EP1624805A1 - Production d'images de tomographie par ordinateur par reconstruction spiralee d'un objet d'analyse qui effectue un mouvement partiellement cyclique - Google Patents

Production d'images de tomographie par ordinateur par reconstruction spiralee d'un objet d'analyse qui effectue un mouvement partiellement cyclique

Info

Publication number
EP1624805A1
EP1624805A1 EP04739105A EP04739105A EP1624805A1 EP 1624805 A1 EP1624805 A1 EP 1624805A1 EP 04739105 A EP04739105 A EP 04739105A EP 04739105 A EP04739105 A EP 04739105A EP 1624805 A1 EP1624805 A1 EP 1624805A1
Authority
EP
European Patent Office
Prior art keywords
area
scan
moving
feed rate
movement
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP04739105A
Other languages
German (de)
English (en)
Inventor
Herbert Bruder
Thomas Flohr
Matthias Niethammer
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Siemens AG
Original Assignee
Siemens AG
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Siemens AG filed Critical Siemens AG
Publication of EP1624805A1 publication Critical patent/EP1624805A1/fr
Withdrawn legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/027—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis characterised by the use of a particular data acquisition trajectory, e.g. helical or spiral
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/4064—Arrangements for generating radiation specially adapted for radiation diagnosis specially adapted for producing a particular type of beam
    • A61B6/4085—Cone-beams

