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    • 12. 发明授权
    • Method for improving the signal-to-noise ratio in a nuclear magnetic
resonance tomography apparatus
    • 改进核磁共振成像装置中信号噪声比的方法
    • US5084675A
    • 1992-01-28
    • US565951
    • 1990-08-10
    • Hans-Erich ReinfelderHubertus Fischer
    • Hans-Erich ReinfelderHubertus Fischer
    • A61B5/055G01R33/32G01R33/56
    • G01R33/56G01R33/543G01R33/5608G01R33/5616
    • In the echo planar imaging (EPI) method of operating a nuclear magnetic resonance (magnetic resonance imaging) tomography apparatus, the necessary, rapid switching of gradients having a high amplitude usually cannot be achieved with square-wave gradients, and therefore a read-out gradient having a sinusoidal shape is generally used. Given a chronologically equidistant sampling of the nuclear magnetic resonance signal in the time domain, however, a sampling in the k-space with different rates is present. The bandwidth of the signal is proportional to the sampling rate in the k-space. In the method disclosed herein, bandwidth of a bandpass filter or a low-pass filter in the signal processing circuit for the nuclear magnetic resonance signal is adapted to the time dependent bandwith of the nuclear magnetic resonance signal, i.e., to the sampling rate in the k-space. The bandwidth is increased with increasing sampling rate. The signal-to-noise ratio is noticeably improved.
    • 在操作核磁共振(磁共振成像)断层摄影装置的回波平面成像(EPI)方法中,通常使用方波梯度不能实现具有高振幅的梯度的必要的快速切换,因此读出 通常使用具有正弦形状的梯度。 然而,鉴于时域上的核磁共振信号的时间上等距离的采样,存在具有不同速率的k空间中的采样。 信号的带宽与k空间中的采样率成比例。 在本文公开的方法中,用于核磁共振信号的信号处理电路中的带通滤波器或低通滤波器的带宽适应于核磁共振信号的时间依赖带宽,即适应于 k空间。 带宽随采样率的增加而增加。 信噪比明显提高。
    • 13. 发明授权
    • Method for operating a nuclear magnetic resonance tomography apparatus
    • 用于操作核磁共振断层摄影装置的方法
    • US4825159A
    • 1989-04-25
    • US183231
    • 1988-04-19
    • Arnulf OppeltHubertus FischerHelmut Barfuss
    • Arnulf OppeltHubertus FischerHelmut Barfuss
    • A61B5/055G01R33/48G01R33/50G01R33/56G01R33/20
    • G01R33/56G01R33/50
    • An examination subject is irradiated with a sequence of RF pulses. Negative gradient pulses G.sub.z3 and G.sub.y4, as well as a phase-coding gradient G.sub.x2 are generated preceding each RF pulse. Negative gradient pulses G.sub.z2 and G.sub.y1, as well as a phase-coding gradient G.sub.x1, are generated following each RF pulse. The phase-coding gradient G.sub.x1 is inverted relative to the phase-coding gradient G.sub.x2. The negative gradient pulse G.sub.y1 is followed by a positive gradient pulse G.sub.y2 which serves as a read-out gradient during which a first signal S.sub.1 is received. A positive gradient pulse G.sub.y3 is generated preceding the negative gradient pulse G.sub.y4, the positive gradient pulse G.sub.y3 serving as a read-out gradient during which a second signal S.sub.2 is received. Two signals having different T.sub.2 weighting are thus obtained in each measuring sequence, without extending the measuring time. Two images having different T.sub.2 contrast, and thus increased diagnostic value, can thus be produced.
    • 用一系列RF脉冲照射检查对象。 在每个RF脉冲之前产生负梯度脉冲Gz3和Gy4,以及相位编码梯度Gx2。 在每个RF脉冲之后产生负梯度脉冲Gz2和Gy1以及相位编码梯度Gx1。 相位编码梯度Gx1相对于相位编码梯度Gx2反转。 负梯度脉冲Gy1之后是用作接收第一信号S1的读出梯度的正梯度脉冲Gy2。 在负梯度脉冲Gy4之前产生正梯度脉冲Gy3,正梯度脉冲Gy3用作接收第二信号S2的读出梯度。 因此,在每个测量序列中获得具有不同T2加权的两个信号,而不延长测量时间。 因此可以产生具有不同T2对比度,从而增加诊断价值的两个图像。
    • 15. 发明申请
    • PEDIATRIC COIL ASSEMBLY
    • 小型线圈总成
    • US20120126814A1
    • 2012-05-24
    • US12950746
    • 2010-11-19
    • Hubertus FischerHiroyuki FujitaJoseph HerczakLars Lauer
    • Hubertus FischerHiroyuki FujitaJoseph HerczakLars Lauer
    • G01R33/44
    • G01R33/34084G01R33/30G01R33/34007G01R33/34046G01R33/3415
    • In order to increase the signal to noise ratio, and thus increase the quality of images produced during pediatric MRI, a pediatric RF coil assembly includes a head coil and a flexible body coil in a single dedicated device shaped and sized for a child. The flexible body coil may be operable to at least partially surround and abut the body of the child located on the pediatric RF coil assembly, while the head coil may at least partially surround and abut the head of the child located on the pediatric RF coil assembly. In order to optimize workflow, the child may be positioned on the pediatric RF coil assembly in a first room and moved to a second room including an MRI system after the child is brought to sleep or sedated in the first room. The pediatric RF coil assembly and the child may be moved to the second room using a handle rotatably attached to the pediatric RF coil assembly, and may be positioned on a patient table of the MRI system when the imaging process is to begin.
    • 为了增加信噪比,从而增加儿科MRI期间产生的图像的质量,儿科RF线圈组件包括头部线圈和柔性体线圈,其形状和尺寸适合于儿童。 柔性体线圈可以可操作以至少部分地围绕和邻接位于儿科RF线圈组件上的儿童的身体,而头部线圈可以至少部分地围绕和邻接位于儿科RF线圈组件上的儿童的头部 。 为了优化工作流程,孩子可以定位在第一房间中的小儿RF线圈组件上,并且在儿童在第一房间中睡眠或镇静之后移动到包括MRI系统的第二房间。 可以使用可旋转地附接到儿科RF线圈组件的手柄将小儿RF线圈组件和儿童移动到第二房间,并且当成像过程开始时,可​​将其放置在MRI系统的患者台上。