CN1113138A - 采用螺旋扫描的计算机层析x射线照相法 - Google Patents
采用螺旋扫描的计算机层析x射线照相法 Download PDFInfo
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Abstract
本发明提供一种采用螺旋扫描的计算机层析X
射线照相技术,采用这种技术可大大降低噪声和局部
分辨率的不均匀性。
对于通过互补数据插入的投影来说最佳滤波器
的频率特性按上式计算。
Description
在计算机层析X射线照相法(CT)中,传统的普遍采用的单层照相被螺旋-CT-技术的连续不断的体积照相所代替。为了从所拍摄的体积重现一单张照片,有必要在移动方向(Z-轴)采用能建立数据组的插入法。该数据组相当于一个平面的单层照片。期间,建立了螺旋-CT,同时为进一步改进采用了各种不同的插入法。采用这种不同的内插入法,以便来调节照片的体层灵敏度轮廓图形和照片的噪声特性。如果想尽量使外形形成细长形,即在Z-方向尽量得到较高的局部分辨率,就必需使用所谓的180°-算法。这种方法的实施是通过权重方法来完成,以便尽可能地减少计算费用。
在用这种方法获得的照片组中,特别是在大的物体中常常显示出噪声图形和物体的图象清晰度不均匀的分布。对此,需要通过一张照片一张照片地循环调整来改变这种分布。这里所说的一次循环相当于X射线管进行360°-回转时所移动的距离。图1是根据想象绘出的。图1示出与螺旋权重W(θ)有关的相对变化的曲线。这种不均匀的分布是一种干扰且能妨碍检查人员的工作。当对照片数据进行阀值以上的三维显示时,这种不均匀分布可能造成其它的人为现象。所产生的这种显示结果在任何情况下与180°-的特殊算法具有很大区别。
本发明的目的在于:为螺旋扫描的计算机层析X射线照相技术提供一种算法。这种算法可有效地降低噪声与图象清晰度分布的不均匀性,且在多数情况下可消除这种不均匀性。
本发明的解决方案是通过权利要求的特征来解决的。
下面根据图中描绘的实施例对本发明作详细的说明,如图所示:
图1:表示与螺旋权重W(θ)有关的相对变化的曲线。
图2:用于详细说明本发明的计算机层析X射线照相。
图3:对图2中计算机层析X射线照相进行详细说明的曲线。
图2示出一发出扇形X射线束2的X射线源1,该扇形X射线束入射在一个向X射线源1的焦点弯曲的并由一排探测元件组成的射线探测器3上。在X射线源1和射线探测器3之间有一病人5和病床4。
为了扫描病人5的身体,将病床4按箭头6方向以预定的速度调动,同时测量元件1、3围绕系统轴7按箭头所示旋转。在此,由射线探测器3的探测元件提供的数据传输给计算机8,该计算机从中计算病人5的照片并将其重新反应在显示器9上。这些照片就是经扫描过的计算机层析X射线体层照片。将病床4沿箭头6方向调动,以便对病人5预定的体积进行扫描的取代方法是,可在病床4不动时沿箭头10方向对探测元件1、3进行调动。
在进行所示的计算机层析X射线体层照相时,通过采用互补的180°-螺旋内插补法按照下式来产生平面数据组:
PZ(γ,θ)=(1-W(θ))·Pz1(γ,θ)+W(θ)·Pz2(γ,θ)(1)式中,PZ(γ,θ)-属于位置Z的平面数据组的投影,探测角为γ,投影角为θ,
W(θ)-为螺旋权重:W(θ)=(Z-Z1)/(0.5d),d是每次螺旋循环的平台的移动,Z1=平台位置,此时平台位置为P1(γ,θ)。
PZ1(γ,θ)-平台位置的测量数据,在该平台位置上,当最后一次到平台位置Z之前所占有的角度为θ或θ+π。
PZ2(γ,θ)-相当于180°互补数据。
用通常的折叠背面投影法,将所产生的平面数据组PZ(γ,θ)加工成照片。也可以在背面投影时通过螺旋数据组每次投影的权重进行螺旋内插补。这种近似的解决方案很容易实现,也就是说,在流水线运行时,在现有的硬件上,在计算机8中使用流水线处理器(处理程序)。内插补法与权重法均能导致照片中噪声分布不均匀(即使物体完全对称),其中权重法产生了很大的不均匀性,且从照片质量来看也有些缺点。按照式(1)的内插法会导致噪声的不均匀性,因为在投影PZ中的噪声水平取决于投影角度。对于
PZ1(γ,θ)=P1+n1(ξ)
PZ2(γ,θ)=P2+n2(ξ)(2)
式中Pi-为投影i的测定部分,