Definitions

  • the invention relates to a method and a computed tomography device (CT device) for generating CT images by spiral reconstruction of a partially cyclically moving examination object, preferably of a patient, the examination object being carried out in one pass by a spiral movement of at least one focus and at least one opposite detector is scanned, the scanning of the examination area takes place with a relative feed speed between gantry and couch, and a spatial image of the absorption coefficients is determined with a plurality of intersection planes of an examination volume on the basis of the data obtained by the scanning.
  • CT device computed tomography device
  • a similar method and a similar CT device are known for example from the published patent application DE 198 42 238 A2.
  • This document discloses a recording method for a periodically moving object, in particular a beating heart of a patient, with a movement and a resting phase by means of a CT device with a gantry rotating in a spiral around the examination object with a focus and a multi-cell detector, whereby for a complete Run or scan the feed rate of the patient bed and the speed of the gantry are coordinated with one another in such a way that sufficient image information for the best possible reconstruction can be collected during the resting phase of the periodically moving object.
  • the movement or rest phases can be determined by a connected ECG. There is no provision for changing the feed speed during the scan.
  • the disadvantage of this invention is that a relatively low feed rate is necessary and, as a result, a high dose load during the admission must be accepted.
  • Image planes is moved, while the feed rate is increased with increasing distance from the nearest image plane. This results in an almost sinusoidal course of the feed speed over the entire scanning path regardless of the movement situation of the scanned area.
  • the disadvantage of such methods is the poor recording quality due to the motion blur in the area of the moving part of the recording object, for example the heart of a patient.
  • the invention is therefore based on the object of finding a method for generating CT images of an at least partially cyclically moving examination object, and a CT device for carrying out this method, which on the one hand enables cyclically moving areas with high
  • the inventors have recognized that this object can be achieved in that different feed speeds are used during a scan run, depending on whether an area with strong movement changes or a largely static area is being scanned.
  • a known reconstruction method from cardio-CT with a relatively low feed rate can be used when scanning the moving area and the normal reconstruction method with high feed rate can be used when scanning largely static areas.
  • the normal reconstruction method with high feed rate can be used when scanning largely static areas.
  • the feed rate is understood to mean the relative speed between the CT device and the examination object, usually a patient on a mobile couch.
  • the aforementioned cyclical movement does not relate to the movement of the entire examination object, but rather to the cyclical movement of a partial area relative to the entire examination object, such as, for example, the movement of the heart and possibly surrounding areas due to the movement of the heart.
  • the inventors now propose to improve the known method for generating CT images of a partially cyclically moving examination object, preferably of a patient, in the known method with one pass the examination object by a spiral movement is scanned by at least one focus and at least one opposite detector, the scanning of the examination area takes place with a relative feed speed v t between the gantry and the couch, and a spatial image of the absorption coefficients is determined on the basis of the data obtained by the scanning with a large number of sectional planes of an examination volume ,
  • the inventive with respect to the examination object (P), at least one static object region and at least one moving object region with cyclic self-movement are determined and, during a passage of the scanning of the examination object (P) in the at least one moving object region, a first feed speed (vi ) and in the at least one static object area a different, second feed rate (v 2 ) is used.
  • the examination object can be divided into moving and unmoving areas before the scan, so that the feed rate is adapted during the passage according to the area scanned in each case.
  • a high feed rate is selected for the stationary or static sub-areas of the examination object and a low feed rate in the moving area.
  • the methods known per se for picking up cyclically moving objects, preferably with rest and movement phases, can then be used.
  • the scan itself can be used to detect whether there is movement in the current scanning area or not. It is thus determined during the scan whether the currently scanned area is a moving sub-area or a static sub-area of the object, and the feed rate is regulated "online", as it were, depending on the movement situation of the scanned area.
  • the first variant which requires a preview to determine the differently treated subareas
  • it thus becomes automatic or semi-automatic during the scan run switched between a normal CT scan, in which all the determined detector data are used for the reconstruction, and a cardio CT scan, in which only detector data from certain phase sections of a cyclical movement are used for the reconstruction.
  • the semi-automatic switchover for example, the operating personnel can be informed of the necessary speed change by a corresponding signal and can make this change manually.
  • a reconstruction method can be used, as described in the published patent application DE 101 27 269 AI, when switching to the area with cyclical movement, the corresponding cardio method according to the published patent application DE 102 07 623 AI can be switched ,
  • the method according to the invention is not limited to the reconstruction methods specified here, but can be used in all known spiral reconstruction methods.
  • the inventors propose that a higher feed speed v 2 is used to scan a static object area and a lower feed speed Vi is used to scan a moving object area.
  • the position of the beating heart can be determined for dividing the examination object into static and moving object areas, predetermined ones also
  • Border areas which are also stimulated to move by the beating heart, can be included in the defined moving area.
  • Such a determination of static and moving object areas before the scan can be carried out, for example, by at least one topogram recording, sometimes also called a scout scan.
  • the examination object is moved in the longitudinal direction relative to the gantry with a non-rotating focus and detector, and a transparent image is obtained.
  • static and moving object areas can also be determined before the scan by at least one optical recording.
  • a particularly advantageous embodiment of the method according to the invention provides that the transition between the feed speeds takes place with a predetermined maximum acceleration. This avoids the fact that the object under examination, particularly if it is a patient, is stimulated by the process of excessive acceleration as a whole to movements which have a disruptive effect. If such an influence on the patient is to be completely avoided, a movable gantry can be used for patients standing still in the room, contrary to the otherwise customary design of CT devices for the relative movement from gantry to patient. In such a case, the patient or the examination object is not influenced by the change in the feed speeds.
  • the inventors also propose that moving and static object areas be determined during the scan and that a low feed rate (i) is selected when a cyclical movement is detected and a higher feed rate (v 2 ) is selected when a static state is detected.
  • the detection of the movement of the examination object in the current scan area and preferably during the scan is carried out by the intensity measurement of at least one pair of beams on a common beam axis, preferably two beams running in opposite directions, in relation to one another following times is compared.
  • the total absorption of the same beam path by the examination object is measured several times at different times in a multi-line spiral CT and that changes in the absorption measurement can be used to infer a change - i.e. a movement - within the beam path.
  • this basically known detection method of moving and stationary areas reference is made, for example, to published patent application DE 100 64 785 AI (priority application from US 472,560).
  • the movement of the heart can be temporally resolved by EKG leads and divided into movement phases and rest phases, only detected data from the rest phase being used for image generation.
  • a “gated” recording method preferably cardio recording method
  • a CT spiral reconstruction method that only uses detector data from a predetermined cycle phase of the cyclically moved region can also be used for cleaning the moving area, while a spiral reconstruction method that uses all measured detector data for reconstruction is used for scanning the static region.
