200800109 九、發明說明： 【發明所屬之技術領域】 &本發明係關於—掃描單元、-斷層攝影裝置及-斷層攝 影方法’尤其係關於用於一電腦斷層攝影裝置之掃描單 元、一電腦斷層攝影裝置及一電腦斷層攝影方法。 【先前技術】 電腦化斷層攝影（ct)係—使用數位處理來產生—研究中 物件（受關注物件、檢查中物件）内的三維影像之過程二並 :來自二系列從圍繞一旋轉之單軸取得的二維x射線影 。ct影像之重建可藉由應用適當演算法完成。 / CT成像之基本原理係_檢查中物件之投射資料由一 c丁 統之偵測器取得。投射資料表示由輻射束通過之物件的 為了自投射資料產生影像，此等投射資料（線積分） 個2射回而導致二維影像，即表示一碟狀。可重建複數 —維影像中之一所謂立體像素表示法，即一種三維 ’、表丁法右偵測器已以平面形式配置，則可達到一 用二維螺旋重建=體像素。此處理可使 同執彳了〜、中—投射之«器資料的不 :刀係在不同位置處投射回而成為平面，其甚至可有一 不同方向。為了使用於檢杳从 係引入用W 時間有效地實質減少， 已知—藉1描若干平行層之方法。自US 4 303 830中， 射源數目斷層攝影系統係包含若干輻射源及-些與輻 接收器，射接收器由-列_ 錢射接收器係配置以在旋轉轴方向中偏離， H9525.doc 200800109 以致複數個層係同時被掃描，即從 .^ ^ 攸田谷早一輻射接收器取 得的資料，可重建表示經掃描物件的一層。 在現代更精緻的所謂，，錐形射束，，CT及重建方法中，二唯 ㈣器之投射資料（即具有配置成矩陣形式之複數個㈣ 70件的债測器）係直接投射回，成為-單-重建步驟中之 立體像素的三維分佈。電腦斷層攝影中之目前趨勢係依增 加㈣器列數目之方向進行，且因此朝向極大幅度涵蓋檢 查中之物件。 電腦斷層攝影之-重要應用係所謂心臟電腦斷層攝影， 其係與重建心臟跳動之：r維旦彡推士日日 轫（一、、隹衫像有關。具有大偵測器之系 統（即包括二維偵測單元的系統）將允許使用一圓形或幾乎 圓形轨跡涵蓋整個心臟，即無螺旋式重建之必要。為了辦 加此等類型之掃描器的時間解析度，具有若干輕射源^ 稱為管）之配置，及在CT之一高架上的偵測器已於之前提 出。二或三管及谓測器(包括伯測元件矩陣)可安裝在高架 上。當將谓測器以正確關係彼此相對地置放時，則 花普通時間之一半或三分之—漆猶& ^ 〆一刀之來獲取一整組投射。在此一 心臟CT掃描之理想情況中’係獲取橫跨U0度（或360度）之 角範圍的資料，使得此角範圍係分成不重疊之分段，其中 =刀&係由一㈣器提供。然而’谓測器之對應配置在該 耗圍中（其中使用來自若干伯測器的資料）提供相同樣本。 此增加系統對於混淆假影之靈敏性。 需要提供一種用於斷層攝影裝置之替代掃描單元、一斷 ★攝如3置’及-斷層攝影方法’其較不傾向於線積分之 I19525.doc 200800109 非最佳取樣，或可 此需要可藉由二 像中之假影的發生。 掃描單元Π: 請求項用於-斷層攝影裝置之 〇田早:、_層攝影裝置及斷層攝影方 【發明内容】 σ 依據一範例性具體實施 置之掃描單元，…七'㈣於-斷層攝影裝 早。亥％描早凡包含複數個偵測單元，直 债測單元包含配置在行及列中之複數個伯測元件。；等偵 測：：係以：：列第一债測單元之該等谓測元件相對於」 列弟一 _早％具有—㈣元件之—預定分數 方式彼此相對地偏移。 菊離之 依據-斷層攝影裝置之一範例性具體實施例，一斷層攝 ，裝置包含-掃描=元，其中該掃描單元包含複數㈣測 早元’其中各4貞測單元包含gjy署太― 匕3配置在仃及列中的複數個摘測 讀。該等偵測單元係以使m貞測單元之該等制 元件相對於-列第二债測單元具有一谓測元件4一預定分 數的一偏離之方式彼此相對地偏移。 依據-範例性具體實施例，—種用於重建__檢查中物件 的影像之斷層攝影方法，係使用依據本發明之一範例性具 體實施例之斷層攝影裳置，其中該方法包含發射至少一輻 射束，在至少-輻射束穿過檢查中物件後以複數個偵測： 元偵測該至少-輻射束，且藉由該等偵測單元提供信號指 示用於檢查中之物件。較佳係，檢查中物件之影像係由此 等信號或資料中重建。 本發明之一範例性具體實施例的主旨係提供一種用於一 H9525.doc 200800109 斷層攝影裝置(如電腦斷層攝 掃描單元包含複數個偏測單元。此等)二;…其中該 -些摘測元件，其係配置成一矩陣之二早'之各者包含 中。尤复伤兮莖扁、日t 夕式，即在行及列 一係w亥專偵測早元係以一 置，以致_筮 ..t 式彼此相對地配 乂致弟-偵測單元之各列债 偵測單元之別扁、Βϊ _ L 卞你相對於一第二 偵測7〇件偏移。換句話 係未對準爷蓉χ , °亥專列偵測單元 了 +忒4另—偵測單元列，而是 配。 兄破此相對之失 此偏移或偏離可導致不同偵 事實。此夺料心取樣圖案交錯的 又錯可導致改進斷層攝影影像之重建口所 係重建影像的解析度〜於資料間之二宜尤其 以增加。在血型t认失配的事實得 仕，、t l月況中，一掃描單元 係藉由一罝一 7占， 心刀奴（其中各分段 早偵測單元提供）確實重疊，复 技術之掃描單亓由^ ± /、中在依據先刖 同偵測單元之門…， 相冋置放時(即不 早疋之間之列偵測元件未偏移）， 分之非最佳取样 ^ 致線積200800109 IX. Description of the invention: [Technical field to which the invention pertains] & The present invention relates to a scanning unit, a tomography apparatus and a tomography method, in particular to a scanning unit for a computer tomography apparatus, a computerized tomography Photography device and a computer tomography method. [Prior Art] Computerized tomography (ct) - the use of digital processing to generate - the process of studying the three-dimensional image of objects (objects of interest, objects under inspection) and two: from the two series from a single axis around a rotation The obtained two-dimensional x-ray shadow. The reconstruction of the ct image can be done by applying an appropriate algorithm. / The basic principle of CT imaging _ The projection data of the object inspected is obtained by a c-system detector. The projected data indicates that the object passing through the radiation beam produces an image for self-projecting data, and the projection data (line integral) is 2 shots to cause a two-dimensional image, that is, a dish. Reconstructible complex - One of the so-called voxel representations in a dimensional image, that is, a three-dimensional ', and the right-of-view detector has been configured in a planar form to achieve a two-dimensional spiral reconstruction = body pixel. This process can be used to perform the projection of the ~, the medium-projection data, and the knife system is projected back at different positions to become a plane, which can even have a different direction. In order to be used for inspection, the introduction of the W time is effectively reduced substantially, and it is known to describe the method of several parallel layers. In US 4 303 830, the source number tomography system comprises a plurality of radiation sources and some of the radiation receivers, the radiation receivers being configured by the -column receiver to deviate in the direction of the axis of rotation, H9525.doc 200800109 So that multiple layers are scanned at the same time, that is, from the data obtained by the ^^ 攸田谷早一辐射接收, a layer representing the scanned object can be reconstructed. In modern, more sophisticated so-called, conical beams, CT and reconstruction methods, the projection data of the two (four) devices (ie, the debt detectors with a plurality of (four) 70 pieces configured in a matrix form) are directly projected back, The three-dimensional distribution of the voxels in the-single-reconstruction step. The current trend in computed tomography is in the direction of increasing the number of (4) columns, and therefore covers the objects in the inspection to a very large extent. Computer Tomography - The important application is the so-called cardiac computed tomography, which is related to the reconstruction of the heart beat: r. 