ni(ξ)-为随机变量,它模拟σ2 0方差的量子噪声。
这些描述了内插补法投影的方差
Var{PZ(γ,θ)}=σ2 0(1-2W(θ)+2W2(θ))(3)
其中,Var{·}-为方差算符。
投影角度的函数的方差在图1中示出。在式(3)与图1中可直接看到:噪声水平有显著变化,并在照片中的不均匀性很明显。为了避免这种效果,建议在所有的内插补的投影中采用平衡(补偿)噪声水平的方法。这种方法不仅能平衡(补偿)方差而且还能补偿整个功率频谱,以保证照片中的噪声分布均匀。假如,投影与噪声为统计正交,则内插补的投影的功率频谱见下式:
S{PZ(γ,θ)}=S{(1-W(θ))·(P1+n1(ξ))+W(θ)·(P2+n2(ξ))}
=S{(1-W(θ))·P1+W(θ)·P2}+(1-W(θ))2·S{n1(ξ)}+W2(θ)·S{n2(ξ)} (4)
式中S{·}-为功率频谱算符,
在式(4)中看到,只有当信号与噪声不重叠时整个功率频谱补偿才有可能。如果由于物理上的原因不是这种情况,则按照距离平方最小值原理,可进行尽可能好的补偿。参见式(4),W=0.5作为参考(基准),即标准信号也含有噪声。这种最佳化提供了以下最佳维纳氏(wiener)滤波器:
其中,H(f,θ)-最佳维纳氏滤波器的频率特性,
i,j-为互补投影的相应指数,
为了找到实用的解决方案,我们做了如下假定:
S{P1}=S{P2}=S{Pi}=S{Pj}=S0(6)
即,投影的功率频谱不在人们所需范围的Z-方向进行改变,为的是整理位置Z的照片,另外该噪声是局部固定的,且得知方差为σ2 0,该方差允许写成:
H(f,θ)= (S0+0.5σ0 2)/(S0+(1-2W(θ)+2W2(θ))·σ0 2) (7)
图3中示出了式(7)中典型滤波器的有关曲线。人们需要该投影功率频谱按式(7)进行最佳滤波器的设计。对此,可用不同的方法来实现。由于假定:噪声是局部固定的,则必须是相应的数据块及滤波器有较短的最佳长度。这些对于功率频谱的判断方法来说是一个很复杂的限制。即使是采用相当稳定的参数方法,它也会导致不稳定的情况出现。因为,对于短的数据段来说,投影的功率频谱包含很低的部分,所以稳定的并能实际应用的公式(7)可以近似为:
H+(f,θ)=F0(f)· (0.5-2W(θ)+2W2(θ))/((1-2W(θ)+2W2(θ))) + 0.5/((1-2W(θ)+2W2(θ))) (8)
对于函数F0,应保证有一个好的近似值。另外,逆傅里叶变换的长度(即滤波系数的数目)尽可能小。因为函数F0与滤波长度取决于扫描器参数和物体,所以在任何情况下必须分别实现最佳化。Blackman Fenster函数可以作为许多可能的形式之一,提供很好的具有较少滤波系数的结果。在这种情况下该滤波器用以下公式表达。
h(k,θ)= 0.5/((1-2W(θ)+2W2(θ))) + (0.5-2W(θ)+2W2(θ))/((1-2W(θ)+2W2(θ))) ·
(9)
fk-为窗值。
在Blackman Fenster时其长度为N:
fk=0.42-0.5·cos( (2π(k-(N-1)/2))/(N-1) )+0.08·cos( (4π(k-(N-1)/2)/(N-1) )
(10)
典型的滤波器长度,系数为5-13,并提供好于10%的噪声均匀性。式(8)与式(9)描述了一种低通滤波器,其性能由W(θ)来调制。例如:W=0.5就是说作为标准信号,该滤波器未影响到数据;如W=0或W=1为效果最佳,所述方法的有效性与目前采用的权重法相比是很高的。
Claims (3)
1、螺旋扫描的计算机层析X射线照相法,在这种照相技术中按下式计算由互补数据插入的投影的功率频谱:
S{PZ(γ,θ)}=S{(1-W(θ))·(P1+n1(ξ))+W(θ)·(P2+n2(ξ))}
=S{(1-W(θ))·P1+W(θ)·P2}+(1-W(θ))2·S{n1(ξ)}+W2(θ)·S{n2(ξ)}
2、根据权利要求1的计算机层析X射线照相法,采用这种照相技术按简化了的下式计算所述最佳滤波器的频谱特性,以便使噪声分布均匀,
H(f,θ)= (S0+0.5σ0 2)/(S0+(1-2W(θ)+2W2(θ))·σ0 2)
其中,S{P1}=S{P2}=S{Pi}=S{Pj}=S0
