CN103091652B - For the mammary gland magnetic resonance RF receiving coil of magnetic resonance imaging system - Google Patents
For the mammary gland magnetic resonance RF receiving coil of magnetic resonance imaging system Download PDFInfo
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- CN103091652B CN103091652B CN201310042180.5A CN201310042180A CN103091652B CN 103091652 B CN103091652 B CN 103091652B CN 201310042180 A CN201310042180 A CN 201310042180A CN 103091652 B CN103091652 B CN 103091652B
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Abstract
The invention discloses a kind of mammary gland magnetic resonance RF receiving coil for magnetic resonance imaging system, comprise cage assembly and the antenna circuit being located at cage assembly inside, cage assembly comprises bottom deck assembly and the baffle plate assembly for pressing close to human body, baffle plate assembly is provided with two for inserting the through hole of mammary gland, multiple joint pin is provided with between bottom deck assembly and baffle plate assembly, bottom deck assembly, joint pin, two are formed respectively for holding the imaging space of the Open architecture of patient's mammary gland between through hole, antenna circuit comprises multiple coil receiving elements of the formation hyperchannel phased array structures be paperwrapped in respectively outside imaging space.The present invention can meet the mammary gland biopsy of guided by magnetic resonance, contribute to promoting in mammary gland magnetic resonance scanning to the scanning coverage of axillary lymph and wall of the chest tissue and picture quality, have that signal to noise ratio (S/N ratio) is high, wide coverage, image quality are high, easy to use, the simple advantage of structure.
Description
Technical field
The present invention relates to magnetic resonance imaging system field, be specifically related to a kind of mammary gland magnetic resonance RF receiving coil for magnetic resonance imaging system.
Background technology
Magnetic resonance imaging (MRI) is the another major progress of medical imaging diagnosis technology after CT.The ultimate principle of magnetic resonance imaging comes from the discovery of nineteen forty-six American scholar Bloch and Purcell, under the effect of outside magnetic field, some proton around the spin of main field (external magnetic field) precession (comprising the Hydrogen Proton in human body) is under of short duration rf wave effect, and angle of precession increases; After rf wave stops, those protons can return to original state again gradually, and the radiofrequency signal that release is identical with field wave frequency simultaneously, this physical phenomenon is called as nuclear magnetic resonance.Mr imaging technique utilizes this principle, by a Pulsed filed gradient additional in main field, optionally excite the atomic nucleus in the human body of required position, then the NMR signal that atomic nucleus produces is received, finally carry out Fourier transform in a computer, frequency coding and phase encoding are carried out to these signals, thus sets up a complete magnetic resonance image (MRI).
MR imaging apparatus comprises radio-frequency sending coil and received RF coil, radio-frequency sending coil is for generation of Pulsed filed gradient, the NMR signal that received RF coil produces for receiving atomic nucleus, received RF coil can be transmitting coil itself also can be the absolute coil receiving only radiofrequency signal.In magnetic resonance imaging system, Signal-to-Noise (SNR) height that the good and receiving coil of the magnetic field homogeneity that radio-frequency sending coil produces receives is the key factor obtaining high quality graphic.The method improving signal to noise ratio (S/N ratio) has two kinds, one is quadrature receiving, and another kind is phased-array coil technology, and the latter uses multiple independently small coil to cover this region together, because the noise of the very zonule only closing on coil just can enter coil, therefore, it is possible to effectively improve signal to noise ratio (S/N ratio).But when radio-frequency sending coil and received RF coil are same coil, use phased-array coil can there is a problem, namely be difficult to the magnetic field's regularity ensureing that coil produces, this problem is especially embodied in the magnetic resonance imager for detecting partes corporis humani position.Because the shape of each physiological site of human body is different, very irregular again, and size also difference is very large, so how according to the physiological structure feature at each position of human body, arrange coil circuit dexterously, thus the comparatively uniform Distribution of Magnetic Field of acquisition and larger detection sensitivity are the maximum tasks of coil design personnel in the world always.In order to realize above-mentioned coil design target, the design of coil case and internal mechanical structure also becomes the key factor ensureing high-quality scan image and meet physiological structure coverage, and well-designed physical construction coordinates the antenna circuit being assemblied in its inner space jointly to achieve most important link in a coil design.
