating pole, comprising the following steps:
S1: the area of feasible solutions of main coil, shielded coil and compensating pole is determined；
S2: the initial number and original dimension of the compensating pole are preset；
S3: grid dividing is carried out to main coil area of feasible solutions, shielded coil area of feasible solutions, each grid is equivalent to an electricity
Flow ring；
S4: establishing the linear relationship of the magnetic field strength of the electric current and imaging region in each grid, calculates superconducting line line
Measure the globally optimal solution most saved；
S5: being calculated by linear programming, if numerical convergence, obtains the initial of the main coil and the shielded coil
Size；
S6: using the compensating pole, the main coil and the respective original dimension of the shielded coil as independent variable, with
Superconducting coil is objective function with the uniformity of magnetic field of line amount or the imaging region, carries out Non-Linear Programming calculating；
S7: if the convergency value that Non-Linear Programming is calculated meets the preset condition of convergence, the compensating pole, institute are obtained
State the optimal size of main coil and the shielded coil.
Preferably, if linear programming calculated result does not restrain, returning to the step S1 in the step S5 and counting again
It calculates.
Preferably, in the step S6, if the convergency value that Non-Linear Programming is calculated is unsatisfactory for preset convergence item
Part returns to the step S1 and recalculates.
The present invention discloses a kind of magnetic resonance magnet structure, and degree of opening is big, and the open space between superconducting magnet
The interior imaging region for generating high evenness, to carry out magnetic resonance fast imaging, thus real time imagery when realizing interventional therapy,
And image quality is high, facilitates doctor according to imaging results and carries out interventional therapy；Invention additionally discloses a kind of coils, compensating pole
Dimensionally-optimised algorithm is calculated by linear programming and Non-Linear Programming, optimize main coil and shielded coil with line amount so that
The magnet structure is more compact, is easily installed, and reduces its manufacturing cost.
Detailed description of the invention
To describe the technical solutions in the embodiments of the present invention more clearly, institute in being described below to the embodiment of the present invention
Attached drawing to be used is needed to be briefly described, it should be apparent that, the accompanying drawings in the following description is only some implementations of the invention
Example, for those of ordinary skill in the art, without creative efforts, can also implement according to the present invention
The content of example and these attached drawings obtain other attached drawings.
Fig. 1 is the structural schematic diagram for the magnetic resonance magnet structure that the specific embodiment of the invention provides；
Fig. 2 is the diagrammatic cross-section for the magnetic resonance magnet structure that the specific embodiment of the invention provides；
Fig. 3 is the flow chart of the coil of specific embodiment of the invention offer, the dimensionally-optimised algorithm of compensating pole；
Fig. 4 is the area of feasible solutions division of coil, the dimensionally-optimised algorithm of compensating pole that the specific embodiment of the invention provides
Schematic diagram；
Fig. 5 is the calculated result signal of coil, the dimensionally-optimised algorithm of compensating pole that the specific embodiment of the invention provides
Figure.
In figure:
1- superconducting magnet；11- cryostat；12- liquid helium vessel；13- main coil；14- compensating pole；15- shielding line
Circle；16- shimming module；2- supporter；3- main coil area of feasible solutions；4- compensating pole area of feasible solutions；5- shielded coil feasible region
Domain；6- imaging region；7- grid cluster.
Specific embodiment
To keep the technical problems solved, the adopted technical scheme and the technical effect achieved by the invention clearer, below
It will the technical scheme of the embodiment of the invention will be described in further detail in conjunction with attached drawing, it is clear that described embodiment is only
It is a part of the embodiment of the present invention, instead of all the embodiments.Based on the embodiments of the present invention, those skilled in the art exist
Every other embodiment obtained under the premise of creative work is not made, shall fall within the protection scope of the present invention.