  • the radiation intensity which emanates from the at least one focus, is adapted to the current feed rate v t .
  • this can be done by controlling the tube current in the X-ray tube.
  • the inventors also propose the improvement of a CT device which is used to scan an at least partially cyclically moving examination object, preferably a patient, and with a beam of rays emanating from at least one focus and with at least one flat array of detectors is equipped with a large number of distributed detector elements for detecting the rays of the beam, the at least one focus being moved relative to the examination object on a spiral focus path encircling the examination object at a feed rate v.
  • the improvement lies in the fact that at least means are provided for carrying out the method described above, the means mentioned being able to be implemented at least in part by programs or program modules.
  • the CT device can have a device for controlling the feed speed v as a function of the state of motion and / or the scanning area.
  • FIG. 1 Schematic representation of a spiral CT
  • FIG. 2 Schematic representation of a spiral recording
  • Fig. 3 topogram with boundaries of the moving and stationary zones
  • Fig. 4 feed curve along the z-axis
  • Fig. 5 feed curve along the z-axis with acceleration limitation
  • FFiigg .. 66 Topogram with moving, stationary and transition zones
  • Fig. 7 Schematic representation of motion detection using parallel beams and their complementary return beams.
  • FIG. 1 shows a schematic illustration of a spiral CT with a focus 1 rotating about a center M, which emits a conical X-ray beam 3 for scanning a patient P.
  • This cone-shaped beam 3 is captured on the side opposite the focus by a multi-line detector 2 arranged in a ring over 360 ° and measured with regard to its intensity, so that a spatial image of the patient with respect to his absorption coefficient is known in a manner known per se and often described. efficient can be represented.
  • a computing system 4 which has an output unit 5 and an input unit 6 and in which control and evaluation programs Prg n run, is used to evaluate the measured raw data.
  • the basic methods for evaluating the measured raw data are generally known. As an example, reference is made to the publication by Willi A., computed tomography, ISBN 3-89578-082-0, described above. For the rest, a wide range of patent literature is available on these evaluation methods.
  • CT refers, but also to single or multi-cell detectors that rotate with the focus. It can also be used with CT devices that have multiple fokens and multiple detectors. It is essential, however, that when measuring the raw data the focus moves on a spiral path, as shown in FIG. 2, relative to the patient. This spiral path can be achieved on the one hand by advancing the patient in the z direction while simultaneously rotating the focus on a circular path. On the other hand, there is also the possibility to fix the patient in the room and only focus around the patient rotating on a spiral path. In this case, either a detector can also rotate or, in the case of a stationary, circularly arranged detector, it can only be moved linearly in the z direction. The distance between two spiral points of the same angle is referred to as the feed V.
  • a relative movement of the patient in the z direction is carried out, so that a so-called topogram of the patient can be recorded, which Basically corresponds to a transmitted light X-ray of the patient perpendicular to the z direction.
  • a so-called topogram of the patient corresponds to a transmitted light X-ray of the patient perpendicular to the z direction.
  • no X-ray film is exposed, but the intensity values of the detectors lying opposite the focus are processed as a function of the moving path.
  • Such a topogram T is shown in FIG. 3. It shows the transmitted light image of patient P in the thorax and upper abdominal area.
  • the area of the topogram can now be marked on the basis of this recording, manually or by an automatic image recognition method, in the area with a motion blur of the beating heart is to be reckoned with.
  • two limits I and II are shown in the present FIG. 3, the two limits I and II respectively characterizing the upper and lower end of the heart.
  • the inventors in the particular embodiment described here propose to move with two different feed speeds v x and v 2 in a single pass or scan over the entire topogram shown in FIG. 3, during the single one A normal spiral during the run with the low feed speed
  • a scan is carried out, in which all measured detector data are used for reconstruction, and in the section with low feed speed, a typical gated spiral reconstruction is carried out, in which only data from specific cycle areas of the cycle periods of the cyclically moved
  • Part of the examination object for example from the resting phases of a heart and / or the neighboring areas and organs, can be used for reconstruction.
  • FIG. 4 A schematic representation of these different feed speeds over the entire scan area is shown in FIG. 4, which corresponds in its spatial arrangement to the topogram T of FIG. 3 lying above it.
  • FIG. 4 shows in a first area a high feed speed v 2 , which is coupled at the same time with a standard scanning method of a CT which corresponds to a spiral scan of a non-moving object in which the smallest possible redundancies should occur during the measurement.
  • a typical cardio evaluation being used here for the evaluation of the scanned data, with care being taken, for example, with the aid of EKG measurements is that only rays are used for image evaluation that are measured during the resting phase of the heart, while rays are rejected at the time of a movement phase or at least weighted less.
  • FIG. 5 shows such a method with a maximum acceleration, which can be found in the slope of the curve of the feed speeds, between the feed speed vi and v 2 .
  • a maximum acceleration which can be found in the slope of the curve of the feed speeds, between the feed speed vi and v 2 .
  • an intermediate range ⁇ is introduced, in which the transition between the two feed speeds v x and v 2 is carried out under controlled positive or negative acceleration.
  • the inventors propose a further special embodiment of the method according to the invention.
  • this method it is fundamentally not necessary to create a topogram to distinguish between moving and stationary scan areas.
  • a topogram T is shown in FIG. 6, on the basis of which the particular embodiment of the inventive method is to be explained.
  • the topogram from FIG. 6 shows a superimposition of a schematically represented heart with a hatched border area G surrounding this heart.
  • This border area G is intended to define the area surrounding the heart, which is also caused to move due to the heartbeats. These are essentially areas of the lungs and the underlying diaphragm with parts of the adjacent organs. If a scan of the patient is now carried out, this scan begins at a high feed rate, whereby from a 180 ° rotation of the focus around the patient there are always individual beams with a conical beam path, which are in an identical path, but with a time delay in the tissue penetrate.
  • the measured absorption values for two time-delayed beams are compared with an identical path, it can be determined on the basis of the absorption behavior whether there has been any movement in the area of these beams, since such a movement leads to an change in the measured intensity as a function of time. In this way, it can be detected, for example, whether the currently scanned area is subject to a momentary movement or is in a resting phase.
  • this method can be determined during the scanning of the patient whether there are moving areas in the current scanning area and carry out a corresponding, preferably automatic, change in the scanning speed.
  • FIG. 1 a schematic representation of the movement detection by parallel beams and their complementary returning beams is shown in FIG.
  • o_ ⁇ corresponds to the angle of rotation in the fan geometry, and ßi to the angle in the beam fan.
  • Two opposing beams are shown, each with a solid and dotted line, which are measured starting from the focus positions shown as solid points, but with a time delay. Remains the one determined there
  • ultrasound information possibly in conjunction with automatic image recognition methods, can also be used to detect the movement or to automatically differentiate between moving and stationary areas.
  • the invention thus presents a method for generating CT images by means of a spiral CT with spiral reconstruction of an examination object that moves cyclically in some areas, different feed speeds v x and v 2 being used during a scan of the examination object depending on whether the scanned area is at least partially cyclical or stationary.
  • a CT is also presented, which has the means for carrying out the described method.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
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Abstract