Along with the development of magnetic resonance detection technique, the importance of the disorder in screening such as breast cancer more and more comes into one's own, be specifically designed to the design major requirement high s/n ratio of the magnetic resonance radio frequency receiving coil of galactophore scanning, larger coverage, and the open design etc. that the biopsy that may be used for guided by magnetic resonance samples.At present for galactophore scanning magnetic resonance radio frequency receiving coil due to structure simple and crude, there is the defect that signal to noise ratio (S/N ratio) is low, coverage is little, image quality is poor, constrain the application of magnetic resonance detection technique in the fields such as disorder in screening such as breast cancer.
Summary of the invention
The technical problem to be solved in the present invention is to provide that a kind of signal to noise ratio (S/N ratio) of detection signal is high, wide coverage, image quality are high, easy to use, structure is simply for the mammary gland magnetic resonance RF receiving coil of magnetic resonance imaging system.
For solving the problems of the technologies described above, the technical solution used in the present invention is:
A kind of mammary gland magnetic resonance RF receiving coil for magnetic resonance imaging system, comprise cage assembly and the antenna circuit being located at cage assembly inside, described cage assembly comprises bottom deck assembly and the baffle plate assembly for pressing close to human body, described baffle plate assembly is provided with two for inserting the through hole of mammary gland, the supporting cell guide of multiple hollow-core construction is provided with between described bottom deck assembly and baffle plate assembly, described bottom deck assembly, two are formed respectively for holding the imaging space of the Open architecture of patient's mammary gland between supporting cell guide and two through holes, described antenna circuit comprises multiple coil receiving elements of the formation hyperchannel phased array structures be paperwrapped in respectively outside described imaging space.
Further improvement as technique scheme:
Described bottom deck assembly comprises the base plate upper casing and base plate lower casing that cooperatively interact, forms the space for installing coil receiving element between described base plate upper casing and base plate lower casing; Described baffle plate assembly comprises the baffle plate upper casing and baffle plate lower casing that cooperatively interact, forms the space for installing coil receiving element between described baffle plate upper casing and baffle plate lower casing; One end of described base plate upper casing is connected with one end of baffle plate lower casing and its connecting portion is provided with connecting hole for installing coil receiving element, and the other end of described base plate upper casing is connected by supporting cell guide one end with baffle plate lower casing.
The side of described base plate upper casing is provided with the first Connection Block, and the opposite side of described base plate upper casing is provided with three first and connects column base, and described three first connection column bases are arranged on same straight line; The side of described baffle plate lower casing is provided with the second Connection Block, and the opposite side of described baffle plate lower casing is provided with and connects corresponding three second of column base respectively with described three first and connect column base; Described first Connection Block is connected with the second Connection Block, and described three first connection column bases are connected column base respectively by a supporting cell guide with second and are connected.
Described supporting cell guide is made up of the guide pillar lid that two panels is positioned opposite, and one end of described two panels guide pillar lid is inserted in the first connection column base jointly, and the other end of described two panels guide pillar lid is inserted in the second connection column base jointly.
Described antenna circuit comprises 8 coil receiving elements.
On described bottom deck assembly, the location arrangements of relatively described two through holes has 3 coil receiving elements of arranged superposed; Described baffle plate assembly is provided with 2 the coil receiving elements holding described through hole respectively; 3 the coil receiving elements arranged along bottom deck assembly vertical direction are provided with between described bottom deck assembly and baffle plate assembly, wherein 1 coil receiving element is arranged in the position between two through holes, all the other 2 coil receiving element size shape are completely the same, be arranged in the outside of two through holes respectively along the axial connecting line of two through holes, and the coil receiving element that Relative vertical is arranged between two through holes is arranged symmetrically with.
The present invention has following advantage: antenna circuit of the present invention comprises multiple coil receiving elements of the formation hyperchannel phased array structures be paperwrapped in respectively outside imaging space, multiple coil receiving element can fit patient's mammary gland well to improve the signal to noise ratio (S/N ratio) of detection signal, image quality is high, and the bottom deck assembly that passes through of the present invention, two are formed respectively for holding the imaging space of the Open architecture of patient's mammary gland between supporting cell guide and two through holes, the support of the mammary gland test alive to guided by magnetic resonance is achieved when carrying out magnetic resonance imaging, the imaging space of Open architecture can be applicable to the adaptability of patient's breast of different size shape, to the wide coverage of mammary gland, adaptability is good, contribute to promoting in mammary gland magnetic resonance scanning to the scanning coverage of axillary lymph and wall of the chest tissue and picture quality, the signal to noise ratio (S/N ratio) with detection signal is high, wide coverage, adaptability is good, easy to use, the simple advantage of structure.
