CN103065757B - Breast imaging magnetic resonance imaging superconducting magnet system - Google Patents
Breast imaging magnetic resonance imaging superconducting magnet system Download PDFInfo
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- CN103065757B CN103065757B CN201310030232.7A CN201310030232A CN103065757B CN 103065757 B CN103065757 B CN 103065757B CN 201310030232 A CN201310030232 A CN 201310030232A CN 103065757 B CN103065757 B CN 103065757B
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Abstract
The invention provides a breast imaging magnetic resonance imaging superconducting magnet system. The superconducting magnet system comprises an upper cryogenic vessel (1), a lower cryogenic vessel (2), an upper superconducting main coil, an upper superconducting shield coil (4), a lower superconductive main coil, a lower under the superconducting shield coil (6) and a pulse tube refrigerator (17). The upper superconducting main coil and the upper superconducting shield coil (4) are mounted in the upper cryogenic vessel (1), the upper cryogenic vessel (1) is provided with a vertical room temperature bore with a diameter of 40 cm. The lower superconductive main coil and the lower under the superconducting shield coil (6) are mounted in the lower cryogenic vessels (2), and a horizontal space with a gap distance of 45 cm is reserved between the upper and the lower superconducting main coil. In the spherical imaging area which is 8 cm upwardly offset the superconducting magnet central and of the diameter 20 cm, the superconducting magnets generate s spatial magnetic field distribution with magnetic field intensity of 1.0T, peak magnetic field uniformity of 15 ppm, and further, 5-Gauss stray field is respectively limited in ellipsoidal ranges with diameters of 3.5 m vertically and 4.0 m horizontally.
Description
Technical field
The present invention relates to a kind of open formula magnetic resonance image-forming superconducting magnet system.
Background technology
Whole body nuclear magnetic resonance imaging (Magnetic Resonance Imaging, MRI) generally needing at diameter is produce magnetic field peak-to-peak value unevenness in 40 ~ 50cm ball territory to be better than 20ppm(parts per million, ppm) magnetic field of high uniformity distribution.Magnetic resonance image-forming superconducting magnet is by solenoid type coil composition, and the diameter that conventional magnetic resonance image-forming superconducting magnet provides to meet entire patient's imaging demand is greater than the hollow cylinder room temperature hole of 70cm.Patient, when carrying out magnetic resonance imaging, need enter central magnetic field homogeneous area from the one end in long and narrow room temperature hole and carry out image-forming diagnose.A large amount of clinical trial shows that patient is when carrying out magnetic resonance image-forming diagnose, generally go out the claustrophobia such as anxiety, uneasiness phenomenon, how to improve the opening of superconducting magnet system, become the focus that each large-scale commerce company competes in technical field, simultaneously, exploitation possesses the Electromagnetic Optimum Design algorithm of the magnetic resonance image-forming superconducting magnet system designing open demand, has become the focus of Electromagnetic Design expert research.
Open MRI superconducting magnet system is mainly plane type structure, in the upper and lower low-temperature (low temperature) vessel being arranged on two planes symmetrically of superconducting coil, there is provided a spacing to be about the horizontal clearance of 45cm between two low-temperature (low temperature) vessels, patient enters magnet center position by this horizontal clearance and carries out image-forming diagnose.But, because local organs position in human body is different, a magnetic resonance imaging system is difficult to the demand meeting all human body imaging organs, therefore, occur that some magnetic resonance imaging systems customized are to meet the demand of local organs imaging, as head imaging system and joint imaging system etc.Nearest research shows, the demand of female breast magnetic resonance imaging presents the trend year after year increased, and develops the active demand that a set of magnetic resonance image-forming superconducting magnet system for breast imaging meets market and patient.
US Patent No. 005994991A is a kind of open type magnetic resonance imaging (MRI) system that AM General company proposes, this system is installed in the hollow low-temperature (low temperature) vessel of upper and lower symmetry for generation of the superconducting coil in magnetic field, superconducting coil produces magnetic field intensity and is about 0.5T in central area, but due to the shortcomings such as spherical imaging region is less, the uniformity is poor and stray magnetic field scope is larger that make this system have of the loop construction feature described in this patent.US Patent No. 005982260A is a kind of open MRI superconducting magnet system that Oxford magnet technology company proposes, superconduction main coil and superconducting shielding coil are installed in the low-temperature (low temperature) vessel of upper and lower two planes, gap between two low-temperature (low temperature) vessels provides the open space meeting whole body imaging demand, though this system has met the demand of most of entire patient's imaging, but for the more fat female patient of part when carrying out breast imaging diagnosis, there is mammary organ and exceeding risk outside field homogeneity district scope that system provides.