As Figure 1-Figure 2, present embodiment provides a kind of magnetic resonance magnet structure, which includes two
A symmetrically arranged superconducting magnet 1 and supporter 2.Wherein, each superconducting magnet 1 includes cryostat 11, cryogenic thermostat
Liquid helium vessel 12 is provided in device 11, and the liquid helium vessel 12 in two superconducting magnets 1 is integral and is provided with from inside to outside
Main coil 13, compensating pole 14 and the shielded coil 15 being arranged symmetrically, main coil 13 and shielded coil 15 are superconducting coil；Support
Body 2 is set between two superconducting magnets 1, and is hollow structure, and two superconducting magnets 1 are connected with supporter 2.It may be noted that
, shielded coil 15 is with the current direction in main coil 3 on the contrary, to reduce the external magnetic flux leakage of superconducting magnet 1, to reduce
To the electromagnetic interference of external other detection devices and office equipment, so that entire interventional therapy device layout is more compact, and show
Some open magnet structures often shield magnetic flux leakage using pure iron, and weight is generally at 20 tons or more, and the present embodiment
Superconducting magnet 1 only has 4-5 tons, and in contrast, weight is smaller, and cost is lower.
Compared with prior art, magnetic resonance magnet structure provided by the invention is formed by two superconducting magnets 1 and supporter 2
Open space, degree of opening is big, facilitates doctor to enter the magnet structure from multiple angles and carries out interventional therapy；Secondly, by
The main coil 13, compensating pole 14 and shielded coil 15 being arranged symmetrically, main coil 13 and shielded coil are set in liquid helium vessel 12
15 be superconducting coil, and superconducting state is in the liquid helium environment of extremely low temperature, can be carried compared to room temperature copper conductor bigger
Electric current, so as to generate the magnetic field bigger compared to permanent magnet and room temperature copper conductor, and the open space between superconducting magnet 1
The imaging region 6 of the interior high evenness for generating a certain size, to carry out magnetic resonance fast imaging, thus when realizing interventional therapy
Real time imagery, and image quality is high, facilitates doctor according to imaging results and carries out interventional therapy.It should be pointed out that this at
Picture region 6 is ball domain, and ball domain size is diameter 30-50cm, and magnetic field strength is greater than 1T.
In the present embodiment, the above-mentioned setting symmetrical above and below of two superconducting magnets 1, supporter 2 is support post, and connection is up and down
Two superconducting magnets 1 are connected between two superconducting magnets 1 by least one support post.Preferably, cryostat 11
It is composed of cylinder and rotary table, between two support posts of circumferential direction setting of cryostat 11, two support posts
Angle be 130-160 °.It should be noted that there are certain angles between two support posts, binary channels is formed, in order to
Doctor carries out hospital bed position arrangement or interventional treatment operation from back and forth or left and right both direction.Support post angle is set as 130-
160 °, to balance the stability of 1 structure of superconducting magnet.
Further, superconducting magnet 1 includes the cryostat 11 of two settings symmetrical above and below, each cryostat 11
It is connected to support post, connected space is vacuum environment.It include a liquid helium vessel 12, liquid helium in each cryostat 11
Container 12 is set in vacuum environment, to reduce the external leakage heat to liquid helium vessel 12, realizes zero volatilization of liquid helium.It is symmetrical above and below to set
Two liquid helium vessels 12 set and support post inside are connected to, and an entirety are formed, so as to use single chiller to liquid
Helium vessel 12 provides refrigerating capacity, saves 1 manufacturing cost of superconducting magnet, reduces and uses electrical power consumed when using.
Further, it is provided with the shimming module 16 being arranged symmetrically in cryostat 11, in the present embodiment, arranges up and down
A pair of symmetrical shimming module 16, and shimming module 16 is between upper and lower two main coils 13.Shimming module 16 is into one
Step improves the uniformity of magnetic field of imaging region 6, improves image quality, in favor of the implementation of fast scan imaging sequence, meets and is situated between
Enter the real time imagery requirement for the treatment of.Shimming module 16 is located in the groove outside cryostat 11, and gives the peace of plate gradient
Dress stops space, without departing from the groove plane of cryostat 11, will not influence the degree of opening of superconducting magnet 1, so as to
Enough intervention spaces are provided to doctor, improve the convenience of doctor's interventional treatment operation.