维 彡 彡 彡 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一 一The system of 2D detection units will allow the use of a circular or nearly circular trajectory to cover the entire heart, ie the need for a spiral-free reconstruction. In order to handle the time resolution of these types of scanners, there are several light shots. The configuration of source ^ is called tube), and the detector on one of the CT overheads has been proposed before. Two or three tubes and predators (including matrix of test elements) can be mounted on the overhead. When the predators are placed opposite each other in the correct relationship, one or a half of the normal time is taken—a lacquer to get a whole set of projections. In the ideal case of a cardiac CT scan, the data is obtained across the angular range of U0 (or 360 degrees), so that the angular range is divided into non-overlapping segments, where = knife & provide. However, the corresponding configuration of the 'predicate' provides the same sample in this cost (where data from several detectors is used). This increases the sensitivity of the system to confusing artifacts. There is a need to provide an alternative scanning unit for a tomographic apparatus, a method such as a 3' and a tomography method, which is less inclined to line integration. I19525.doc 200800109 is not optimally sampled, or may be borrowed The occurrence of false shadows in the two images. Scanning unit Π: The request item is used for the tomography apparatus: 〇田早:, _ layer photographic apparatus and tomographic apparatus [Summary of the invention] σ According to an exemplary implementation of the scanning unit, ... seven '(four) to - tomography Installed early. The hexagram includes a plurality of detection units, and the direct debt measurement unit includes a plurality of test elements arranged in rows and columns. Detecting:: The following components of the first debt measuring unit are offset from each other with respect to the "Liandi"_early %-(four) elements-predetermined fractional manner. According to an exemplary embodiment of a tomographic apparatus, a tomographic apparatus includes a scan=element, wherein the scanning unit includes a plurality of (four) early detection elements, wherein each of the four measurement units includes a gjy department too-匕3 Configure multiple readings in the 仃 and columns. The detecting units are offset relative to each other such that the elements of the m measuring unit are offset from each other by a predetermined deviation of the pre-measuring element 4 with respect to the -column second measuring unit. According to an exemplary embodiment, a tomographic method for reconstructing an image of an object in an inspection is performed using a tomographic apparatus according to an exemplary embodiment of the present invention, wherein the method comprises transmitting at least one The radiation beam, after at least the radiation beam passes through the object under inspection, detects the at least-radiation beam by a plurality of detections: and the signal is provided by the detection unit to indicate the object for inspection. Preferably, the image of the object under inspection is reconstructed from such signals or data. The subject matter of an exemplary embodiment of the present invention provides a tomographic apparatus for a H9525.doc 200800109 (such as a computer tomography unit comprising a plurality of offset units.) 2; The components, which are configured as a matrix of two early, are included. In particular, the stalks are flat and the stalks are in the form of a stalk, and the singularity of the sacred sacs is used to detect the early primordial system, so that _筮..t is matched with each other. Each of the debt detection units is flat, Βϊ _ L 卞 you are offset from a second detection 7 〇. In other words, it is not aligned with Ye Rongzhen, ° Hai special detection unit + 忒 4 another - detection unit column, but with. Brothers break this relative loss. This offset or deviation can lead to different facts. This misalignment of the sampling pattern of the capture heart can result in an improved resolution of the reconstructed image reconstructed by the reconstructed image of the tomographic image~ especially between the data. In the case of blood type t recognition mismatch, in the case of tl month, a scanning unit is occupied by one to seven, and the heart-knife slave (which is provided by each segment early detection unit) does overlap, and the scanning of the complex technology The single 亓 is ^ ± /, the middle is based on the first detection unit's door..., when it is placed (ie, the detection component is not offset between the early detection), the non-optimal sampling is Line product
