EP2770911A1 - Procédé permettant de produire des enregistrements tomographiques optimisés - Google Patents

Procédé permettant de produire des enregistrements tomographiques optimisés

Info

Publication number
EP2770911A1
EP2770911A1 EP12784529.5A EP12784529A EP2770911A1 EP 2770911 A1 EP2770911 A1 EP 2770911A1 EP 12784529 A EP12784529 A EP 12784529A EP 2770911 A1 EP2770911 A1 EP 2770911A1
Authority
EP
European Patent Office
Prior art keywords
data set
values
optimized
time
measurement
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Withdrawn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
EP12784529.5A
Other languages
German (de)
English (en)
Inventor
Frank-Detlef Scholle
Joachim Hütter
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.)
Life Molecular Imaging SA
Original Assignee
Piramal Imaging SA
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 Piramal Imaging SA filed Critical Piramal Imaging SA
Publication of EP2770911A1 publication Critical patent/EP2770911A1/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T11/00—2D [Two Dimensional] image generation
    • G06T11/003—Reconstruction from projections, e.g. tomography
    • G06T11/008—Specific post-processing after tomographic reconstruction, e.g. voxelisation, metal artifact correction
    • 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]
    • 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]
    • A61B6/037—Emission tomography
    • 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
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/508—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for non-human patients
    • 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
    • A61B6/5205—Devices using data or image processing specially adapted for radiation diagnosis involving processing of raw data to produce diagnostic data
    • 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
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR 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
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T5/00—Image enhancement or restoration
    • G06T5/50—Image enhancement or restoration using two or more images, e.g. averaging or subtraction
    • 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
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/507—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for determination of haemodynamic parameters, e.g. perfusion CT
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/10—Image acquisition modality
    • G06T2207/10072—Tomographic images
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/30—Subject of image; Context of image processing
    • G06T2207/30004—Biomedical image processing

