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WO2008017493A2 - Dispositif et procédé de détermination de la phase de reconstruction d'image optimale pour des objets se déplaçant de manière quasi-périodique - Google Patents

Dispositif et procédé de détermination de la phase de reconstruction d'image optimale pour des objets se déplaçant de manière quasi-périodique Download PDF

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Publication number
WO2008017493A2
WO2008017493A2 PCT/EP2007/007091 EP2007007091W WO2008017493A2 WO 2008017493 A2 WO2008017493 A2 WO 2008017493A2 EP 2007007091 W EP2007007091 W EP 2007007091W WO 2008017493 A2 WO2008017493 A2 WO 2008017493A2
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WO
WIPO (PCT)
Prior art keywords
phase
reconstruction
image reconstruction
image
function
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.)
Ceased
Application number
PCT/EP2007/007091
Other languages
German (de)
English (en)
Other versions
WO2008017493A3 (fr
Inventor
Dirk Ertel
Marc Kachelriess
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.)
VAMP VERFAHREN und APPARATE DER MEDIZINISCHEN PHYSIK GmbH
Original Assignee
VAMP VERFAHREN und APPARATE DER MEDIZINISCHEN PHYSIK GmbH
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 VAMP VERFAHREN und APPARATE DER MEDIZINISCHEN PHYSIK GmbH filed Critical VAMP VERFAHREN und APPARATE DER MEDIZINISCHEN PHYSIK GmbH
Priority to EP07801594A priority Critical patent/EP2049017A2/fr
Publication of WO2008017493A2 publication Critical patent/WO2008017493A2/fr
Publication of WO2008017493A3 publication Critical patent/WO2008017493A3/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T11/00—2D [Two Dimensional] image generation
    • G06T11/003—Reconstruction from projections, e.g. tomography
    • G06T11/005—Specific pre-processing for tomographic reconstruction, e.g. calibration, source positioning, rebinning, scatter correction, retrospective gating
    • 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
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5258—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise
    • A61B6/5264—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise due to motion
    • A61B6/527—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise due to motion using data from a motion artifact sensor
    • 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
    • A61B6/54—Control of apparatus or devices for radiation diagnosis
    • A61B6/541—Control of apparatus or devices for radiation diagnosis involving acquisition triggered by a physiological signal
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2211/00—Image generation
    • G06T2211/40—Computed tomography
    • G06T2211/412—Dynamic

