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WO1993018470A1 - Identification de caracteristiques anatomiques a partir de donnees - Google Patents

Identification de caracteristiques anatomiques a partir de donnees Download PDF

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Publication number
WO1993018470A1
WO1993018470A1 PCT/US1992/008497 US9208497W WO9318470A1 WO 1993018470 A1 WO1993018470 A1 WO 1993018470A1 US 9208497 W US9208497 W US 9208497W WO 9318470 A1 WO9318470 A1 WO 9318470A1
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WO
WIPO (PCT)
Prior art keywords
image
target organ
patient
nuclear medicine
interest
Prior art date
Application number
PCT/US1992/008497
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English (en)
Inventor
Jianzhong Qian
Peggy C. Hawman
Original Assignee
Siemens Medical Systems, Inc.
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
Priority claimed from US07/848,769 external-priority patent/US5381791A/en
Application filed by Siemens Medical Systems, Inc. filed Critical Siemens Medical Systems, Inc.
Priority to JP5515634A priority Critical patent/JPH07504506A/ja
Priority to EP92923056A priority patent/EP0630503A1/fr
Publication of WO1993018470A1 publication Critical patent/WO1993018470A1/fr

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Classifications

    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/10—Segmentation; Edge detection
    • G06T7/12—Edge-based segmentation
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/70—Determining position or orientation of objects or cameras
    • G06T7/73—Determining position or orientation of objects or cameras using feature-based methods
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T7/00—Image analysis
    • G06T7/97—Determining parameters from multiple pictures
    • 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
    • G06T2207/10108—Single photon emission computed tomography [SPECT]
    • 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
    • G06T2207/30048—Heart; Cardiac