佳取樣。若轉速太快或使用所謂 取樣）或所▲田一 叉“、、點取樣（DFS —斤明z方向焦點取樣（zFS取樣）（即 之焦點位置俜名上杜 便其中輻射源 此# 1厘〜間切換之取樣方法）之情況下， 八貫°依據—範例性具體實施例，使用一#測星- 的非相同詈访# :用偵測早7〇 之事實， 導致重疊分段使用不同_單元獲取 只，且由重疊分段產生之冗餘資料係用 擷取。在以下舌“ 小"取樣圖案 *建中’此可自動地導致抑制—重建影像中 又衫，例如所謂風車形假影。 右將心臟電腦斷層攝影資料後續用於所謂非閘控重建 I19525.doc 200800109 二、 ®田Η乍用可能變得明顯。此一非閘♦空重建可進 ::乂執行例如肺臟方面之診斷。在此情況下，需要高空間 :f 此一而解析度之達成’係可藉由將來自所有η個 -早7〇(其中η係配置在掃描單元中之偵測單元的數目） ^貧料交錯成為一資料集，其與個別資料集相比，在旋轉 由之方向中具有η倍更佳取樣，從而導致改進影像中 析度。 ，在下文中’將描述該掃描單元之進—步範例性具體實施 例然而，此等具體實施例亦應用於斷層攝影裝置及斷層 攝影方法。 依，騎描皁^的另_範例性具體實施例，在各對相鄰 债測早7〇之間提供一相等偏離。尤其係該偏離係可在相反 方向^。即，若將―列第—摘測單元界定為中心線，則鄰 近之第二偵測單元的對應列係藉由-既定偏離(例如一列 尺寸的一刀之_)來偏移，而鄰近之第三偵測單元的對 應列係猎由相同既定偏離相對於該列第一偵測單元偏移， ^係^相反方向中。較佳地，該默分數係—除以配置在 掃描單兀中之價測單元數目。其他偏移亦可 偏移不限於-除以整數，即不限於有理數。…㈣ 在鄰近積測單元之間之此-等距間隔可提供改進線積分 之取樣。 〜依據該掃描單元之另一範例性具體實施例，該掃描單元 係調適成繞-旋轉軸旋轉’且該偏離係在該旋轉轴之方 中。 119525.doc 200800109 該旋轉軸一般稱為z方向，因此其可謂個別偵測單元彼 此之偏移係在掃描單元的z方向中。然而，本發明不限於 在方向中偏私。亦可在另一方向中偏移個別積測元件。 例如，亦可藉由叫貞測元件之寬度的-分數在角方向（即 旋轉之圓形方向）中偏移該等债測元件。角方向中之此一 位移可導致一關聯一债測單元之輻射源單元可相對於铺測 元件而偏心之拿音 & 一 此一偏心亦可導致在180度旋轉後由 二偵」則早兀獲取之資料的交錯。即，由於該偏心，在 之的—早—㈣元件之資料’係與在18G度處取得 ==件的資料不相同。在z方向中之此一 向;可Γ:交錯(即圓形方向，即實質上垂仏方 了改進+面中之解析度。 依據該掃描單元夕s ^ 括一_射谓 兀之另一乾例性具體實施例，其進一步包 田，源，其中該輻射源包含複 地，輻射泝留_ 4 3後数個輻射源早兀。較佳 -射源早7L數目等於偵 係提供給各丨I _ 早凡數目，即一輻射源單元 偵，則早兀，其係彼此關聯。 依據該掃描軍元的另—範例性 數目係三。三初袖，，。D …、體只轭例，偵測單元的 及取得檢查中物件的②後 一了在知描早凡之簡單性 隨著偵測單元且’：所需要時間之間達到良好折衷。 掃描單元的複雜性。另― 的數目增加’可能增加 之掃描單元的-旋轉”二面：！為可在繞該檢查中物件 像的時間。 又夕貝科，故可減少取得一影 依據該掃描單元之另一範例 -、饈貝％例，該掃描單元 il9525.doc 200800109 係形成為-錐形射束掃纟元，^ ^ ^ ^ 物#的扣_ & > Tk供檢查中整體 曰不之^號方式調適該等彳貞測單元 體物件係由掃描罝分从^ Δ I ί双一甲之整 h 早的輻射源照明。因此掃描單元無須沿 該旋轉軸移動，以達到表 、 表不整體物件的H。此可簡化掃 田早兀、其係安裝之複雜性，因為無須沿z軸移動。 2下文中，將描述斷層攝影裝置之一進一步範例性具體 貝施例。然而’此具體實施例亦應用於掃描單元及斷層攝Good sampling. If the speed is too fast or use the so-called sampling) or the ▲ field one fork ",, point sampling (DFS - Jin Ming z direction focus sampling (zFS sampling) (that is, the focus position on the name Du Dui which radiation source this # 1 PCT In the case of the sampling method of the switching between the two, according to the exemplary embodiment, the use of a #星星-'s non-identical Suwa #: using the fact that the detection is early, causing overlapping segments to be used differently _ unit acquires only, and redundant data generated by overlapping segments is used for capture. In the following "small" "sampling pattern * built" this can automatically lead to suppression - reconstruction of the image in the shirt, such as the so-called windmill False shadow. Right, the heart computerized tomography data is used for the so-called non-gated control reconstruction. I19525.doc 200800109 2. The use of Η乍田Η乍 may become obvious. This non-stop ♦ empty reconstruction can enter: 乂 perform, for example, the lungs Diagnosis. In this case, a high space is required: f and the resolution can be achieved by taking all n - early 7 〇 (where the η is configured in the scanning unit) The poor materials are interlaced into a data set. Compared with the individual data sets, there are η times better sampling in the direction of rotation, resulting in improved resolution in the image. In the following, the exemplary embodiment of the scanning unit will be described. However, such The specific embodiment is also applied to a tomographic apparatus and a tomographic method. According to another exemplary embodiment of the raccoon soap, an equal deviation is provided between each pair of adjacent debts. The system can be in the opposite direction ^. That is, if the "column-extraction unit" is defined as the center line, the corresponding column of the adjacent second detection unit is determined by the -offset (for example, a column of a size) Offset, and the corresponding column of the adjacent third detecting unit is offset by the same predetermined deviation from the first detecting unit of the column, in the opposite direction. Preferably, the silent score is divided by The number of price units configured in the scanning