Accompanying drawing explanation
In order to be illustrated more clearly in the embodiment of the present invention or technical scheme of the prior art, be briefly described to the accompanying drawing used required in embodiment or description of the prior art below, apparently, accompanying drawing in the following describes is only some embodiments of the present invention, for those of ordinary skill in the art, under the prerequisite not paying creative work, other accompanying drawing can also be obtained according to these accompanying drawings.
Fig. 1 is the perspective view of the embodiment of the present invention.
Fig. 2 is the perspective structure schematic diagram of the embodiment of the present invention.
Fig. 3 is the stereo decomposing structural representation of the embodiment of the present invention.
Fig. 4 is the inside perspective view of baffle plate assembly in the embodiment of the present invention.
Fig. 5 is the inside perspective view of bottom deck assembly in the embodiment of the present invention.
Fig. 6 is the coil receiving element arrangement schematic diagram in the embodiment of the present invention in bottom deck assembly.
Fig. 7 is the coil receiving element arrangement schematic diagram in the embodiment of the present invention in baffle plate assembly.
Fig. 8 is the coil receiving element arrangement schematic diagram along through hole vertical direction in the embodiment of the present invention.
Marginal data:
1, cage assembly;
11, bottom deck assembly; 111, base plate upper casing; 112, base plate lower casing; 113, the first Connection Block; 114, first connects column base; 115, connecting hole;
12, baffle plate assembly; 120, through hole; 121, baffle plate upper casing; 122, baffle plate lower casing; 123, the second Connection Block; 124, second connects column base;
13, supporting cell guide; 131, guide pillar lid;
2, antenna circuit; 21, coil receiving element;
3, imaging space.
Embodiment
Below in conjunction with accompanying drawing, the preferred embodiments of the present invention are described in detail, can be easier to make advantages and features of the invention be readily appreciated by one skilled in the art, thus more explicit defining is made to protection scope of the present invention.
As depicted in figs. 1 and 2, the mammary gland magnetic resonance RF receiving coil that the present embodiment is used for magnetic resonance imaging system comprises cage assembly 1 and is located at the antenna circuit 2 of cage assembly 1 inside, cage assembly 1 comprises bottom deck assembly 11 and the baffle plate assembly 12 for pressing close to human body, baffle plate assembly 12 is provided with two for inserting the through hole 120 of mammary gland, the supporting cell guide 13 of multiple hollow-core construction is provided with between bottom deck assembly 11 and baffle plate assembly 12, bottom deck assembly 11, two are formed respectively for holding the imaging space 3 of the Open architecture of patient's mammary gland between supporting cell guide 13 and two through holes 120, antenna circuit 2 comprises multiple coil receiving elements 21 of the formation hyperchannel phased array structures be paperwrapped in respectively outside imaging space 3.The antenna circuit 2 of the present embodiment comprises multiple coil receiving elements 21 of the formation hyperchannel phased array structures be paperwrapped in respectively outside imaging space 3, multiple coil receiving element 21 can fit well patient's mammary gland to improve the signal to noise ratio (S/N ratio) of detection signal, image quality is high, simultaneously, the supporting cell guide 13 of multiple hollow-core construction is provided with between the bottom deck assembly 11 of the present embodiment and baffle plate assembly 12, therefore, it is possible to ensure that imaging space 3 is open stereoeffect, bottom deck assembly 11, two are formed respectively for holding the imaging space 3 of the Open architecture of patient's mammary gland between supporting cell guide 13 and two through holes 120, its Open architecture can meet the mammary gland biopsy of guided by magnetic resonance, the support of the mammary gland test alive to guided by magnetic resonance is achieved when carrying out magnetic resonance imaging, the imaging space 3 of Open architecture can be applicable to the adaptability of patient's breast of different size shape, to the wide coverage of mammary gland, adaptability is good, contribute to promoting in mammary gland magnetic resonance scanning to the scanning coverage of axillary lymph and wall of the chest tissue and picture quality, the signal to noise ratio (S/N ratio) with detection signal is high, wide coverage, adaptability is good, easy to use, the simple advantage of structure.