Definitions

  • tomographic methods allow the generation of sectional images and three-dimensional representations (3D images).
  • a sectional image reflects the internal structures of the examined body as they were after cutting out a thin layer.
  • a 3D representation shows how the examined structures are spatially present.
  • CT computed tomography
  • X-ray absorption profiles of the body to be examined are generated from many directions. From these absorption profiles, the degree of absorption can then be calculated for each volume element of the body and sectional images and 3D representations can be constructed.
  • positron emission tomography is based on the detection of a variety of annihilation events.
  • the more events that are registered the higher the number of data used for reconstruction and the higher the signal-to-noise ratio.
  • the number of events can in principle be influenced both by the amount of tracer administered and the duration of the scan.
  • the burden of the body with radioactive substances should, however, be kept as low as possible in order to avoid side effects. To minimize side effects, the amount of tracer administered should therefore be minimized.
  • the extension of the scan duration is also limited.
  • the examined body area should not move during the recording, since movements in the recordings lead to a false representation of the tracer distribution.
  • Motionless persistence is a burden on the patient. Some movements, such as respiratory movements and cardiac muscle movements, can not be avoided when taking measurements on living organisms.
  • restrict factors such as the half-life of the radioactive isotopes of the tracer and / or the degradation of the tracer in the body its temporal detectability and / or informative value
  • the aim of the development is to provide a tracer that delivers specific biochemical information to the body under investigation with a high signal-to-noise ratio and low body stress. Any increase in the signal-to-noise ratio resulting from improvements in the measurement and containment technique would be a valuable contribution that could help minimize the burden on the body of a tracer.
  • a first subject of the present invention is a method for generating optimized tomography images, comprising at least the steps:
  • the method according to the invention comprises at least the following steps: a) provision of a data record which represents an area in a body during a measuring time, the representation of the body area in the data set being subdivided into a plurality of discrete partial areas, the measuring time in the data set being in a plurality is subdivided by discrete measurement intervals, wherein each subregion is assigned a discrete structure value for each measurement interval; b) establishing boundary conditions about the expected time course of a structure size in the region of the body during the measurement time; c) calculating optimized structure values for each individual subarea on the basis of structural values of the individual subarea at temporally successive measurement intervals taking into account the boundary conditions; d) Output of an optimized data set which represents the body or an area in the body at arbitrary times within the measuring time and which is based on the optimized structure values.
  • the method according to the invention generates from a first data set, which represents an area in a body during a measuring time, a second, optimized data set, which represents an area in the body during freely selectable times within the measuring time
  • representations of the body area can be generated at freely selectable times within the measuring time
  • Step b) can take place before or after step a), i. the designation of the steps with a) and b) does not necessarily mean that first step a) and then step b) takes place
  • the boundary conditions determine the laws that follow the temporal course of the structure size in the area of the body.
  • the temporal course of the structure size is not arbitrary but it inevitably follows the laws, for example, by the anatomy, morphology and / or physiology of the body area and use a tracer or contrast agent are determined by the physical and chemical properties of the tracer or contrast agent. For example, it is extremely unlikely that the absorbance in the computer tomography of a patient increases and decreases oscillatory as a structure size after a single application of a contrast agent
  • step c) of the inventive method optimized structural values are calculated for each individual subsection.
  • Step c) requires the presence of a first data set and of boundary conditions, so that step c) can take place only after the steps a) and b).
  • the calculation is based on the measured structural values and taking into account the boundary conditions.
  • measured structural values are correlated to temporally successive measurement intervals
  • the sections must contain at least one measuring interval. At z. As the computed tomography or magnetic resonance imaging this is to be considered in the measurement of the data set.
  • c2) Means of the structure values within each section, if there is more than one measurement time range in the selected temporal section. Alternatively, instead of the averaging in a section, a corresponding data record with the time length of the considered section can be reconstructed, as for example possible in the case of PET. c3) fitting a compensation curve into the averaged structure values, the compensation curve providing optimized structure values
  • the size of the sections is adapted to the existing measured structure values In the areas of the measuring time in which large changes in the structure values are to be found, the sections are shorter than in the areas of the measuring time in which the structure values are less from one measuring interval to the next measuring interval change strongly.
  • the decisive factor is therefore the first derivation of the structure values according to time. The larger this is, the shorter the sections are.