unit. Other offsets may also be offset not limited to - divided by integers, that is, not limited to rational numbers. (4) This - equidistant interval between adjacent product units provides an improved line Sampling of points. In another exemplary embodiment of the scanning unit, the scanning unit is adapted to rotate about a rotation axis and the deviation is in the square of the rotation axis. 119525.doc 200800109 The rotation axis is generally referred to as the z direction, so It can be said that the individual detection units are offset from each other in the z direction of the scanning unit. However, the present invention is not limited to being biased in the direction. It is also possible to offset the individual integration elements in the other direction. For example, by calling The width-score of the width of the sensing element is offset in the angular direction (ie, the circular direction of rotation) of the debt measuring elements. This displacement in the angular direction may result in a radiation source unit associated with a debt measuring unit being relative to Placing components and eccentric sounds & eccentricity can also lead to the interleaving of data acquired by the second detective after 180 degrees of rotation. That is, due to the eccentricity, the data of the "early-(four) elements" is different from the data obtained by obtaining the == piece at 18G degrees. In the z direction, it can be: staggered (ie, circular direction, that is, substantially coveted, improved resolution + resolution in the face. According to the scan unit, s ^ 一 _ 射 兀 另一 another example Specific embodiments, which further include a field, wherein the radiation source comprises a complex land, and the radiation source is _ 4 3 after the plurality of radiation sources are early. Preferably, the number of the source is 7L earlier than the detection system provides each 丨I _ The number of early, that is, a radiation source unit, is early, and the system is associated with each other. According to the other example number of the scanning military unit is three. Three initial sleeves, , D ..., body yoke example, Detect The second and the second of the unit that has been inspected have achieved a good compromise between the detection unit and the time required to scan the unit. The complexity of the scanning unit. The number of others is increased. It is possible to increase the "rotation" of the scanning unit. The two sides of the scanning unit are the time when the object image can be wrapped around the inspection. In addition, the Beca, it is possible to reduce the other example of obtaining the image according to the scanning unit - and the example of the mussel , the scanning unit il9525.doc 200800109 is formed as a - cone beam broom , ^ ^ ^ ^ 物#的扣_ &> Tk for inspection in the overall 曰 之 ^ ^ 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 调 ^ ^ Early radiation source illumination. Therefore, the scanning unit does not need to move along the rotating axis to achieve the H of the table and the integral object. This simplifies the complexity of the installation and the installation of the system because it does not need to move along the z axis. In the following, a further exemplary embodiment of a tomographic apparatus will be described. However, this embodiment is also applied to a scanning unit and a tomography.
影方法。 依據另一乾例性具體實施例，該斷層攝影裝置進一步包 括重建單7L，其中該重建單元係調適用以重建一表示檢 查中朴物件之影像，該影像係來自侧單元提供之信號。 可藉由一電腦程式(即藉由軟體)，或藉由使用一或多個 特殊電子最佳化電路（即在硬體中），或以混合形式（即藉由 軟體組件及硬體組件)來實現受關注之物件的檢查⑼如藉 由依據本發明之掃描單元及/或斷層m影裝置取得的心臟 電：：層攝影資料之分析及重建)，。可用任何適合程式 化語言（諸如c++)來撰寫電腦程式，1電腦程式可儲存於 電腦可讀取媒體中，諸如CD-ROM。同時，該電腦程式係 可從網路取得，例如全球資訊網（w〇rldWideWeb)，可自其 將該程式下載入影像處理單元或處理器，或任何適合電腦 中。 亦應/主思到在此上下文中，本發明係不限於電腦斷層攝 影，而疋可包括以c臂為基礎之三維旋轉X射線成像、磁 共振成像、正電子發射斷層攝影以及類似者。亦應注意到 119525.doc -12 - 200800109 本：明：：用，如碎斷病人心臟或肺臟之醫療成像。 本 乾例性具體實施例的主旨係，一種用於 腦斷層攝影裝置之掃描單元用於一電 元及偵測單元，即呈有配置=一維之硬數個輕射源單 =射源早兀之較佳數目可為三。置放不同價測單 兀，因此可交錯其取樣圖案制早 體實施例中，一福測單元可之具 〇 〜 置於中心’而其他二者可分别 耩由一像素咼度的三分之一 在冰ζ細之-古一 上下偏和。即’一偵測單元係 : 移’且其他偵測單元係在沿Ζ軸之相 反方向中偏移。若重疊之分段係使用不同伯 取，則可用不同取樣圖案來擷取此等冗餘資料。在又 = 地導致抑制假影’如所謂風車形假影。若 將〜_料後績用於非間控重建時，一正面副作 變得明顯。此通常係進行以執行肺臟方面之診斷。在此重 建中，需要高空間解析度。在此情況下，來自所有 測器單元则器)之資料可交錯成為一資料集，其：個別 貧料集相比，係在ζ方向中具有三倍更佳取樣，從而導致 改進影像之Ζ解析唐。_古明、立二丄M t 肿符度有關平面中解析度之類似優點可 糟由在其他方向中偏移偵測器達一像素寬度之三分之一來 達到’即-债測元件之寬度的三分之一’或若使用雙焦點 取樣獲取時之像素寬度的六分之一。在此上下文中，術語 其他方向⑤指沿該等列偵測元件，即實質上垂直於Z方 向。當使用在掃描單元之旋轉方向中的雙焦點取樣⑽8取 樣），或使用在實質上垂直於此方向⑽z方向）之方向中的z 119525.doc -13· 200800109 依據-範命m具體實施例該 ，將可明白並闡明本發明之 方向焦點取樣（zFS取樣）時， 掃描單元可能尤其具有優點。 參考以下說明之具體實施例 此等及其他態樣。 