Definitions

  • the invention relates to nuclear medicine and, more particularly, to images produced by nuclear medicine studies of patient organs.
  • the invention relates to nuclear medicine studies of the heart, proper positioning of a patient in studies of patient organs, and determinations of the depth of an organ, such as the heart, within the body.
  • edge detection methods to identify the location of anatomical features, but such attempts have been unsuccessful.- This is because the data used to construct such images is contaminated by scatter and attenuation. Additionally, nuclear medicine images become even more ambiguous because of low resolution, low signal-to-noise ratio, and the presence of radioactivity from adjacent organs and background tissue. Consequently, conventional detection methods are not helpful in identifying anatomical structures of interest; these methods may locate an edge which is without diagnostic significance and may overlook an edge which is highly important.
  • the camera is mispositioned with respect to the patient's target organ (i.e., the organ of interest). (This may happen where the patient has, e.g., an abnormally oriented heart, or where the patient shifts position after being positioned properly.) Even an experienced technician needs substantial time to collect enough data to assess the positioning of the patient and to correct any mispositioning, and an inexperienced technician may need to repeat these steps one or more times before the patient is positioned properly.
  • the diagnostician is forced to choose between using the resulting suboptimal study (which is of diminished diagnostic utility) or repeating it (and thereby dosing the patient once again and decreasing throughput through the camera) .
  • Another concern relates to positioning of the apparatus with respect to the body.
  • nuclear medicine studies such as bone scans
  • organs such as the heart
  • such proper positioning is difficult because many relevant factors (e.g. orientation of the heart within the patient's body, size of the various portions of the heart) are not known before the study is commenced.
  • a nuclear medicine study is usually commenced by positioning the detector of the scintillation camera in approximately the correct orientation, verifying the correctness of the position originally selected, and adjusting the position as necessary.
  • the verification step is usually carried out by viewing a persistence image of the Region Of Interest (ROI) on the camera display.
  • ROI Region Of Interest
  • the anatomical feature of interest for example, the patient's left ventricle
  • the positioning is not highly repeatable.
  • the location of, e.g., the heart within the ROI is only known in a general way, the patient's position during the second study will not precisely replicate the patient's position during the first study.
  • Such depth information cannot easily be determined from planar nuclear medicine image data. If such depth information is to be obtained using SPECT (single-photon emission computed tomography) data, it is necessary to conduct a second study, and SPECT studies are time- consuming and expensive.
  • SPECT single-photon emission computed tomography
  • One object of the invention is to provide method and apparatus which can identify anatomical features in nuclear medicine images of target organs.
  • Another object of the invention is to provide method and apparatus which can automatically identify anatomical landmarks in nuclear medicine images, even when the images contain insufficient data to be diagnostically useful.
  • a further object of the invention is to provide method and apparatus which will permit automatic positioning of the scintillation camera detector.
  • Another object of the invention is to provide method and apparatus which will help a technician identify an anatomical feature of interest, even when the feature is displayed in a distorted form.
  • the invention proceeds from the realization that conventional edge detection methods are unsuitable for use in nuclear medicine images. This is because such methods do not incorporate any anatomy-specific constraints and therefore cannot distinguish between patterns having diagnostic significance and patterns which lack diagnostic significance. Additionally, because nuclear medicine images of tissue are not sharply focussed even under the best of circumstances, it is difficult for edge detection methods to produce meaningful edge curves.
  • a nuclear medicine image is scanned line by line. For the intensity profile of each scan line, local curvatures are computed to identify local intensity maxima and local intensity minima.
  • line segments are constructed from all identified local intensity maxima, and other line segments are constructed from all identified local intensity minima. Then, these line segments are evaluated to see whether they satisfy constraints which are specific to the anatomical region of interest. If so, the line segments are treated as identifying particular anatomical landmarks, ,and on the basis of these landmarks, boundaries for the target organ or the portion of interest of the target organ can be easily located.
  • the referenced "maximum-minimum- maximum" pattern is dictated by the structure of the heart, that pattern exists at all stages of image acquisition even if there is insufficient data to form an image which would be diagnostically useful.
  • the position of the camera detector with respect to the patient's target organ can be inferred from the relative positioning of the above-mentioned line segments. From this, it can be determined whether the camera has been properly positioned and how the camera should be repositioned; this permits the camera to be repositioned so that a study is not conducted at a suboptimal angle.
  • a camera with a motor-driven gantry can 5 be adapted to automatically position itself to an optimal position.
  • the camera detector can be stepped around the patient at small angular increments (each step position is known as a camera stop) , with one frame of information being acquired at each position.
  • the inferred camera position is registered.
  • the camera is set up at an initial position and
  • an image (advantageously a persistence image) is acquired.
  • the data in the image is computer-analyzed in real time in accordance with the invention .described above and a set of position-defining anatomical landmarks of interest (e.g. the left ventricular
  • a planar image of the organ of interest is acquired, using a focussing collimator, at two known and different heights.