Definitions

  • the invention relates to a device and a method for determining the optimal image reconstruction phase for quasi-periodically moving objects, in particular with regard to X-ray computed tomography (CT) of the heart.
  • CT computed tomography
  • the representation of the heart can lead to characteristic movement artifacts in the reconstructed images.
  • the reconstruction algorithm can be synchronized with the object movement. In this case, only projection data from the same movement phases (preferably those with minimal movements of the object to be examined) for a
  • Image reconstruction is used and the remaining data is not taken into account or with reduced weight. This can increase the temporal resolution of the imaging system and the objects are displayed in a quasi-static state.
  • Synchronization signal most widely used for image reconstruction. Moreover, it is known to use the kymogram function, which is e.g. represents the time-dependent centroid movement of a slice under study to use as a synchronization signal.
  • tube current modulation can reduce the dose burden on a cardiac CT scan, with CT's tube current in the high-motion cardiac phases providing low image contributions
  • TCM tube current modulation
  • the heart movement is a non-uniform quasiperiodic motion
  • the heart has a high rate of movement.
  • the diastolic phase on the other hand, after relaxation, the heart is in a short, sedentary resting phase.
  • the diastolic phase which is between 60% and 80% of an RR cycle of an ECG signal
  • the systolic phase which is between 20% and 40% of a RR cycle, for artifact-free reconstruction.
  • An object of the present invention is to enable automatic determination of this optimal reconstruction phase in view of reduction of motion artifacts.
  • This object is achieved by a method for displaying a quasi-periodically moving object with the aid of an image recording system, in particular a computer tomograph, using a phase-correlated reconstruction technique in which an optimal image reconstruction phase is determined using a motion function of the object.
  • Determining the optimal image reconstruction phase using a motion function of the object is characterized.
  • the invention is also achieved by using the motion function of an object to determine an optimal image reconstruction phase in a method of displaying a quasi-periodically moving object using a phase-correlated reconstruction technique and a computer program for solves an above-mentioned image pickup system comprising computer program instructions for carrying out the above-mentioned method when the computer program is executed on a computer.
  • a quasi-periodic signal is understood as meaning a signal with a recurring signal profile, the period of which, however, being variable and not necessarily constant. In this sense, however, a quasi-periodic signal can also be strictly periodic.
  • the present invention modifies the current standard reconstruction technique for computed tomography (CT) -based imaging of moving objects. To obtain images free of motion artifacts, a phase-correlated reconstruction technique is used.
  • the present invention describes a computer tomograph with a fully automatic, computer-aided determination of the optimal reconstruction phase to minimize the
  • the phase section of the quasi-periodic motion function of the moving object is determined from a movement function of the object, in particular the kymogram function, in which a minimal movement takes place.
  • the size of the considered phase section is determined by the system parameters of the imaging modality used.
  • the method described relies on the direct analysis of the actual movement function of the object, ie for example, the actual heart movement function, not a similarity calculation or third-party data.
  • the determination of the optimal reconstruction phase is not based on data describing the object movement only indirectly or indirectly, but on the basis of direct and immediate motion data.
  • the determination of the optimal reconstruction phase takes place exclusively in the raw data space, ie in particular using CT raw data.
  • the image quality is thus improved without the need for steps beyond the already performed image reconstruction.
  • no calculations in the image space, ie based on already reconstructed CT images, are required. This significantly reduces the total time required for the actual CT scan, resulting in a noticeably improved CT scan.
  • the core of the invention is a method that allows to individually calculate the optimal phase for an image reconstruction, in real time for each individual period of the movement, in real time. As a result, the time required for the image reconstruction or the image quality can be improved.
  • the kymogram signal is calculated from the raw data at fixed time intervals, which reflects the time course of the center of mass, from which in turn its speed and finally the optimal reconstruction phase, namely that with minimal movements, can be calculated. In one embodiment of the invention, that of the
  • kymogram kymogram function
  • kymogram signal kymogram signal
  • Fig. 2 shows the ECG signal and the corresponding
  • FIG. 4 shows a cardio-CT image created using a conventional reconstruction technique and a cardio-CT image created using a phase-correlated reconstruction technique.
  • the present invention describes the detection of the optimal motion phase for phase-correlated image reconstruction using the calculated cardiac motion function, the kymogram. This allows a motion artifact-free image reconstruction in the optimal reconstruction phase. A patient-specific adaptation of the reconstruction phase is no longer necessary.
  • the invention will be described below using the example of a cardio-CT system 1. This consists essentially of imaging elements 2 (X-ray tube, detectors, etc.) and an associated control component 3 and a Schmrekoristrukomponente 4, which creates CT images using the raw data obtained from the imaging elements 2, see. FIG. 1. The steps essential to the invention described below are predominantly realized by the control component 3.
  • control component 3 comprises at least one data processing unit with a number of function modules explained in greater detail below, wherein each function module is designed to perform a specific function or a number of specific functions according to the described method.
  • the function modules can be hardware modules or software modules.
  • the invention can be implemented either in the form of computer hardware or in the form of computer software or in a combination of hardware and software.
  • the functions described below are realized by computer program instructions when the computer program is executed on a computer.
  • the computer may be, for example, a standard personal computer or a dedicated medical workstation.