【實施方式】 一範例性具體實 明之一具體實施 圖1顯示一電腦斷層攝影掃描器系統之Shadow method. According to another exemplary embodiment, the tomographic apparatus further includes a reconstruction unit 7L, wherein the reconstruction unit is adapted to reconstruct an image representative of the object in the inspection, the image being from a signal provided by the side unit. Can be by a computer program (ie by software), or by using one or more special electronic optimization circuits (ie in hardware), or in a mixed form (ie by software components and hardware components) To perform inspection of the object of interest (9), such as analysis and reconstruction of cardiac electricity: layer photographic data obtained by the scanning unit and/or the tomographic apparatus according to the present invention. The computer program can be written in any suitable programming language (such as c++), and the computer program can be stored in a computer readable medium such as a CD-ROM. At the same time, the computer program can be obtained from the Internet, such as the World Wide Web (w〇rldWideWeb), from which the program can be downloaded into the image processing unit or processor, or any suitable computer. It should also be appreciated that in this context, the invention is not limited to computed tomography, and may include three-dimensional rotational X-ray imaging, magnetic resonance imaging, positron emission tomography, and the like, based on c-arm. It should also be noted that 119525.doc -12 - 200800109 Ben: Ming:: Medical imaging such as breaking the heart or lungs of a patient. The main purpose of the present embodiment is that a scanning unit for a brain tomography apparatus is used for a cell and a detecting unit, that is, a hard light source with a configuration = one dimension; The preferred number of 兀 can be three. Different price measurement orders are placed, so that the sample pattern can be interleaved in the early embodiment. One unit can be placed at the center and the other two can be separated by a pixel. One is in the hail and fine - the ancient one is up and down. That is, 'one detection unit is: shift' and the other detection units are offset in opposite directions along the x-axis. If the overlapping segments use different logs, different sampling patterns can be used to capture the redundant data. In addition, the ground causes the suppression of artifacts, such as the so-called windmill-shaped artifacts. If the ~_ material is used for non-intermediate reconstruction, a positive side effect becomes apparent. This is usually done to perform a diagnosis of the lungs. In this rebuild, high spatial resolution is required. In this case, the data from all the detector units can be interleaved into a data set, which has three times better sampling in the ζ direction than the individual poor material set, resulting in improved image resolution. Tang. _古明,立二丄 M t Swollenness is similar to the resolution in the plane. It can be worse by offsetting the detector to one-third of the width of one pixel in other directions to achieve the 'net-debt component. One-third of the width' or one-sixth of the pixel width when double-focus sampling is used. In this context, the term other direction 5 refers to detecting elements along the columns, i.e., substantially perpendicular to the Z direction. When using the bifocal sampling (10) 8 sampling in the direction of rotation of the scanning unit, or using z 119525.doc -13· 200800109 in the direction substantially perpendicular to the direction (10) z direction), according to the specific embodiment The scanning unit may be particularly advantageous when it is possible to understand and clarify the directional focus sampling (zFS sampling) of the present invention. Reference is made to the specific embodiments described below. [Embodiment] One exemplary embodiment is embodied in a computer tomography scanner system.
施例的簡化示意圖，其中可使用依據本發 例的掃描單元。 丨心〜电胸研席躡影裝置100係一錐形射束C^f 描器。然而’本發明亦可使用一扇型射束幾何形狀來實 現。圖W所述的CT掃描器包含一高架101，其係可繞一旋 轉軸102旋轉。高架101係藉由一馬達1〇3驅動。參考數字 105指諸如一Χ射線源之一輻射源，其發射多色或單色輻 射。 參考數字106指一形成從輻射源單元發射成一錐形輻射 • 束1〇7之輻射束的孔徑系統。錐形射束107被導引使得其穿 過配置在高架101中心（即在CT掃描器的檢查區内）的受關 注物件110，且撞擊在偵測器（偵測單元）115上❶如可自圖i 取付，偵測器115係配置在高架lOil與輻射源單元1〇5相 對，使得偵測器115之表面係由錐形射束1〇7覆蓋。在圖i 中描述之偵測器115包含複數個偵測元件115a，其各可偵 測之X射線已藉由該受關注物件110散射或衰減’或穿過該 文關注物件11 ο β圖1中概要地顯示之偵測器i i 5係二維偵 測為’即個別债測器元件配置在一平面中。此等偏測器係 119525.doc -14- 200800109 用於所謂錐形射束斷層攝影。為了清楚原因，僅一輻射源 單元及一偵測單元顯示於圖丨中。依據本發明之範例性具 體只細例，至少—個摘測單元及—對應數目之輻射源草元 係配置在冋条1 0 1上。較佳地係使用三個偵測單元及三個 輻射源單元’但取決於需要，可使用任何適合數目的單 元，例如θ、五或六。隨著單元數目增加，在該高架的單 方疋轉中將可取樣更多資料，而另—方面該系統變得越來 越複雜It等债測單元及輻射源單元係等距土也置於高架 101上，即在三個偵測單元之情況下，該等單元係置於每 一 120度處。 