  • each section is inversely proportional to the amount of first derivative of the structure values by time.
  • the sections can be chosen such that two sections each adjoin one another; it is also conceivable to design the sections in such a way that two or more sections each overlap.
  • the sections are designed such that in each case two temporally successive sections overlap in their edge regions. In a particularly preferred embodiment, two temporally successive sections overlap each in one edge point
  • Averaging is understood to mean the formation of known mathematical mean values such as, for example, the arithmetic or geometric or harmonic or quadratic mean or weighted mean.
  • the choice of the respective mean value depends above all on the considered structure size and the existing boundary conditions.
  • the arithmetic mean is formed.
  • the average values are preferably assigned to the middle of the respective time segment, so that a mean value curve results which represents the average structural values as a function of time.
  • a mean value curve results which represents the average structural values as a function of time.
  • a compensation curve is fitted in the mean value curve.
  • the compensation curve is selected on the basis of the boundary conditions set up in step b) of the method according to the invention.
  • the compensation curve is adjusted so that the deviations between the mean value curve and the compensation curve are as small as possible. It is also a weighted adjustment conceivable. Weighting means that the compensation curve in the area of the higher-weighted structure values may have a smaller deviation from the mean value curve than in the area of the lower-weighted structure values.
  • spline functions are suitable as compensation curves.
  • apart from recirculation peaks for example, a global maximum for the application of a tracer or contrast agent and, if appropriate, in each case a local maximum at zJB. present extravasation, leakage in tumors, specific or unspecific enrichment in the mathematical function.
  • the beginning of the curve can be extrapolated with the aid of the slope of the first two mean values.
  • the compensation curve provides optimized structure values at arbitrary times within the measurement interval, since the compensation curve represents a continuous time curve and does not consist of discrete values
  • the result is a data set with optimized structure values at freely selectable times within the measurement interval. Due to the boundary conditions taken into account, in the optimized data record that has been taken there is information which makes it possible to specifically highlight or suppress morphological and / or physiological structures within the data record.
  • a mathematical model is used to calculate the optimized feature width in step c).
  • This embodiment of the method according to the invention comprises the following steps: c1) providing a mathematical model which describes the temporal behavior of the structure value in the regions of the body; c2) for each subarea: adapting at least one parameter of the model to the measured structure values and determining a model function which optimally reproduces the temporal course of the measured structure values as a result of a mathematical optimization method, the model function being optimized
  • the mathematical model represents the boundary conditions that have been set up in step b) of the method according to the invention.
  • auxiliary means such as e.g. a tracer or contrast agent - preferably a single or multi-compartment model.
  • the considered Kötper Scheme is considered as a built up of one or more compartments body.
  • a compartment in the model is used for each temporal change of the structure value. For example, after a bolus application in the blood of a patient, a tracer distributes itself in a manner and speed characteristic of the patient and the tracer and is gradually eliminated and, if necessary, metabolized.
  • a compartment in the model function is to be provided.
  • various mathematical methods can be used. For example, a model function can be obtained by solving the differential equations that can be established for the model, as is the case in pharmacokinetic modeling.
  • model function can also be obtained by simulating the time evolution of the considered structure values over the measurement time.
  • mode functional parameters By varying the mode functional parameters, a mathematical adaptation of the model function to the temporal behavior of the structure values is possible.
  • the determination of a model function by adaptation to a mathematical model is preferably carried out in the inventive method using the simulation approach.
  • the result is a model function that optimally reproduces the temporal behavior of the structure values in the mathematical sense.
  • the model function provides optimized structure values at arbitrary times within the measurement interval the model function represents a continuous time curve and does not consist of discrete values. For each subarea of the scanned body, a set of optimized parameters, which indicates the influence of each compartment on the temporal course of the structure value, results from the named method variant
  • the contrasting of the vascular system in the output data set can be suppressed or highlighted as required.
  • the result of the model adaptation is thus a data set with optimized structure values and a data set with associated mode parameters, with which the optimized data record can be output in various variants useful for understanding the examination data.
  • step d) of the method according to the invention the output of an optimized data set takes place.
  • the optimized data set represents an area in the examined body.
  • the range in step d) coincides with the range in step a).
  • the area in step d) represents only a partial area of the area from step a). It is conceivable that partial areas have been discarded in the course of or following the calculation of the optimized structural values in step c) or by a motion correction , This applies in particular to edge regions of the data set that may not spatially coincide due to motion in all measurement time intervals.