The above-mentioned optional pure iron of compensating pole 14, the ferrimagnets such as silicon steel sheet are made, to increase the magnetic of imaging region 6
Field intensity reduces superconducting coil line amount, reduces the manufacturing cost of superconducting magnet 1.Compensating pole 14 is located in liquid helium vessel 12
Liquid helium environment in, thereby may be ensured that the magnetic conductivity of compensating pole 14 is not influenced by ambient temperature variation, enhance
The stability of magnetic resonance imaging guarantees doctor in the surgical quality of interventional therapy.
As shown in Figure 3-Figure 5, present embodiment also provides a kind of coil, the dimensionally-optimised algorithm of compensating pole, specifically includes
Following steps:
1) according to symmetry, coil domain can be set on a quarter model, and according to the boundary of superconducting magnet 1
Region determines the area of feasible solutions of main coil 13, shielded coil 15 and compensating pole 14.
2) initial number and original dimension of predesigned compensation magnetic pole 14 optionally compensate in compensating pole area of feasible solutions 4
14 numbers of magnetic pole are 3-5, in order to fabricate.
3) grid dividing is carried out to main coil area of feasible solutions 3, shielded coil area of feasible solutions 5, is classified as M × N number of grid,
Each grid can be equivalent to an electric current loop.
4) compensating pole 14 is calculated to the field contribution of imaging region 6 by finite element algorithm, and establishes each net
The linear relationship of the magnetic field strength of electric current and imaging region 6 in lattice carries out linear programming to Optimized model, obtains superconducting line use
The globally optimal solution that line amount most saves.
5) it is calculated by linear programming, if numerical convergence, 13 area of feasible solutions of main coil and shielded coil 15 can be obtained
Mesh current distribution map in area of feasible solutions, coil current are split into multiple grid clusters 7, and each grid cluster 7 can be equivalent to one
Superconducting coil, and then determine according to the size of grid cluster 7 original dimension of main coil 13 and shielded coil 15；If calculated result is not
Convergence, returns to step 1) and recalculates.
6) using compensating pole 14, main coil 13 and the respective original dimension of shielded coil 15 as independent variable, with superconducting line
Circle is objective function with the uniformity of magnetic field of line amount or imaging region 6, carries out Non-Linear Programming calculating.
If 7) convergency value that Non-Linear Programming is calculated meets the preset condition of convergence, compensating pole 14, main line are obtained
The optimal size of circle 13 and shielded coil 15；If the convergency value that Non-Linear Programming is calculated is unsatisfactory for the preset condition of convergence,
Step 1) is returned to recalculate.
It should be noted that linear programming can use many algorithms, such as interior plot point hair, simplex method.Non-linear rule
Many algorithms, such as genetic algorithm, sequential quadratic programming algorithm, simulated annealing can be used by drawing.
The present invention is by the magnetic resonance magnet structure provided, and degree of opening is big, and the open space between superconducting magnet 1
It is interior generate high evenness imaging region 6, to carry out magnetic resonance fast imaging, thus when realizing interventional therapy it is real-time at
Picture, and image quality is high, facilitates doctor according to imaging results and carries out interventional therapy.
Coil, compensating pole dimensionally-optimised algorithm of the present invention by offer, optimization main coil 13 and shielded coil 14
It is easily installed with line amount so that the magnet structure is more compact, reduces its manufacturing cost.
Note that the above is only a better embodiment of the present invention and the applied technical principle.It will be appreciated by those skilled in the art that
The invention is not limited to the specific embodiments described herein, be able to carry out for a person skilled in the art it is various it is apparent variation,
It readjusts and substitutes without departing from protection scope of the present invention.Therefore, although being carried out by above embodiments to the present invention
It is described in further detail, but the present invention is not limited to the above embodiments only, without departing from the inventive concept, also
It may include more other equivalent embodiments, and the scope of the invention is determined by the scope of the appended claims.
Claims (10)
1. a kind of magnetic resonance magnet structure characterized by comprising
Two symmetrically arranged superconducting magnets (1), each superconducting magnet (1) includes cryostat (11), described low
It is provided with liquid helium vessel (12) in warm thermostat (11), and the liquid helium vessel (12) in two superconducting magnets (1) is made
It is integral the main coil (13), compensating pole (14) and shielded coil (15) for being provided be arranged symmetrically from inside to outside, the master
Coil (13) and the shielded coil (15) are superconducting coil；And
Supporter (2) is set between two superconducting magnets (1), and the supporter (2) is hollow structure, described in two
Superconducting magnet (1) is connected with the supporter (2).
