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    • 21. 发明授权
    • Magnetic resonance imaging with integrated poleface features
    • 具有集成极面特征的磁共振成像
    • US6147495A
    • 2000-11-14
    • US141990
    • 1998-08-28
    • Gordon D. DeMeesterJohn V. M. McGinleyIan R. Young
    • Gordon D. DeMeesterJohn V. M. McGinleyIan R. Young
    • A61B5/055G01R33/383G01R33/3873G01V3/00
    • G01R33/383G01R33/3873
    • A magnetic resonance imaging scanner includes a pair of opposing pole pieces (20, 20') disposed symmetrically about an imaging volume (24) facing one another. The pair of opposing pole pieces (20, 20') includes a first ferrous pole piece (20) which has a front side (22) facing the imaging volume (24) and a back side (28). Also included is a second ferrous pole piece (20') which also has a front side (22) facing the imaging volume (24) and a back side (28). A magnetic flux return path (30) extends, remotely from the imaging volume (24), between a point adjacent the back side 28 of the first pole piece (20) and a point adjacent the back side 28' of the second pole piece (20)'. A source of magnetic flux generates a magnetic flux through the imaging volume (24), the pair of opposing pole pieces (20, 20'), and the magnetic flux return path (30). An array of annular hoops (40) and (40') are integrated with the pair of opposing pole pieces (20, 20') for homogenizing the magnetic flux through the imaging volume (24). The annular hoops (40, 40') are made of a material having magnetic properties different from those of the pair of opposing pole pieces (20, 20').
    • 磁共振成像扫描器包括一对相对的极片(20,20'),所述相对极片相对于彼此面对的成像体积(24)对称设置。 一对相对的极片(20,20')包括具有面向成像体积(24)的前侧(22)和后侧(28)的第一铁极片(20)。 还包括还具有面向成像体积(24)的前侧(22)和后侧(28)的第二铁极片(20')。 远离成像体积(24)的磁通返回路径(30)在与第一极靴(20)的背侧28相邻的点与邻近第二极靴的后侧28'的点之间延伸 20)'。 磁通源产生通过成像体积(24),一对相对极片(20,20')和磁通量返回路径(30)的磁通量。 环形环(40)和(40')的阵列与所述一对相对的极片(20,20')集成,用于使通过成像体积(24)的磁通量均匀化。 环形环(40,40')由具有与一对相对极片(20,20')不同的磁性能的材料制成。
    • 22. 发明授权
    • MRI magnet with fast ramp up capability for interventional imaging
    • MRI磁铁具有快速上升的介入成像能力
    • US6097187A
    • 2000-08-01
    • US915624
    • 1997-08-21
    • Vishnu SrivastavaGordon D. DeMeesterMichael A. Morich
    • Vishnu SrivastavaGordon D. DeMeesterMichael A. Morich
    • G01R33/3815G01R33/3875G01V3/00
    • G01R33/3815G01R33/3875
    • Primary superconducting coils (50) generate a magnetic field through an examination region (10). Stabilizing coils (70) are magnetically coupled with the magnetic field generated by the primary coils. A primary persistence switch (60) and a stabilizing coils persistence switch (72) are opened when the primary coils are connected to a current source (62) to ramp-up the magnetic field. The persistence switches are closed, disconnecting the primary coils from the current source and connecting the primary coils and the stabilizing coils into closed loops. As the magnetic flux generated by the primary coils fluctuates as the primary coils stabilize, the changing flux induces currents in the stabilizing coils. The currents induced in the stabilizing coils generate an offsetting magnetic flux such that the net magnetic flux generated by the primary and stabilizing coils is held constant.