  • step d) can take place only after step c).
  • the optimized data set may be output in the form of one or more two- or three-dimensional representations of the area of the body on a screen or as an expression. Likewise, it is conceivable that the output takes place on a data carrier in the form of machine-readable data.
  • the optimized data set which has been produced by means of the method according to the invention is likewise an object of the present invention.
  • a further subject of the present invention is a computer program product with program code stored on a machine-readable carrier for carrying out the method according to the invention on a computer.
  • the method according to the invention is suitable for optimizing all known 3D images or tomography images, for example for optimizing SPECT, PET, CT or MRT images, or measurement data from a 3D or 4D ultrasound method or optical tomography ( See relevant literature such as: Ashok Kliurana, Nirvikar Dahiya: 3D & 4D Vitrasound - A Text and Atlas, Jaypee Brothers Medical Pubiishers (P) Ltd., 2004, R.
  • Movements which occur during the measuring time in the scanned body or in subregions of the scanned body are reduced by the method according to the invention in many cases, which is particularly advantageous in highly noisy data sets image blurring, as they are unavoidable in static recordings with only one record per total measurement time are reduced by the method according to the invention and the spatial resolution is closer to the physically possible resolution of the scanning device.
  • the structure values per section located in the different temporal sections are averaged and corrected according to the selected boundary conditions for a main maximum and at most a secondary maximum, if necessary, in the amount of the value.
  • the slightly higher average of the penultimate Section (Minute 44-52) down to the mean of the third last section (minute 36-44) down, since there may be no further maximum in the curve due to the boundary conditions except the much larger secondary maximum at less than 20 minutes.
  • FIGS. 2 to 4 show, by way of example, a section of a measurement data set in the anatomically customary planes.
  • FIG. 2 shows the data set without processing using the method according to the invention.
  • the noise reduction with the method according to the invention can be seen in FIG. 3 on the basis of structures which can be easily recognized and substantially fewer individual spots.
  • FIG. 4 the structure recognizable in FIG. 3 is confirmed.
  • the dataset illustrated in FIG. 4 does not allow any conclusions to be drawn about the kinetics of the tracer distribution in the scanbody, in contrast to the dataset from FIG. figure description
  • Figure 1 Representation of an exemplary time course of the tracer concentration during an in vivo PET scan in a discrete portion of a PET data set
  • the section bars in FIG. 1b are each entered at the level of the value obtained from the section average.
  • the start of the PET scan was done immediately after application of the tracer
  • Figure 2 representation of the anatomical views
  • the scan was performed on a C nomolgus monkey after application of a thrombus tracer from PET tracer research with a small animal PET scanner. Shown is the measurement data record number 28 of 60 successive scans without noise reduction by the inventive method. The measurement duration of each measurement data set is 1 minute. The measurement of all data records took place one after the other without a break.
  • the planes for the views shown are identical to those of Figure 3a-c and Figure 4a-c.
  • the crosses recognizable in the figures represent the cursor position in the computer program product according to the invention with which the figures were created.
  • Figure 3 representation of the anatomical views
  • the scan was performed on a cynomolgus monkey after application of a thrombus tracer from PET tracer research with a small animal PET scanner. Shown is the measurement data set number 28 of 60 successive scans after application of the inventive method. The measurement duration of each measurement data set is 1 minute. The measurement of all data records took place one after the other without a break.
  • the planes for the views shown are identical to those of Figure 2a-c and Figure 4a-c.
  • the crosses recognizable in the figures represent the cursor position in the computer program product according to the invention with which the figures were created.
  • the scan was performed on a cynomolgus monkey after application of a thrombus tracer from PET tracer research with a small animal PET scanner. Shown is the averaging of all 60 individual data sets that were scanned during the total measurement time. The measurement duration of each measurement data set is 1 minute. The measurement of all data records took place one after the other without a break. The individual data sets have not been processed by the method according to the invention.
  • the planes for the views shown are identical to those of Figure 2a-c and Figure 3a-c.
  • the crosses recognizable in the figures represent the cursor position in the Computeiprograinm Cool invention, with which the figures were created.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Medical Informatics (AREA)
  • Physics & Mathematics (AREA)
  • Surgery (AREA)
  • Veterinary Medicine (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Optics & Photonics (AREA)
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  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • High Energy & Nuclear Physics (AREA)
  • General Physics & Mathematics (AREA)
  • Theoretical Computer Science (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Dentistry (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
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  • Measuring And Recording Apparatus For Diagnosis (AREA)
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  • Medicines Containing Antibodies Or Antigens For Use As Internal Diagnostic Agents (AREA)