  • the computer program instructions are implemented in a manner known per se in any programming language and can be provided to the data processing unit in any form, for example in the form of data packets which are transmitted via a computer network or in the form of a diskette, a CD-ROM or the like. ROM or a computer program product stored on a different medium.
  • the image reconstruction component 4 also comprises at least one data processing unit and a computer software designed correspondingly for image reconstruction.
  • Such an image reconstruction component is known in the art. In particular, it may be a computer unit installed remotely from the imaging elements 2.
  • the control component 3 comprises a first functional module 5, which is designed to provide the kymogram function of the examined heart.
  • the first functional module 5 with the imaging elements 2 of the CT
  • the kymogram is calculated by the first function module 5 directly from the CT raw data. In contrast to an ECG 7 in which this is only indirectly the case, with the kymogram the actual movements of the heart are detected. On the known structure and the operation of this first functional module 5 of the control component 3 will not be discussed further below.
  • the kymogram signal is provided by the first functional module 5 to a second functional module 6 of the control component 3 or transmitted to it via a data line 103. This second functional module 6 then performs the individual steps described in detail below.
  • FIG. 2 shows an ECG signal 7 and the corresponding kymogram function 8.
  • the movement phase p represents the relative time within the period, ie the time within a period tp € [0, T [normalized to the period T:
  • Phase motion function is preferably obtained by averaging the motion function r c (t) over the recording duration for a selected motion phase p:
  • a motion function of the COM points is generated which is representative of a motion cycle of the COM
  • the modular phase refers to an arbitrary synchronization signal, which reflects the quasi-periodic object movement.
  • the kymogram function itself can be used as the synchronization signal.
  • an additional ECG 10 is used, which is connected via a data line 102 to the control component 3 of the CT system 1.
  • the RR cycle 11 of such an ECG signal is shown in Fig. 2 (below).
  • a phase motion function 12 of an example patient r c (p) for p ⁇ t) e [0, 1 [with 100 samples is shown in FIG.
  • the gray scale coding allows an assignment to the corresponding ECG signal in FIG. 2 (bottom).
  • the velocity of the heart with respect to the motion phase can be determined with the aid of the distance of two adjacent phase-based COM points r c ⁇ p) and r c (p + ⁇ p) to one another.
  • two adjacent COM points at higher speeds have a greater distance ⁇ r c (p + ⁇ p) -r c (p)
  • the optimal reconstruction phase p opt is determined by solving a minimization problem in the second functional module 6 of the control component 3.
  • the distance of the phase COM point r c (p) with respect. of the phase point p to the neighboring phase points r c (p + pi) is minimized by a relevant range 2 -p w :
  • the relevant region 2 -p w width of the time window for the phase-correlated image reconstruction
  • the relevant region 2 -p w is defined by the relative time resolution in the specific example of a phase-correlated image reconstruction in the cardio-CT. This is from the patient's heart rate used
  • the window width would increase at higher heart rates and approximately halve when using a multi-segment reconstruction algorithm with, for example, two windows.
  • Image reconstruction component 4 transmit control signals that enable the selection element to select only those CT raw data for image reconstruction, which include a minimum possible object movement.
  • the necessary measurement data for image reconstruction receives the corresponding component 4 via the data line 107 from the imaging element 2.
  • Reconstructed cardiac CT image 13 and an image 14 made with a phase-correlated reconstruction technique, as shown in FIG. 4, illustrates the improved image quality.
  • Tube current modulation performed.
  • the kymogram function r c (fc) is already calculated during the CT scan.
  • the phase motion function r c (p) can then not be calculated by averaging over the entire recording duration of the kymogram function r c (t), but instead results in a phase movement function dependent on the time of recording:
  • the optimal reconstruction phase P o p t (t) is a time dependency. From this time dependence, the timing of the optimal reconstruction phase within the next cycle of motion can be predicted. This is done using appropriately adapted calculation algorithms in the second functional module 6 of the control component. In other words, from already determined values, the optimum reconstruction phase for the next heart movement cycle can be predicted. Depending on this, then an activation of the imaging elements 2 of the CT system 1 via a
  • Data line 104 in particular the X-ray tube, by the second functional module 6 such that in motion-rich phases that provide low image contributions, the tube current as a function of the cardiac phase p (fc) designed and thus the dose burden is reduced.
  • a correlation calculation is carried out with a template curve (sample movement pattern). For this purpose, previously determined patient-specific
  • the template curve is then stored in the second functional module 6 or provided to the second functional module 6 for use, for example, from an external database via a data line 105, which also for data transport of result or control data of the control component 3 to an external receiving station (not shown) can be.
  • the second functional module uses the minimization method described above to make the optimal reconstruction phases global, within one Movement cycle, or locally, for example, within the systolic or diastolic phase, determined in the Tetnplatekurve.
  • the optimal reconstruction phase and characteristic movement phases such as the midsystolic and diastolic phases, can be determined become. In other words, a comparison of measured data with pattern data takes place so that an optimal reconstruction phase already determined in advance can be found very quickly.
  • This correlation calculation is applicable to both online (ie, real-time) and standard off-line calculation.
  • Template curves can be provided in particular for different heart rate ranges.
  • the heart rate dependency of the optimal reconstruction phase can be met in a simple manner.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Medical Informatics (AREA)
  • Physics & Mathematics (AREA)
  • Biomedical Technology (AREA)
  • Molecular Biology (AREA)
  • Biophysics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Optics & Photonics (AREA)
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  • Radiology & Medical Imaging (AREA)
  • Veterinary Medicine (AREA)
  • Heart & Thoracic Surgery (AREA)
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Abstract