Summary of the invention
The object of the invention is overcome existing magnetic resonance image-forming superconducting magnet systemic openness deficiency and carry out the shortcomings such as insertion type operative treatment difficulty, propose a kind of magnetic resonance image-forming superconducting magnet system for breast imaging.
Superconducting magnet system of the present invention is made up of upper low-temperature (low temperature) vessel, lower low-temperature (low temperature) vessel, upper superconduction main coil, upper superconducting shielding coil, lower superconduction main coil, lower superconducting shielding coil and vascular refrigerator.Upper superconduction main coil, upper superconducting shielding coil, lower superconduction main coil and lower superconducting shielding coil are axisymmetric coaxial solenoid coil coil, upper superconduction main coil and upper superconducting shielding coil are arranged in low-temperature (low temperature) vessel, and lower superconduction main coil and lower superconducting shielding coil are arranged in lower low-temperature (low temperature) vessel.Upper low-temperature (low temperature) vessel is hollow flat-surface type structure, and provide diameter to be the vertical room temperature hole of 40cm, lower low-temperature (low temperature) vessel is planarized structure, provides spacing to be the horizontal clearance of 45cm between upper and lower low-temperature (low temperature) vessel.Upper low-temperature (low temperature) vessel and lower low-temperature (low temperature) vessel are connected by the hollow column at 180 degree, two intervals, and hollow column is communicated with the liquid helium tank in two low-temperature (low temperature) vessels, and supports the interaction force between two low-temperature (low temperature) vessels.Vascular refrigerator is arranged on the upper surface place of low-temperature (low temperature) vessel, and its one-level cold head connects the upper cold screen of upper low-temperature (low temperature) vessel, and secondary cold head is placed in the upper liquid helium tank of low-temperature (low temperature) vessel, can realize zero volatilization of liquid helium in low-temperature (low temperature) vessel and lower low-temperature (low temperature) vessel.
It is the spheric region of 20cm that the uniform magnetic field that superconducting magnet system of the present invention produces is distributed in a diameter, the center of spherical imaging region upper superconduction main coil, on superconducting shielding coil, lower superconduction main coil and lower superconducting shielding coil the axis of symmetry on and 8cm is upwards departed from distance superconducting magnet system center, superconducting magnet system produces at spherical imaging region the magnetic field of high uniformity distribution that magnetic field intensity is 1.0T, magnetic field peak-to-peak value unevenness is 15ppm, and 5 Gauss's stray magnetic fields constrain within the scope of the ellipsoid of 3.5m and 4.0m respectively at vertical direction and horizontal direction.
The vertical room temperature hole that the present invention proposes provides enough open spaces to carrying out insertion type operative treatment, female patient lies low and enters superconducting magnet central area from horizontal clearance on one's sick bed, and make the mammary organ of patient be placed in spherical imaging region by upper and lower to the position adjusting sick bed, carry out magnetic resonance image-forming diagnose, manipulator is stretched into spherical imaging region from vertical room temperature hole, insertion type operative treatment is carried out in the position accurately being controlled manipulator by computer simultaneously.
Accompanying drawing explanation
Fig. 1 embodiment of the present invention is used for the loop construction schematic diagram of the magnetic resonance image-forming superconducting magnet system of breast imaging;
Fig. 2 embodiment of the present invention is used for the schematic appearance of the magnetic resonance image-forming superconducting magnet system of breast imaging;
The uniformity of magnetic field contour distribution map that the magnetic resonance image-forming superconducting magnet system that Fig. 3 embodiment of the present invention is used for breast imaging produces in space;
The stray magnetic field contour distribution map that Fig. 4 embodiment of the present invention produces for the magnetic resonance image-forming superconducting magnet system of breast imaging.
Embodiment
The present invention is further illustrated below in conjunction with the drawings and the specific embodiments.