Abstract

L'invention concerne le domaine des procédés d'imagerie, en particulier à des fins de diagnostic. La présente invention concerne un procédé permettant de produire des enregistrements tomographiques optimisés, un produit-programme informatique permettant la mise en oeuvre du procédé selon l'invention sur un ordinateur, ainsi que les enregistrements optimisés produits au moyen du procédé selon l'invention.
EP12784529.5A 2011-10-25 2012-10-24 Procédé permettant de produire des enregistrements tomographiques optimisés Withdrawn EP2770911A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102011085180A DE102011085180A1 (de) 2011-10-25 2011-10-25 Verfahren zur Erzeugung optimierter Tomografie-Aufnahmen
PCT/EP2012/071035 WO2013060716A1 (fr) 2011-10-25 2012-10-24 Procédé permettant de produire des enregistrements tomographiques optimisés

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EP2770911A1 true EP2770911A1 (fr) 2014-09-03

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EP12784529.5A Withdrawn EP2770911A1 (fr) 2011-10-25 2012-10-24 Procédé permettant de produire des enregistrements tomographiques optimisés

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Country Link
US (1) US20140294275A1 (fr)
EP (1) EP2770911A1 (fr)
JP (1) JP2014535048A (fr)
KR (1) KR20140131500A (fr)
CN (1) CN104144649A (fr)
AU (1) AU2012330480A1 (fr)
BR (1) BR112014009244A8 (fr)
CA (1) CA2853188A1 (fr)
DE (1) DE102011085180A1 (fr)
IL (1) IL231618A0 (fr)
IN (1) IN2014MN00918A (fr)
MX (1) MX2014004276A (fr)
RU (1) RU2014120903A (fr)
SG (1) SG11201401780UA (fr)
WO (1) WO2013060716A1 (fr)
ZA (1) ZA201402962B (fr)

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CN105717087B (zh) * 2016-03-10 2019-05-14 天津大学 螺旋离散扫描式荧光剂药代动力学参数直接成像方法

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US20020035459A1 (en) * 1998-09-14 2002-03-21 George M. Grass Pharmacokinetic-based drug design tool and method
DE102007046579B3 (de) * 2007-09-27 2009-01-29 Siemens Ag Verfahren zur Detektion von Bewegungen und Korrektur von Bewegungen in tomographischen und projektiven Aufnahmeserien und Tomographie- beziehungsweise Projektionssystem zur Durchführung dieses Verfahrens
US8824757B2 (en) * 2009-12-10 2014-09-02 Koninklijke Philips N.V. Method and apparatus for using time of flight information to detect and correct for motion in imaging scans
US8761478B2 (en) * 2009-12-15 2014-06-24 General Electric Company System and method for tomographic data acquisition and image reconstruction
US20110148928A1 (en) * 2009-12-17 2011-06-23 General Electric Company System and method to correct motion in gated-pet images using non-rigid registration
FR2957441B1 (fr) * 2010-03-10 2016-01-01 Commissariat Energie Atomique Procede d'extraction simultanee de la fonction d'entree et des parametres pharmacocinetiques d'un principe actif.
JP5339562B2 (ja) * 2010-03-30 2013-11-13 独立行政法人放射線医学総合研究所 核医学イメージング装置の画像化方法、システム、核医学イメージグシステム及び放射線治療制御システム
CN102151142B (zh) * 2011-04-14 2012-08-15 华中科技大学 一种正电子发射断层成像中的运动门控方法及系统

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Publication number Publication date
DE102011085180A1 (de) 2013-04-25
IN2014MN00918A (fr) 2015-05-01
ZA201402962B (en) 2015-04-29
KR20140131500A (ko) 2014-11-13
MX2014004276A (es) 2014-07-09
US20140294275A1 (en) 2014-10-02
JP2014535048A (ja) 2014-12-25
SG11201401780UA (en) 2014-09-26
AU2012330480A1 (en) 2014-04-17
CA2853188A1 (fr) 2013-05-02
WO2013060716A1 (fr) 2013-05-02
BR112014009244A2 (pt) 2017-06-13
RU2014120903A (ru) 2015-12-10
CN104144649A (zh) 2014-11-12
BR112014009244A8 (pt) 2017-06-20
IL231618A0 (en) 2014-05-28

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