在掃描受關注物件110期間，輻射源單元105、孔徑系統 106及偵測115係在由箭頭117所指之方向中沿高架⑻旋 轉。為了高架1G1連同輻射源單元1()5、孔徑系統1〇6及债 測„。115之叙轉，馬達1()3係連接至—馬達控制單元12〇， 其係連接至一控制單开〗9 ς 1 ^ 早π 125(其亦可指計鼻、重建或決定單 元）。 二在圖1中’叉關注物件110係一人類，其被置於在一操作 在掃描人11〇之頭部11〇a或心臟期間，在高架 101繞著人110旋轉之同時，操作台112可沿平行於高架101 之旋轉軸⑽的方向位移該人110。此位移可藉由一馬達 113進行。藉由此，、％ 係化一螺碇知描路徑來掃 s ^ ’該㈣台m亦可停止’以從而使用所 謂軸或圓形掃描來測量資 所有描述情況中n 思、，較佳地係在 仃圓形掃描，其中在平行於旋轉軸 119525.doc -15- 102 200800109 之方向中沒有位移，而僅有高架1 〇 !繞旋轉軸i 〇2之旋轉。 視需要，可提供一心電圖器件，其測量人類11〇心臟的 心電圖，而X射線由於通過心臟而衰減且藉由偵測器115偵 測到。與所測量心電圖有關之資料被發送至控制單元 125 〇 偵測器115係連接至控制單元125。控制單元125接收偵 測結果（即來自偵測器115之偵測元件115a的讀出），且基於 φ 此等讀出來決定掃描結果。再者，控制單元125與馬達控 制單元120通信，以使用馬達1〇3及113，協調高架ι〇ι與操 作台112的運動。 控制單元125可調適成用以重建一來自偵測器115之讀出 的影像。由控制單元125產生之一重建影像亦可經由一介 面輸出至顯示器（未顯示於圖lf )。 控制單元125可藉由一資料處理器實現，以處理來自偵 測器115之偵測器元件115&的讀出。 、 φ 在圖1中顯示之電腦斷層攝影裝置可擷取心臟之多循環 :臟電腦斷層攝影資料。換句話說，當高架1G1旋轉且當 知作台112線性偏移時，則一螺旋掃描係藉由χ射線源如 及债測器115針對心臟來執行。在此螺旋掃描期間，心臟 可跳動複數次且可涵蓋多個RR循環。在此等跳動期間， ，取複，個心臟電腦斷層攝影資料。同時，可藉由心電圖 單兀測m〜電圖。在已獲取此等資料以後，資料被傳送 至控制單元125，且可回溯地分析經測量資料。 測里資料（即心臟電腦斷層攝影資料及心電圖資料） 119525.doc -16- 200800109 係由控制單元125處理’其可經由—圖 園办使用者介面（GUI) 進一步予以控制。然而，應注意本發明 +七明不限於此特定資料 獲取及重建。 ' 圖2概要顯示依據一範例性具體實施例之掃描單元的示 意圖，即不同偵測單元的相對置放。 掃描單元20G包含三個輻射源單元，其係示意性地描述 為點201、202、203。該等輕射源單元係圓形地置放在一 高架（其未顯示於圖2中）上。在圖2中，輻射源單元旋轉的 ，徑係由黑線2G7概要地_示…偵測單元係與各輕射源 單元相對地配置，即一第一福制留— 弟偵測早兀204與第一輻射源單 .元20 1相對地配置，一篦一掐、、目^话—aλ 弟一偵測早兀2〇5與第二輻射源單元 202相對地配置，且一篦二掐、、目丨丨结—w 置且弟一偵測早70206與第三輻射源單元 2 0 3相對地配置。各摘測置开白入 1貝成I早το包合一些以矩陣形式配置之 摘測元件’即各债測單元待_維自 一 干凡货、一維偵測早兀。八列208、 209、210、211 ' 212、η Λ Λ ^ 213、214、和21 5及24行的一矩陣 係概要地顯示，但可你用/ / ώ人 便用任何適合數目的列及行。依據範 例性具體實施例，第一禎、、丨s - 乐偵測早凡204係相對於在2方向中置 於中心’其係在圖2中葬士並55。1 > - 甲稭由則碩216|曰示，即黑線2〇7在列 210及211之間通過。第二制單元2〇5係相對於第一偵測 單元2〇4向下偏移-像素高度的三分之-，而第三偵測單 元206係相對於第一偵：| 、’、〗單兀204向上偏移一像素高度的三 七等偏私係藉由將黑線2〇7相對於該等列偵測 件置放而概要地顯示。 依據本發明，亦可供+ 了此在二維偵測器單元之其他方向偏移 119525.doc -17- 200800109 4貞測裔早元，即膏曾μ午士 、 貝上垂直於Ζ方向。較佳地，此偏移亦 ' 單兀的數目’即在所示的範例性具體實施例 :’其較佳地亦係-像素寬度的三分之―，絲使用所謂 ^焦絲樣時之-像素寬度的六分之…此—偏移意即由 輻射源早凡(如第二輻射源2〇2)之中心點，及旋轉中心(即 圓周黑線207之中心點、所反…从 … τ所界疋的-線，其不與第二偵測器 05之二維平面的中心相交’而是在偏移-像素寬度 的:分之—（在则取樣之情況下為六分卜）之―點處與 此平：相交。此將導致所謂的藉由個別偵測單元取得之資 枓的父錯’因為當高架係在〇度處時取得之資料⑽積分）， 將不會與當高架在⑽度處時取得的資料（線積分）匹配。將 會有導致改進平面中解析度之資料的小失配(交錯)。 —總之，將-電腦斷層攝影裝置之掃描單元的二維该測單 兀以使其在彼此相對之z方向中顯現—預定失配之方式來 配^於掃描單元中’可視為本發明之—態樣。此失配可導 致伙-檢查中物件取得之資料的交錯，其可導致改進自檢 查中物件取得之影像的的重建品質。 双 應注意的係術語"包含，，不排除其他元件或步驟，且"―" 或一個，，不排除複數個。同樣地，關聯不同具體實施奸 述之凡件可加以組合。亦應注意到請求項中之： 應被視為限制請求項的範嘴。 、 【圖式簡單說明】 本發明之-範例性具體實施例已參考以下圖式描述於 119525.doc -18 - 200800109 測單元的相 圖2顯示依據一範例性具體實施例之不同偵 對置放的示意圖。 類似或相同元 圖式中的描述係示意性。在不同圖式中 件具有類似或相同參考符號。 【主要元件符號說明】A simplified schematic of an embodiment in which a scanning unit in accordance with the present invention can be used.丨心~Electric chest study 蹑影装置100 is a cone beam C^f scanner. However, the invention can also be implemented using a fan beam geometry. The CT scanner of Figure W includes an overhead 101 that is rotatable about a rotating shaft 102. The overhead 101 is driven by a motor 1〇3. Reference numeral 105 refers to a radiation source such as a source of radiation that emits multi-color or monochromatic radiation. Reference numeral 106 refers to an aperture system that forms a radiation beam that is emitted from a radiation source unit into a cone of radiation • beam 1〇7. The cone beam 107 is guided such that it passes through the object of interest 110 disposed at the center of the elevated 101 (i.e., within the examination zone of the CT scanner) and impinges upon the detector (detection unit) 115. The detector 115 is disposed on the overhead lOil opposite to the radiation source unit 1〇5 such that the surface of the detector 115 is covered by the cone beam 1〇7. The detector 115 described in FIG. i includes a plurality of detecting elements 115a whose respective detectable X-rays have been scattered or attenuated by the object of interest 110 or passed through the article of interest 11 θ β FIG. The detector ii 5 is schematically displayed in two dimensions as "the individual debt detector elements are arranged in a plane. These detectors are used in the so-called cone beam tomography 119525.doc -14- 200800109. For the sake of clarity, only one radiation source unit and one detection unit are shown in the figure. According to an exemplary embodiment of the present invention, at least one of the extracting units and the corresponding number of radiating source grasses are disposed on the stringer 101. Preferably, three detection units and three radiation source units are used' but any suitable number of units may be used, such as θ, five or six, depending on the need. As the number of units