Fig. 1 is the loop construction schematic diagram of the magnetic resonance image-forming superconducting magnet system for breast imaging of the embodiment of the present invention.As shown in Figure 1, superconducting magnet system of the present invention is made up of upper low-temperature (low temperature) vessel 1, lower low-temperature (low temperature) vessel 2, upper superconduction main coil, upper superconducting shielding coil 4, lower superconduction main coil, lower superconducting shielding coil 6 and vascular refrigerator 17.Upper low-temperature (low temperature) vessel 1 is made up of upper liquid helium tank 7, upper cold screen 8 and upper vacuum tank 9, and lower low-temperature (low temperature) vessel 2 is made up of lower liquid helium tank 10, lower cold screen 11 and lower vacuum tank 12.Upper low-temperature (low temperature) vessel 1 is hollow flat-surface type, the inside radius of upper liquid helium tank 7, outer radius and axial height are respectively 22cm, 60cm and 35cm, upper cold screen 8 is arranged on the outside of liquid helium tank 7, upper gap between cold screen 8 and upper liquid helium tank 7 is 2mm, upper vacuum tank 9 is arranged on the outside of cold screen 8, gap between upper vacuum tank 9 and upper cold screen 8 is 2mm, and upper low-temperature (low temperature) vessel 1 can provide diameter to be the vertical room temperature hole 15 of 40cm.Radius and the axial height of lower liquid helium tank are respectively 60cm and 35cm, lower cold screen 11 is arranged on the outside of lower liquid helium tank 10, lower gap between cold screen 11 and lower liquid helium tank 10 is 2mm, lower vacuum tank 12 is arranged on the outside of lower cold screen 11, and the gap between lower vacuum tank 12 and lower cold screen 11 is 2mm.Connected by two hollow columns of 180 degree of being separated by between upper low-temperature (low temperature) vessel 1 and lower low-temperature (low temperature) vessel 2.Upper superconduction main coil is made up of superconduction main coil 3.5 on superconduction main coil 3.4 and the 5th on superconduction main coil 3.3, the 4th on superconduction main coil 3.2, the 3rd on superconduction main coil 3.1, second on first, and lower superconduction main coil is made up of first time superconduction main coil, 5.1, second time superconduction main coil 5.2, the 3rd time superconduction main coil 5.3 and the 4th time superconduction main coil 5.4.Upper superconduction main coil, upper superconducting shielding coil 4, lower superconduction main coil and lower superconducting shielding coil 6 are the axial symmetry solenoid coil of axle centered by symmetry axis 13.Upper superconduction main coil and upper superconducting shielding coil 4 are arranged in the upper liquid helium tank 7 of low-temperature (low temperature) vessel 1, and lower superconduction main coil and lower superconducting shielding coil 6 are arranged in the lower liquid helium tank 10 of lower low-temperature (low temperature) vessel 2.The sense of current that on first, superconduction main coil 3.1 loads is forward, the sense of current that on second, superconduction main coil 3.2 loads is reverse, the sense of current that on 3rd, superconduction main coil 3.3 loads is forward, the sense of current that on 4th, superconduction main coil 3.4 loads is oppositely, and the sense of current that on the 5th, superconduction main coil 3.5 loads is forward.On first superconduction main coil 3.1 be arranged on radial position in liquid helium tank 7 near inwall place, vertical room temperature hole 15 and axial location in the axial middle position of liquid helium tank 7, on second on superconduction main coil 3.2, the 3rd on superconduction main coil 3.3, the 4th on superconduction main coil 3.4 and the 5th superconduction main coil 3.5 to be installed in liquid helium tank 7 near the position, bottom at superconducting magnet center 20 and to arrange successively apart from the direction increased along with symmetry axis 13.Upper superconducting shielding coil 4 is a solenoid coil passing to reverse current, is arranged on highest distance position place, liquid helium tank 7 middle distance superconducting magnet center 20.The sense of current of first time superconduction main coil 5.1 loading is reverse, the sense of current of second time superconduction main coil 5.2 loading is forward, the sense of current of the 3rd time superconduction main coil 5.3 loading is oppositely, and the sense of current of the 4th time superconduction main coil 5.4 loading is forward.First time superconduction main coil, 5.1, second time superconduction main coil 5.2, the 3rd time superconduction main coil 5.3 and the 4th time superconduction main coil 5.4 to be installed in lower liquid helium tank 10 near the position, upper end at superconducting magnet center 20 and to arrange successively apart from the direction increased along with symmetry axis 13.Lower superconducting shielding coil 6 is a solenoid coil passing to reverse current, is arranged on highest distance position place, lower liquid helium tank 10 middle distance superconducting magnet center.The uniform magnetic field that superconducting magnet system produces is distributed in the spherical imaging region 14 that a diameter is 20cm, and the center of spherical imaging region 14 is on the axis of symmetry 13, and 8cm place is upwards departed from distance superconducting magnet system center 20.Spacing is provided to be the horizontal clearance 16 of 45cm between upper low-temperature (low temperature) vessel 1 and lower low-temperature (low temperature) vessel 2.Vascular refrigerator 17 is arranged on the upper surface place of low-temperature (low temperature) vessel 1, and its one-level cold head connects the upper cold screen 8 of upper low-temperature (low temperature) vessel 1, and secondary cold head is placed in the upper liquid helium tank 7 of low-temperature (low temperature) vessel 1, can realize zero volatilization of liquid helium in low-temperature (low temperature) vessel 1 and lower low-temperature (low temperature) vessel 2.