2. magnetic resonance magnet structure according to claim 1, which is characterized in that two superconducting magnets (1) are right up and down
Claim setting, the supporter (2) is support post, and it is vertical to pass through at least one described support between two superconducting magnets (1)
Column connection.
3. magnetic resonance magnet structure according to claim 2, which is characterized in that cryostat (11) periphery is circle
Two support posts are arranged along the circumferential direction of the cryostat (11), the folder between two support posts in shape
Angle is 130-160 °.
4. magnetic resonance magnet structure according to claim 2 or 3, which is characterized in that each cryostat (11)
It is connected to the support post, connected space is vacuum environment.
5. magnetic resonance magnet structure according to claim 4, which is characterized in that each liquid helium vessel (12) is and institute
State support post connection.
6. magnetic resonance magnet structure according to claim 1, which is characterized in that the compensating pole (14) is by ferromagnetism material
Material is made.
7. magnetic resonance magnet structure according to claim 1, which is characterized in that set in two cryostats (11)
It is equipped with the shimming module (16) being arranged symmetrically, the shimming module (16) is between the main coil (13).
8. the dimensionally-optimised algorithm of a kind of coil, compensating pole, which comprises the following steps:
S1: the area of feasible solutions of main coil (13), shielded coil (15) and compensating pole (14) is determined；
S2: the initial number and original dimension of the compensating pole (14) are preset；
S3: grid dividing is carried out to main coil area of feasible solutions (3), shielded coil area of feasible solutions (5), each grid is equivalent to one
Electric current loop；
S4: establishing the linear relationship of the electric current in each grid and the magnetic field strength of imaging region (6), calculates superconducting line line amount
The globally optimal solution most saved；
S5: being calculated by linear programming, if numerical convergence, obtains the main coil (13) and the shielded coil (15)
Original dimension；
S6: using the compensating pole (14), the main coil (13) and the shielded coil (15) respective original dimension as
Independent variable carries out Non-Linear Programming using the uniformity of magnetic field of superconducting coil line amount or the imaging region (6) as objective function
It calculates；
S7: if the convergency value that Non-Linear Programming is calculated meets the preset condition of convergence, the compensating pole (14), institute are obtained
State the optimal size of main coil (13) and the shielded coil (15).
9. the dimensionally-optimised algorithm of coil according to claim 8, compensating pole, which is characterized in that in the step S5, if
Linear programming calculated result does not restrain, and returns to the step S1 and recalculates.
10. the dimensionally-optimised algorithm of coil according to claim 8, compensating pole, which is characterized in that in the step S6,
If the convergency value that Non-Linear Programming is calculated is unsatisfactory for the preset condition of convergence, returns to the step S1 and recalculate.
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112307657A (en) * | 2020-09-22 | 2021-02-02 | 山东大学 | Superconducting magnetic resonance magnet for neonatal imaging and design method |
| CN114724796A (en) * | 2022-06-09 | 2022-07-08 | 山东奥新医疗科技有限公司 | Magnetic resonance superconducting magnet with novel structure |
| CN114818392A (en) * | 2022-06-28 | 2022-07-29 | 山东奥新医疗科技有限公司 | Shielding coil design method and related assembly |
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| CN112307657A (en) * | 2020-09-22 | 2021-02-02 | 山东大学 | Superconducting magnetic resonance magnet for neonatal imaging and design method |
| CN112307657B (en) * | 2020-09-22 | 2023-03-17 | 山东大学 | Superconducting magnetic resonance magnet for neonatal imaging and design method |
| CN114724796A (en) * | 2022-06-09 | 2022-07-08 | 山东奥新医疗科技有限公司 | Magnetic resonance superconducting magnet with novel structure |
| CN114818392A (en) * | 2022-06-28 | 2022-07-29 | 山东奥新医疗科技有限公司 | Shielding coil design method and related assembly |
| CN114818392B (en) * | 2022-06-28 | 2022-09-06 | 山东奥新医疗科技有限公司 | Shielding coil design method and related assembly |
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