increases, more data can be sampled in the elevated unilateral twirling, and on the other hand, the system becomes more and more complicated. It is also placed on the elevated scale of the debt measuring unit and the radiation source unit. At 101, in the case of three detection units, the units are placed at every 120 degrees. During scanning of the object of interest 110, the radiation source unit 105, aperture system 106, and detection 115 are rotated along the overhead (8) in the direction indicated by arrow 117. For the overhead 1G1 together with the radiation source unit 1() 5, the aperture system 1〇6 and the debt measurement „115, the motor 1() 3 is connected to the motor control unit 12〇, which is connected to a control single open 〖9 ς 1 ^ early π 125 (which can also refer to the nose, reconstruction or decision unit). In Figure 1, the 'fork object 110 is a human, which is placed in an operation at the head of the scanner 11 During the portion 11A or the heart, while the overhead 101 is rotated about the person 110, the console 112 can displace the person 110 in a direction parallel to the axis of rotation (10) of the elevated frame 101. This displacement can be performed by a motor 113. Thus, the % systemizes a threaded path to sweep s ^ 'the (four) table m can also be stopped 'to use the so-called axis or circular scan to measure all the descriptions, preferably In a circular scan, there is no displacement in the direction parallel to the axis of rotation 119525.doc -15- 102 200800109, but only the elevation 1 〇! rotation around the axis of rotation i 〇 2. If desired, an electrocardiogram device can be provided , which measures the electrocardiogram of the human heart, while the X-rays are attenuated and borrowed by the heart. Detected by the detector 115. The data related to the measured electrocardiogram is sent to the control unit 125. The detector 115 is connected to the control unit 125. The control unit 125 receives the detection result (ie, from the detector 115) The reading of the component 115a is performed, and the scanning result is determined based on the reading of φ. Further, the control unit 125 communicates with the motor control unit 120 to coordinate the overhead ι and the console 112 using the motors 1〇3 and 113. The control unit 125 is adapted to reconstruct an image read from the detector 115. The reconstructed image generated by the control unit 125 can also be output to the display via an interface (not shown in Figure lf). The unit 125 can be implemented by a data processor to process the readout of the detector elements 115& from the detector 115. φ The computed tomography apparatus shown in Fig. 1 can capture multiple cycles of the heart: dirty Computerized tomography data. In other words, when the overhead 1G1 is rotated and when the station 112 is linearly offset, then a helical scan is performed by the xenon source such as the debt detector 115 for the heart. During this period, the heart can be beaten multiple times and can cover multiple RR cycles. During these beatings, the heart computer tomography data is retrieved. At the same time, the m-electrogram can be measured by the electrocardiogram. After the data is transmitted, the data is transmitted to the control unit 125, and the measured data can be analyzed retrospectively. The measured data (ie, cardiac computed tomography data and electrocardiogram data) 119525.doc -16- 200800109 is processed by the control unit 125 It can be further controlled via the User Interface (GUI). However, it should be noted that the present invention is not limited to this particular data acquisition and reconstruction. Figure 2 is a schematic illustration of the scanning unit in accordance with an exemplary embodiment, i.e., the relative placement of different detection units. Scan unit 20G contains three radiation source units, which are schematically depicted as points 201, 202, 203. The light source units are placed circularly on an overhead frame (which is not shown in Figure 2). In FIG. 2, the radiation source unit is rotated, and the diameter is determined by the black line 2G7. The detection unit is disposed opposite to each of the light source units, that is, a first welfare system is detected. The first radiation source is disposed opposite to the first radiation source unit. The first radiation source unit is disposed opposite to the second radiation source unit 202, and the first radiation source unit 202 is disposed opposite to the second radiation source unit 202. And the target is configured to be opposite to the third radiation source unit 203. Each of the surveys is opened to the white. 