Fig. 2 is the schematic appearance of the magnetic resonance image-forming superconducting magnet system for breast imaging of the embodiment of the present invention.As shown in Figure 2, connected between upper low-temperature (low temperature) vessel 1 and lower low-temperature (low temperature) vessel 2 by two connecting struts, connecting struts can provide liquid helium loop between low-temperature (low temperature) vessel 1 and lower low-temperature (low temperature) vessel 2 and supporting role.
Fig. 3 is the uniformity of magnetic field contour distribution map produced in space for the magnetic resonance image-forming superconducting magnet system of breast imaging of the embodiment of the present invention.As shown in Figure 3, superconducting magnet system produces at the spherical imaging region 14 that diameter is 20cm the high uniform magnetic field distribution that magnetic field peak-to-peak value unevenness is 15ppm.
Fig. 4 is the stray magnetic field contour distribution map that the magnetic resonance image-forming superconducting magnet system for breast imaging of the embodiment of the present invention produces.As shown in Figure 4,5 Gauss's stray magnetic fields constrain within the scope of the ellipsoid of 3.5m and 4.0m respectively at vertical direction and horizontal direction.
Claims (3)
1., for a magnetic resonance image-forming superconducting magnet system for breast imaging, it is characterized in that described superconducting magnet system is made up of upper low-temperature (low temperature) vessel (1), lower low-temperature (low temperature) vessel (2), upper superconduction main coil, upper superconducting shielding coil (4), lower superconduction main coil, lower superconducting shielding coil (6) and vascular refrigerator (17); Upper superconduction main coil and upper superconducting shielding coil (4) are arranged in low-temperature (low temperature) vessel (1), lower superconduction main coil and lower superconducting shielding coil (6) are arranged in lower low-temperature (low temperature) vessel (2), and vascular refrigerator (17) is arranged on the upper surface place of low-temperature (low temperature) vessel (1);
Described upper low-temperature (low temperature) vessel (1) is made up of upper liquid helium tank (7), upper cold screen (8) and upper vacuum tank (9), and lower low-temperature (low temperature) vessel (2) is made up of lower liquid helium tank (10), lower cold screen (11) and lower vacuum tank (12); Upper superconduction main coil and upper superconducting shielding coil (4) are arranged in the upper liquid helium tank (7) of low-temperature (low temperature) vessel (1), and lower superconduction main coil and lower superconducting shielding coil (6) are arranged in the lower liquid helium tank (10) of lower low-temperature (low temperature) vessel (2); Upper low-temperature (low temperature) vessel (1) is hollow flat-surface type container; Upper cold screen (8) is arranged on the outside of liquid helium tank (7); Upper vacuum tank (9) is arranged on the outside of cold screen (8); Lower cold screen (11) is arranged on the outside of lower liquid helium tank (10); Lower vacuum tank (12) is arranged on the outside of lower cold screen (11); Upper low-temperature (low temperature) vessel (1) is hollow flat-surface type structure, and lower low-temperature (low temperature) vessel (2) is planarized structure, and upper low-temperature (low temperature) vessel (1) and lower low-temperature (low temperature) vessel (2) are connected by the hollow column at 180 degree, two intervals; The one-level cold head of vascular refrigerator (17) connects the upper cold screen (8) of upper low-temperature (low temperature) vessel (1), and the secondary cold head of vascular refrigerator (17) is placed in the upper liquid helium tank (7) of low-temperature (low temperature) vessel (1);
Described upper superconduction main coil, upper superconducting shielding coil (4), lower superconduction main coil and lower superconducting shielding coil (6) are the axial symmetry solenoid coil of axle centered by symmetry axis (13); The sense of current that on first, on superconduction main coil (3.1), the 3rd, on superconduction main coil (3.3) and the 5th, superconduction main coil (3.5) loads is forward, and the sense of current that on second, on superconduction main coil (3.2) and the 4th, superconduction main coil (3.4) loads is reverse; On described first superconduction main coil (3.1) be arranged on radial position in liquid helium tank (7) near the inwall place of vertical room temperature hole (15) and axial location in the axial