As shown in Figure 2, Figure 3 and Figure 4, the bottom deck assembly 11 of the present embodiment comprises the base plate upper casing 111 and base plate lower casing 112 that cooperatively interact, forms the space for installing coil receiving element 21 between base plate upper casing 111 and base plate lower casing 112; Baffle plate assembly 12 comprises the baffle plate upper casing 121 and baffle plate lower casing 122 that cooperatively interact, forms the space for installing coil receiving element 21 between baffle plate upper casing 121 and baffle plate lower casing 122; One end of base plate upper casing 111 is connected with one end of baffle plate lower casing 122 and its connecting portion is provided with connecting hole 115 for installing coil receiving element 21, and the other end of base plate upper casing 111 is connected with one end of baffle plate lower casing 122 by supporting cell guide 13.Because supporting cell guide 13 is hollow-core construction, therefore by supporting cell guide 13 and the connecting hole 115 for installing coil receiving element 21, add the space formed between upper plate upper casing 111 and base plate lower casing 112 for installing coil receiving element 21, the space for installing coil receiving element 21 is formed between baffle plate upper casing 121 and baffle plate lower casing 122, therefore the installation site of all coils receiving element 21 is Open architecture, the formation hyperchannel phased array structures be paperwrapped in by multiple coil receiving element 21 outside imaging space 3 can be realized on the one hand easily, also be convenient on the other hand observe adjustment to the layout of coil receiving element 21, and conveniently inspection and maintenance is carried out to coil receiving element 21.The base plate upper casing 111 of the present embodiment, base plate lower casing 112, baffle plate upper casing 121 and baffle plate lower casing 122 are plastic casing, between base plate upper casing 111 and base plate lower casing 112, between baffle plate upper casing 121 and baffle plate lower casing 122, being connected with all adopting web member between baffle plate lower casing 122 of base plate upper casing 111, in addition plug-in also can be adopted to connect, do not repeat them here.
In the present embodiment, the side of base plate upper casing 111 is provided with the first Connection Block 113, and the opposite side of base plate upper casing 111 is provided with three first connection column bases 114, three first connection column bases 114 and is arranged on same straight line; The side of baffle plate lower casing 122 is provided with the second Connection Block 123, and the opposite side of baffle plate lower casing 122 is provided with and connects corresponding three second of column base 114 respectively with three first and connect column base 124; First Connection Block 113 is connected with the second Connection Block 123, three first connection column bases 114 are connected column base 124 respectively by a supporting cell guide 13 with second and are connected, first Connection Block 113 and the second Connection Block 123 are arranged down in use, form support holder structure, be conducive to safeguarding the position of patient's mammary gland in the imaging space 3 of Open architecture.
In the present embodiment, supporting cell guide 13 is made up of the guide pillar lid 131 that two panels is positioned opposite, one end of two panels guide pillar lid 131 is inserted in the first connection column base 114 jointly, the other end of two panels guide pillar lid 131 is inserted in the second connection column base 124 jointly, therefore facilitate and carry out examination and maintenance to the coil receiving element 21 be arranged between two panels guide pillar lid 131, installing/dismounting is all very simple.
The antenna circuit 2 of the present embodiment comprises 8 coil receiving elements 21, and coil receiving element 21 specifically can adopt printed circuit board (PCB) or copper wires to make as required.
As shown in Figure 5, in the present embodiment, the location arrangements of 8 coil receiving elements 21 is as follows: on bottom deck assembly 11, the location arrangements of relative two through holes 120 has 3 coil receiving elements 21 of arranged superposed; Baffle plate assembly 12 is provided with 2 the coil receiving elements 21 holding through hole 120 respectively; 3 the coil receiving elements 21 arranged along bottom deck assembly 11 vertical direction are provided with between bottom deck assembly 11 and baffle plate assembly 12, wherein 1 coil receiving element 21 is arranged vertically within the position between two through holes 120, all the other 2 coil receiving element 21 size shape are completely the same, be arranged in the outside of two through holes 120 respectively along the axial connecting line of two through holes 120, and the coil receiving element 21 that Relative vertical is arranged between two through holes 120 is arranged symmetrically with.