    • 初级超导线圈(50)通过检查区域(10)产生磁场。 稳定线圈(70)与由初级线圈产生的磁场磁耦合。 当初级线圈连接到电流源(62)以升高磁场时,主持续开关(60)和稳定线圈持续开关(72)打开。 持续开关闭合,将初级线圈与电流源断开,并将初级线圈和稳定线圈连接成闭合回路。 随着初级线圈产生的磁通量随着初级线圈的稳定而波动,变化的磁通会引起稳定线圈中的电流。 在稳定线圈中感应的电流产生偏移磁通,使得由初级和稳定线圈产生的净磁通保持恒定。
    • 23. 发明授权
    • Movable magnets for magnetic resonance surgery
    • 用于磁共振手术的活动磁铁
    • US6029081A
    • 2000-02-22
    • US44425
    • 1998-03-19
    • Gordon D. DeMeesterIan R. Young
    • Gordon D. DeMeesterIan R. Young
    • G01R33/38A61B5/055
    • G01R33/3806
    • A magnetic resonance imaging apparatus (10) includes a couch (54) for supporting a region of interest of a subject (44) being examined in an examination region. A main magnet for generating a substantially uniform temporally constant main magnetic field through the examination region includes a stationary pole piece (24), a movable pole piece (22), a ferrous flux return path (26), and a magnetic flux generator that selectively generates magnetic flux that flows between the pole pieces (22, 24) through the examination region and through the ferrous flux return path (26) which connects the pole pieces (22, 24). The stationary pole piece (24) is arranged adjacent a first side of the examination region. The movable pole piece (22) is arranged to be selectively moved between a first position adjacent a second side of the examination region opposite the stationary pole piece (24) so that the stationary and movable pole pieces (24, 22) define the examination region therebetween, and a second position remote from the examination region.
    • 磁共振成像装置(10)包括用于支撑在检查区域中检查的被检体(44)的感兴趣区域的沙发(54)。 用于通过检查区域产生基本上均匀的时间常数的主磁场的主磁体包括固定极片(24),可动极片(22),铁磁返流路径(26)和选择性地 产生通过检查区域在极片(22,24)之间流动并通过连接极片(22,24)的铁质磁通返回路径(26)的磁通量。 静止极片(24)布置成与检查区域的第一侧相邻。 所述可动极片(22)被布置成选择性地在与所述静止极片(24)相对的所述检查区域的第二侧的第一位置之间移动,使得所述固定和可动极片(24,22)限定所述检查区域 并且远离检查区域的第二位置。
    • 24. 发明授权
    • Superconducting gradient shield coils
    • 超导梯度屏蔽线圈
    • US5289128A
    • 1994-02-22
    • US859152
    • 1992-03-27
    • Gordon D. DeMeesterJohn L. PatrickMichael A. Morich
    • Gordon D. DeMeesterJohn L. PatrickMichael A. Morich
    • A61B5/055G01R33/20G01R33/38G01R33/385G01R33/421H01F6/00
    • G01R33/3856G01R33/385G01R33/4215
    • An examination region (12) is defined within the bore of a superconducting magnet assembly (10). An RF coil (22) and gradient magnetic field coils (14) are disposed within the bore of the superconducting magnet assembly around the examination region. The superconducting magnet includes a hollow, cylindrical vacuum vessel (40). An annular, liquid helium holding low temperature reservoir (60) extends centrally through the vacuum vessel, but is sealed therefrom such that liquid helium is not drawn into the vacuum. A plurality of annular superconducting magnets (56) are received in the low temperature reservoir immersed in the liquid helium. A first cold shield (44) and a second cold shield (50) are mounted in the vacuum vessel surrounding the low temperature reservoir. A main magnetic field shield coil (66) is disposed in the low temperature reservoir outside of the annular superconducting magnets for canceling the magnetic field generated by the annular magnets surrounding the magnet. A gradient shield coil (70) is mounted in low temperature reservoir inside the annular superconducting magnets to cancel magnetic fields generated by the gradient magnetic field coils in the region beyond the gradient shield coil. The gradient shield coil is electromagnetically coupled to the gradient field coils to be driven by magnetic fields emanating therefrom. Optionally, the gradient shield coil can be constructed of a higher temperature superconducting material and disposed in association with one of the cold shields.
    • 检查区域(12)被限定在超导磁体组件(10)的孔内。 RF线圈(22)和梯度磁场线圈(14)被布置在超导磁体组件的围绕检查区域的孔内。 超导磁体包括中空的圆柱形真空容器(40)。 一个环状的液氦保持低温储存器(60)在真空容器的中心延伸,但被密封,使得液氦不被吸入真空。 多个环形超导磁体(56)被容纳在浸入液氦的低温储存器中。 第一冷屏蔽(44)和第二冷屏蔽(50)安装在围绕低温储存器的真空容器中。 主磁场屏蔽线圈(66)设置在环形超导磁体外部的低温储存器中,用于抵消围绕磁体的环形磁体产生的磁场。 梯度屏蔽线圈(70)安装在环形超导磁体内部的低温储存器中,以消除梯度屏蔽线圈之外的区域中的梯度磁场线圈产生的磁场。 梯度屏蔽线圈与梯度场线圈电磁耦合,由其发出的磁场驱动。 可选地,梯度屏蔽线圈可以由更高温度的超导材料构成并且与其中一个冷屏蔽件相关联地设置。