1B is formed into an early τ. Some of the components are arranged in a matrix form, that is, each of the debt measurement units is _dimensionally self-contained and one-dimensionally detected. A matrix of eight columns 208, 209, 210, 211 '212, η Λ Λ ^ 213, 214, and 21 5 and 24 rows is shown schematically, but you can use any suitable number of columns with / / ώ Row. According to an exemplary embodiment, the first 祯, 丨 s - 乐 早 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 204 Then the 216| indicates that the black line 2〇7 passes between the columns 210 and 211. The second unit 2〇5 is offset downward relative to the first detecting unit 2〇4 by a three-point height of the pixel, and the third detecting unit 206 is relative to the first detecting: |, ', 〗 The singularity of the single-strip 204, which is shifted upward by one pixel height, is displayed roughly by placing the black line 2〇7 with respect to the column-detecting members. According to the present invention, it is also possible to offset the other direction of the two-dimensional detector unit by 119525.doc -17- 200800109 4 贞 裔 早 , , , , , , , , , , , , , , , 。 。 。 。 。 。 。 。 。 。 。 。 。 。 Preferably, the offset is also the number of 'single turns', that is, in the exemplary embodiment shown: 'it is preferably also - three-thirds of the width of the pixel", when the wire is used - the sixth of the pixel width... This offset means the center point of the radiation source (such as the second radiation source 2〇2), and the center of rotation (i.e., the center point of the circumferential black line 207, the inverse... ... the line of τ bounds, which does not intersect the center of the two-dimensional plane of the second detector 05' but at the offset-pixel width: the division - (in the case of sampling, it is six points) ) - the point is equal to this: intersect. This will result in the so-called father's fault of the resource obtained by the individual detection unit 'because the information obtained when the elevated system is at the temperature (10) points) will not be The data (line integral) obtained when the elevated position is at (10) degrees matches. There will be a small mismatch (interlace) that leads to improved resolution in the plane. - In summary, the two-dimensional measurement of the scanning unit of the computed tomography apparatus is such that it appears in the z-direction relative to each other - a predetermined mismatch in the scanning unit is considered to be the invention - Aspect. This mismatch can lead to a staggering of the information obtained by the object-inspection, which can result in improved reconstruction quality of the image obtained from the object in the self-examination. Doubles should be noted that the term "includes, does not exclude other components or steps, and "" or one, does not exclude plural. Similarly, the pieces associated with different specific practices can be combined. It should also be noted that in the request: it should be considered as a limit for the request. BRIEF DESCRIPTION OF THE DRAWINGS Exemplary embodiments of the present invention have been described with reference to the following figures at 119525.doc -18 - 200800109. Phase 2 of the measurement unit shows different detection placements according to an exemplary embodiment. Schematic diagram. The descriptions in the similar or identical elements are schematic. The parts have similar or identical reference symbols in different drawings. [Main component symbol description]
100 電腦斷層攝影裝置 101 高架 102 旋轉軸 103 馬達 105 輻射源單元 106 孔徑系統 107 錐形輻射束/錐形身 110 受關注物件/人 110a 人之頭部 112 操作台 113 馬達 115 偵測器 115a 偵測元件 120 馬達控制單元 125 控制單元 200 掃描單元 201 輻射源單元 119525.doc -19- 200800109 202 輻射源單元/第 203 輻射源單元 204 第一偵測單元 205 第二偵測單元 206 第三偵測單元 207 黑線 208 列 209 列 210 列 211 列 212 列 213 列 214 列 215 列 119525.doc -20-100 computer tomography apparatus 101 overhead 102 rotating shaft 103 motor 105 radiation source unit 106 aperture system 107 cone beam / cone 110 subject matter / person 110a person's head 112 console 113 motor 115 detector 115a Measuring element 120 motor control unit 125 control unit 200 scanning unit 201 radiation source unit 119525.doc -19- 200800109 202 radiation source unit / 203 radiation source unit 204 first detection unit 205 second detection unit 206 third detection Unit 207 Black Line 208 Column 209 Column 210 Column 211 Column 212 Column 213 Column 214 Column 215 Column 119525.doc -20-