As shown in Figure 6, on bottom deck assembly 11, the location arrangements of relative two through holes 120 has 3 of arranged superposed coil receiving elements 21 to form passage F, passage G and passage H, passage G is positioned at the middle of bottom deck assembly 11, passage F and passage H size shape completely the same, and be symmetrically distributed in the right and left of passage G and each and passage G formed one little overlapping.
As shown in Figure 7, baffle plate assembly 12 is provided with 2 the coil receiving elements 21 holding through hole 120 respectively and forms passage A and channel B, passage A and B holds through hole 120 respectively, is positioned at the left and right first half of the imaging space 3 holding patient's mammary gland, and encloses the profile in coil aperture.
As shown in Figure 8,3 the coil receiving elements 21 arranged along bottom deck assembly 11 vertical direction between bottom deck assembly 11 and baffle plate assembly 12 form channel C, passage D and passage E respectively, passage D is arranged in the position between two through holes 120, channel C and passage E size shape completely the same, axial connecting line along two through holes 120 is arranged in the outside of two through holes 120 respectively, and the coil receiving element 21 that Relative vertical is arranged between two through holes 120 is arranged symmetrically with, and is namely symmetrically distributed in the right and left of passage D.
The foregoing is only the preferred embodiment of the present invention, protection scope of the present invention is not limited in above-mentioned embodiment, and every technical scheme belonging to the principle of the invention all belongs to protection scope of the present invention.For a person skilled in the art, some improvements and modifications of carrying out under the prerequisite not departing from principle of the present invention, these improvements and modifications also should be considered as protection scope of the present invention.
Claims (5)
1. the mammary gland magnetic resonance RF receiving coil for magnetic resonance imaging system, it is characterized in that: comprise cage assembly (1) and be located at the inner antenna circuit (2) of cage assembly (1), described cage assembly (1) comprises bottom deck assembly (11) and the baffle plate assembly (12) for pressing close to human body, described baffle plate assembly (12) is provided with two for inserting the through hole (120) of mammary gland, the supporting cell guide (13) of multiple hollow-core construction is provided with between described bottom deck assembly (11) and baffle plate assembly (12), described bottom deck assembly (11), two are formed respectively for holding the imaging space (3) of the Open architecture of patient's mammary gland between supporting cell guide (13) and two through holes (120), described antenna circuit (2) comprises multiple coil receiving elements (21) of the formation hyperchannel phased array structures being paperwrapped in described imaging space (3) outside respectively, described bottom deck assembly (11) comprises the base plate upper casing (111) and base plate lower casing (112) that cooperatively interact, forms the space for installing coil receiving element (21) between described base plate upper casing (111) and base plate lower casing (112), described baffle plate assembly (12) comprises the baffle plate upper casing (121) and baffle plate lower casing (122) that cooperatively interact, forms the space for installing coil receiving element (21) between described baffle plate upper casing (121) and baffle plate lower casing (122), one end of described base plate upper casing (111) is connected with one end of baffle plate lower casing (122) and its connecting portion is provided with connecting hole (115) for installing coil receiving element (21), and the other end of described base plate upper casing (111) is connected with one end of baffle plate lower casing (122) by supporting cell guide (13).
2. the mammary gland magnetic resonance RF receiving coil for magnetic resonance imaging system according to claim 1, it is characterized in that: the side of described base plate upper casing (111) is provided with the first Connection Block (113), the opposite side of described base plate upper casing (111) is provided with three first and connects column base (114), and described three first connections column base (114) are arranged on same straight line; The side of described baffle plate lower casing (122) is provided with the second Connection Block (123), and the opposite side of described baffle plate lower casing (122) is provided with and connects corresponding three second of column base (114) respectively with described three first and connect column base (124); Described first Connection Block (113) is connected with the second Connection Block (123), and described three first connections column base (114) are connected column base (124) respectively by a supporting cell guide (13) with second and are connected.