middle position of liquid helium tank (7); On second on superconduction main coil (3.2), the 3rd on superconduction main coil (3.3), the 4th on superconduction main coil (3.4) and the 5th superconduction main coil (3.5) to be installed in liquid helium tank (7) near the position, bottom at superconducting magnet system center (20) and to arrange successively along with the direction that increases of symmetry axis (13) distance; Upper superconducting shielding coil (4) is a solenoid coil passing to reverse current, is arranged on the highest distance position place of liquid helium tank (7) middle distance superconducting magnet system center (20); The sense of current that first time superconduction main coil (5.1) and the 3rd time superconduction main coil (5.3) load is reverse, and second time superconduction main coil (5.2) and the sense of current that the 4th time superconduction main coil (5.4) loads are forward; First time superconduction main coil (5.1), second time superconduction main coil (5.2), the 3rd time superconduction main coil (5.3) and the 4th time superconduction main coil (5.4) to be installed in lower liquid helium tank (10) near the position, upper end of superconducting magnet system center (20) and to arrange successively along the direction increased with symmetry axis (13) distance; Lower superconducting shielding coil (6) is a solenoid coil passing to reverse current, is arranged on lower liquid helium tank (10) middle distance superconducting magnet system center (20) highest distance position place;
Produce the magnetic field of high uniformity distribution that magnetic field intensity is 1.0T, magnetic field peak-to-peak value unevenness is 15ppm in the spherical imaging region (14) that superconducting magnet system upwards departs from 8cm position in distance superconducting magnet system center (20), diameter is 20cm, 5 Gauss's stray magnetic fields constrain within the scope of the ellipsoid of 3.5m and 4.0m respectively at vertical direction and horizontal direction; Superconducting magnet system provides vertical room temperature hole (15) and horizontal clearance (16).
2., according to the magnetic resonance image-forming superconducting magnet system for breast imaging according to claim 1, it is characterized in that the gap between described upper cold screen (8) and upper liquid helium tank (7) is 2mm; Gap between upper vacuum tank (9) and upper cold screen (8) is 2mm; Lower gap between cold screen (11) and lower liquid helium tank (10) is 2mm; Gap between lower vacuum tank (12) and lower cold screen (11) is 2mm; Spacing is provided to be the horizontal clearance (16) of 45cm between upper low-temperature (low temperature) vessel (1) and lower low-temperature (low temperature) vessel (2).
3. according to the magnetic resonance image-forming superconducting magnet system for breast imaging according to claim 1, it is characterized in that described spherical imaging region (14) to be a diameter be the spheric region of 20cm, superconducting magnet system center (20) 8cm on symmetry axis (13), and is upwards departed from the center of spherical imaging region (14).
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|---|---|---|---|---|
| CN101017722A (en) * | 2006-01-05 | 2007-08-15 | 株式会社日立制作所 | Superconducting magnet apparatus and nuclear magnetic resonance imaging apparatus |
| CN101030471A (en) * | 2006-01-23 | 2007-09-05 | 株式会社日立制作所 | Electromagnet apparatus |
| CN101202142A (en) * | 2006-11-17 | 2008-06-18 | 株式会社日立制作所 | Superconductive magnet device and magnetic resonance imaging apparatus |
| CN101884533A (en) * | 2009-05-15 | 2010-11-17 | 美时医疗技术(上海)有限公司 | Superconducting magnetic resonance imaging machine used for breast disease diagnosis, and construction method and use thereof |
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| JP4934067B2 (en) * | 2008-01-24 | 2012-05-16 | 株式会社日立製作所 | Superconducting magnet apparatus and magnetic resonance imaging apparatus |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101017722A (en) * | 2006-01-05 | 2007-08-15 | 株式会社日立制作所 | Superconducting magnet apparatus and nuclear magnetic resonance imaging apparatus |
| CN101030471A (en) * | 2006-01-23 | 2007-09-05 | 株式会社日立制作所 | Electromagnet apparatus |
| CN101202142A (en) * | 2006-11-17 | 2008-06-18 | 株式会社日立制作所 | Superconductive magnet device and magnetic resonance imaging apparatus |
| CN101884533A (en) * | 2009-05-15 | 2010-11-17 | 美时医疗技术(上海)有限公司 | Superconducting magnetic resonance imaging machine used for breast disease diagnosis, and construction method and use thereof |
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