L'invention concerne un dispositif et un procédé de détermination de la phase de reconstruction optimale d'une image pour des objets se déplaçant de manière quasi-périodique, en particulier concernant la tomographie computérisée (CT) du coer. L'un des objectifs de la présente invention est, dans le cadre de la réduction des artéfacts de déplacement, de permettre une détermination automatique de la phase de reconstruction optimale d'une image. Cet objectif est atteint par un procédé de représentation d'un objet se déplaçant de manière quasi-périodique à l'aide d'un système d'enregistrement d'image (1), en particulier d'un scanner, en utilisant une technique de reconstruction à corrélation de phase, dans lequel est déterminée une phase de reconstruction optimale d'une image à l'aide d'une fonction de mouvement (8) de l'objet.
PCT/EP2007/007091 2006-08-10 2007-08-10 Dispositif et procédé de détermination de la phase de reconstruction d'image optimale pour des objets se déplaçant de manière quasi-périodique Ceased WO2008017493A2 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP07801594A EP2049017A2 (fr) 2006-08-10 2007-08-10 Dispositif et procédé de détermination de la phase de reconstruction d'image optimale pour des objets se déplaçant de manière quasi-périodique

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102006037601.3 2006-08-10
DE102006037601A DE102006037601A1 (de) 2006-08-10 2006-08-10 Vorrichtung und Verfahren zur Bestimmung der optimalen Bildrekonstruktionsphase für sich quasiperiodisch bewegende Objekte

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Publication Number Publication Date
WO2008017493A2 true WO2008017493A2 (fr) 2008-02-14
WO2008017493A3 WO2008017493A3 (fr) 2008-04-10

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EP (1) EP2049017A2 (fr)
DE (1) DE102006037601A1 (fr)
WO (1) WO2008017493A2 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102009028805A1 (de) 2009-04-23 2010-10-28 Mir Medical Imaging Research Holding Gmbh Vorrichtung und Verfahren zur Bestimmung der Bewegungsphase sich quasiperiodisch bewegender Objekte mit dem Ziel der Steuerung von Aufnahmesystemen
US10736594B2 (en) 2018-11-26 2020-08-11 General Electric Company Data-based scan gating

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DE102011078517B4 (de) * 2011-07-01 2013-09-05 Siemens Aktiengesellschaft Verfahren zum Bereitstellen einer Darstellung eines sich nahezu zyklisch bewegenden Objekts
CN109389653B (zh) * 2018-09-27 2023-01-03 上海联影医疗科技股份有限公司 心脏图像重建方法、装置、计算机设备和可读存储介质
US11024062B2 (en) 2018-06-11 2021-06-01 Shanghai United Imaging Healthcare Co., Ltd. Systems and methods for evaluating image quality

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JP2664189B2 (ja) * 1988-03-25 1997-10-15 株式会社日立製作所 核磁気共鳴を用いた検査装置
US5271055A (en) * 1992-08-19 1993-12-14 General Electric Company Methods for reducing motion induced artifacts in a projection imaging system
DE19854939C2 (de) * 1998-11-27 2001-11-22 Siemens Ag Verfahren und Gerät zur Erzeugung von CT-Bildern
EP1061474A1 (fr) * 1999-06-17 2000-12-20 VAMP Verfahren und Apparate der Medizinischen Physik GmbH Tomographe réduisant les artéfacts de mouvement d'un objet et extrayant des informations quant au mouvement de l'objet
WO2001041648A1 (fr) * 1999-12-07 2001-06-14 Koninklijke Philips Electronics N.V. Procede de traitement d'images a ultrasons et systeme d'affichage d'une sequence d'images composites d'un segment arteriel
DE10129631A1 (de) * 2001-06-20 2003-01-02 Philips Corp Intellectual Pty Verfahren zur Rekonstruktion eines hoch aufgelösten 3D-Bildes
US7620444B2 (en) * 2002-10-05 2009-11-17 General Electric Company Systems and methods for improving usability of images for medical applications
US7542544B2 (en) * 2004-01-06 2009-06-02 The Regents Of The University Of Michigan Ultrasound gating of cardiac CT scans
ITPI20040066A1 (it) * 2004-09-21 2004-12-21 Cnr Consiglio Naz Delle Ricerche Metodo e dispositivo per la valutazione automatica di indici di funzionalita' cardiovascolare mediante elaborazione di immagini ecografiche
JP2008525081A (ja) * 2004-12-22 2008-07-17 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ 心臓のコンピュータ断層撮影の方法及び装置

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102009028805A1 (de) 2009-04-23 2010-10-28 Mir Medical Imaging Research Holding Gmbh Vorrichtung und Verfahren zur Bestimmung der Bewegungsphase sich quasiperiodisch bewegender Objekte mit dem Ziel der Steuerung von Aufnahmesystemen
US10736594B2 (en) 2018-11-26 2020-08-11 General Electric Company Data-based scan gating

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WO2008017493A3 (fr) 2008-04-10
DE102006037601A1 (de) 2008-02-14
EP2049017A2 (fr) 2009-04-22

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