3. the mammary gland magnetic resonance RF receiving coil for magnetic resonance imaging system according to claim 2, it is characterized in that: described supporting cell guide (13) is made up of the guide pillar lid (131) that two panels is positioned opposite, one end of described two panels guide pillar lid (131) is inserted in the first connection column base (114) jointly, and the other end of described two panels guide pillar lid (131) is inserted in the second connection column base (124) jointly.
4. the mammary gland magnetic resonance RF receiving coil for magnetic resonance imaging system according to claim 3, is characterized in that: described antenna circuit (2) comprises 8 coil receiving elements (21).
5. the mammary gland magnetic resonance RF receiving coil for magnetic resonance imaging system according to claim 4, is characterized in that: on described bottom deck assembly (11), the location arrangements of relatively described two through holes (120) has 3 coil receiving elements (21) of arranged superposed; Described baffle plate assembly (12) is provided with 2 the coil receiving elements (21) holding described through hole (120) respectively; 3 coil receiving elements (21) of arranging along bottom deck assembly (11) vertical direction are provided with between described bottom deck assembly (11) and baffle plate assembly (12), wherein 1 coil receiving element (21) is arranged in the position between two through holes (120), all the other 2 coil receiving element (21) size shape are completely the same, be arranged in the outside of two through holes (120) respectively along the axial connecting line of two through holes (120), and the coil receiving element (21) that Relative vertical is arranged between two through holes (120) is arranged symmetrically with.
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| CN201310042180.5A CN103091652B (en) | 2013-02-04 | 2013-02-04 | For the mammary gland magnetic resonance RF receiving coil of magnetic resonance imaging system |
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| CN201310042180.5A CN103091652B (en) | 2013-02-04 | 2013-02-04 | For the mammary gland magnetic resonance RF receiving coil of magnetic resonance imaging system |
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Families Citing this family (4)
| Publication number | Priority date | Publication date | Assignee | Title |
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| CN108652631A (en) * | 2018-05-24 | 2018-10-16 | 安徽大中润科技有限公司 | Mammary gland magnetic resonance is imaged and intervention integrated apparatus and its box body |
| CN109758152A (en) * | 2019-03-07 | 2019-05-17 | 中国科学技术大学 | A kind of mammary gland magnetic resonance elastogram exciting bank and system |
| CN111537929B (en) * | 2020-04-20 | 2023-01-24 | 联影(常州)医疗科技有限公司 | Radio frequency coil assembly and magnetic resonance system |
| CN112137619A (en) * | 2020-09-30 | 2020-12-29 | 达研医疗技术（合肥）有限公司 | Mammary gland coil positioning scanning imaging method |
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| CN203117410U (en) * | 2013-02-04 | 2013-08-07 | 上海辰光医疗科技股份有限公司 | Mammary gland magnetic resonance radio frequency receiving coil for magnetic resonance imaging system |
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| US6163717A (en) * | 1998-11-25 | 2000-12-19 | Toshiba America Mri, Inc. | Open structure breast coil and support arrangement for interventional MRI |
| US9638770B2 (en) * | 2004-05-21 | 2017-05-02 | Devicor Medical Products, Inc. | MRI biopsy apparatus incorporating an imageable penetrating portion |
| US9801565B2 (en) * | 2006-01-30 | 2017-10-31 | Koninklijke Philips N.V. | Methods and workflow design for improving specificity of breast MR |
| CN100469309C (en) * | 2006-03-15 | 2009-03-18 | 上海复旦辰光科技有限公司 | Breast radio-frequency coil device for the horizontal magnetic resonance imaging |
| US20090134965A1 (en) * | 2007-10-11 | 2009-05-28 | Insight Neuroimaging Systems Llc | Efficient methodology for the decoupling for multi-loop rf coil geometries for magnetic resonance imaging |
| DE102008048291B4 (en) * | 2008-09-22 | 2012-02-16 | Siemens Aktiengesellschaft | Breast coil assembly for magnetic resonance applications |
| CN102579046B (en) * | 2011-12-12 | 2013-11-06 | 中国科学院深圳先进技术研究院 | Breast coil device |
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| CN203117410U (en) * | 2013-02-04 | 2013-08-07 | 上海辰光医疗科技股份有限公司 | Mammary gland magnetic resonance radio frequency receiving coil for magnetic resonance imaging system |
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