3、根据权利要求2的计算机层析X射线照相法,采用这种照相技术使滤波器近似于下式的最佳滤波的值H+(f,θ),以便噪声分布均匀,
H+(f,θ)=F0(f) (0.5-2W(θ)+2W2(θ))/((1-2W(θ)+2W2(θ))) + 0.5/((1-2W(θ)+2W2(θ)))
其中,通过补偿函数F0来保证得到很好的近似值。
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DE19625863C2 (de) * | 1996-06-27 | 2002-06-27 | Siemens Ag | Verfahren zur Bildrekonstruktion für einen im Spiralbetrieb arbeitenden Computertomographen |
US5818896A (en) * | 1996-11-18 | 1998-10-06 | General Electric Company | Methods and apparatus for three-dimensional and maximum intensity projection image reconstruction in a computed tomography system |
US6115487A (en) * | 1998-01-08 | 2000-09-05 | General Electric Company | Correction algorithm for bone-induced spectral artifacts in computed tomograph imaging |
US6493416B1 (en) | 2001-11-21 | 2002-12-10 | Ge Medical Systems Global Technology Company, Llc | Method and apparatus for noise reduction in computed tomographic systems |
US6754300B2 (en) * | 2002-06-20 | 2004-06-22 | Ge Medical Systems Global Technology Company, Llc | Methods and apparatus for operating a radiation source |
US20090185655A1 (en) * | 2004-10-06 | 2009-07-23 | Koninklijke Philips Electronics N.V. | Computed tomography method |
US7711170B2 (en) * | 2005-05-10 | 2010-05-04 | General Electric Company | Method and system for filtering scan data |
CN103054961B (zh) * | 2011-10-24 | 2014-08-13 | 西安世纪盛康药业有限公司 | 肾康注射液在制备治疗慢性肾功能衰竭并发症或由透析引起的并发症的药物中的应用 |
CN103099854B (zh) * | 2011-11-11 | 2014-08-13 | 西安世纪盛康药业有限公司 | 肾康注射液在制备防治心脑血管疾病药物中的应用 |
CN103099853B (zh) * | 2011-11-11 | 2014-08-13 | 西安世纪盛康药业有限公司 | 肾康注射液在制备防治深静脉栓塞药物中的应用 |
CN107505344A (zh) * | 2017-07-25 | 2017-12-22 | 中国海洋石油总公司 | 利用“最小二乘积”法的岩性解释方法 |
CN109215019B (zh) * | 2018-08-24 | 2021-04-23 | 华南农业大学 | 一种基于原木弯曲度的木材切分点定位方法和装置 |
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