La présente invention concerne un procédé pour produire des images de tomographie par ordinateur par une tomographie par ordinateur spiralée avec reconstruction spiralée d'un objet d'analyse qui effectue un mouvement cyclique par zones, et un appareil de tomographie par ordinateur associé. Selon l'invention, au cours d'un passage de balayage sur l'objet d'analyse, différentes vitesses d'avancement v1 et v2 sont utilisées, en fonction de si la zone de balayage se déplace de façon au moins partiellement cyclique ou est stationnaire.
EP04739105A 2003-05-16 2004-04-23 Production d'images de tomographie par ordinateur par reconstruction spiralee d'un objet d'analyse qui effectue un mouvement partiellement cyclique Withdrawn EP1624805A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE10322139A DE10322139A1 (de) 2003-05-16 2003-05-16 Verfahren zur Erzeugung von CT-Bildern von einem sich zumindest teilweise zyklisch bewegenden Untersuchungsobjekt, sowie CT-Gerät zur Durchführung dieses Verfahrens
PCT/EP2004/004348 WO2004100791A1 (fr) 2003-05-16 2004-04-23 Production d'images de tomographie par ordinateur par reconstruction spiralee d'un objet d'analyse qui effectue un mouvement partiellement cyclique

Publications (1)

Publication Number Publication Date
EP1624805A1 true EP1624805A1 (fr) 2006-02-15

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EP04739105A Withdrawn EP1624805A1 (fr) 2003-05-16 2004-04-23 Production d'images de tomographie par ordinateur par reconstruction spiralee d'un objet d'analyse qui effectue un mouvement partiellement cyclique

Country Status (5)

Country Link
US (1) US7486762B2 (fr)
EP (1) EP1624805A1 (fr)
JP (1) JP2006528892A (fr)
DE (1) DE10322139A1 (fr)
WO (1) WO2004100791A1 (fr)

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JP4595608B2 (ja) * 2005-03-22 2010-12-08 株式会社島津製作所 核医学診断装置およびそれに用いられる診断システム
US7515678B2 (en) * 2005-11-23 2009-04-07 General Electric Company Method and system for performing CT image reconstruction with motion artifact correction
JP5022612B2 (ja) * 2006-03-07 2012-09-12 ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー Ｘ線ｃｔ装置
JP5165903B2 (ja) * 2006-03-15 2013-03-21 株式会社東芝 Ｘ線ｃｔ装置、ヘリカルピッチ変更方法
US7885374B2 (en) * 2006-03-15 2011-02-08 Kabushiki Kaisha Toshiba X-ray CT apparatus, a method for changing the helical pitch, an image reconstruction processing apparatus, an image reconstruction processing method, and an image reconstruction processing program
JP4322894B2 (ja) * 2006-06-20 2009-09-02 ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー Ｘ線ｃｔ装置
JP5203750B2 (ja) * 2008-03-04 2013-06-05 株式会社東芝 心電同期スキャン方法及びｘ線コンピュータ断層撮影装置
JP5486776B2 (ja) * 2008-03-07 2014-05-07 日立アロカメディカル株式会社 Ｘ線ｃｔ装置、および、その制御プログラム
EP2146321B1 (fr) * 2008-07-14 2012-12-12 Cefla S.C. Correction d'erreur dynamique en imagerie radiographique
CN103239253B (zh) 2012-02-14 2015-07-15 株式会社东芝 医用图像诊断装置
JP5963163B2 (ja) * 2012-02-14 2016-08-03 東芝メディカルシステムズ株式会社 医用画像診断装置
JP6257962B2 (ja) 2012-09-04 2018-01-10 東芝メディカルシステムズ株式会社 Ｘ線ｃｔ装置

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Also Published As

Publication number Publication date
WO2004100791A1 (fr) 2004-11-25
US20070092057A1 (en) 2007-04-26
US7486762B2 (en) 2009-02-03
DE10322139A1 (de) 2004-12-09
JP2006528892A (ja) 2006-12-28

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