  • the result of this is two images which differ only in the degree of magnification.
  • the method and apparatus for identifying anatomical features is then used to automatically determine, in each of the images, an anatomical landmark related to the organ of interest. Since the focal length of the collimator and the heights of the collimator are known, the difference between the size of the landmark in the two images permits the depth of the organ to be determined using simple geometrical relationships.
  • Fig. 1 is a schematic diagram of a scintillation camera system in accordance with the preferred embodiment of the invention
  • Fig. 2 is a planar image of a patient's heart taken at an angle of 45 degrees Left Anterior Oblique (LAO) ;
  • Fig. 3A is a persistence image of a patient's heart, formed using a parallel hole collimator
  • Fig. 3B is a plot of the detected anatomical landmarks in the patient's heart, superimposed upon the image shown in Fig. 3A;
  • Fig. 4A is a persistence image of a patient's heart, formed using a focussing collimator
  • Fig. 4B is a plot of the detected anatomical landmarks in the patient's heart, superimposed upon the image shown in Fig. 4A;
  • Fig. 5 is a flow chart in accordance with the preferred embodiment of the invention.
  • Fig. 6 shows lines which generally correspond to a patient's ventricles and interventricular septum, derived using the preferred embodiment of the invention
  • Fig. 7 show how a region of interest for locating the left ventricle is determined in accordance with the preferred embodiment of the invention
  • Figs. 8 and 9 show, respectively, a low-statistics
  • FIG. 10 and 11 show, respectively, a low-statistics image of a patient's heart taken at approximately 50 degrees LAO and the anatomical landmarks detected in the image in accordance with the preferred embodiment of the invention
  • Figs. 12 and 13 show, respectively, a low-statistics image of a patient's heart taken at approximately 40 degrees LAO and the anatomical landmarks detected in the image in accordance with the preferred embodiment of the invention
  • Fig. 14 shows how the camera stop position affects the detected length of the interventricular septum as determined in accordance with the preferred embodiment of the invention
  • Fig. 15 shows how the camera stop position affects the detected average intensity of pixels along the interventricular septum as determined in accordance with the preferred embodiment of the invention
  • Fig. 16 shows how the camera stop position affects the detected end point position of the interventricular septum as determined in accordance with the preferred embodiment of the invention
  • Fig. 17 shows the correlations between the relationships displayed in Figs. 14 - 16;
  • Fig. 18 is a flow chart in accordance with the preferred embodiment of the invention in which a scintillation camera detector is automatically positioned in a clinical environment;
  • Fig. 19 is a three dimensional graph of Fig. 2 in which image intensity is shown on the Z axis; Fig. 20 shows a horizontal scan line across the Fig.
  • Fig. 21 is a flow chart of a method in accordance with the preferred embodiment of the invention.
  • Figs. 22A and 22B show the geometrical relationships upon which the preferred embodiment of the invention relies.
  • Fig. 23 is a flow chart in accordance with the preferred embodiment of the invention. Best Mode for Carrying Out the Invention
  • a radioisotope is administered to the patient and the patient's heart is imaged at an appropriate position (typically, 45 degrees LAO).
  • an appropriate position typically, 45 degrees LAO.
  • the patient's ejection fraction it is conventional to identify the boundaries of the patient's left ventricle at various points in the patient's cardiac cycle.
  • a gated bloodpool study is conducted upon a patient 2.
  • a radioisotope is administered to the patient 2 and the heart 4 of the patient 2 is imaged using a scintillation camera generally indicated by reference numeral 6.
  • a number of frames of planar images collected by the camera 6 is routed to a computer 8, and the planar image itself may be displayed upon a display 10.
  • the planar image is a two dimensional picture.
  • the image it is also possible to treat the image as a three-dimensional graph, wherein the X and Y axes represent the Cartesian coordinates of a pixel in the image and the Z axis represents the intensity of the image at that pixel.
  • the intensity of the image at a particular pixel is a function of the number of detected scintillation events which relate to the location of that pixel in the patient 2.
  • Fig. 19 is such a version of the Fig. 2 image.
  • the Fig. 2 image is scanned with a straight line which is parallel to the X axis. At any X position of this line, there will be a particular intensity value which can be treated as a Z value in the Fig. 19 graph, and there will be a plurality of local maxima and minima of Z.
  • the local curvatures of the profile of this scan line can be so computed that local minimum curvatures (negative peaks) precisely correspond to the local maximum points of the profile, the local maximum curvatures (positive peaks) precisely correspond to the local minimum intensity points of the profile, and so that the remaining points of the profile have zero curvature values.
  • the original nuclear medicine image is mapped to a local curvature image where only local maxima and minima are represented by nonzero values. If the heart is located in the image and the scan line crosses it, some of these local maxima and minima will correspond to anatomical features of the heart. For example, as is shown in Fig.
  • the system scans each S-pattern line by line along the X direction, proceeding from the top down or from the bottom up. Two maximum points and one minimum point are detected by intersections of each scan line with the S-pattern. For each scan line, if these three detected points meet all the following conditions, then the S- pattern is assigned a score of 1 from that scan line, otherwise receiving a score of 0.
  • the conditions are: a) the distance between adjacent maximum points should be approximately 8% to 50% of the width of the image, b) the distance between one minimum point and its adjacent maximum points should be approximately 3% to 25% of the width of the image, c) the intensity of each of the minimum points should be greater than 30% of the intensity of the most intense point in the image, and d) the difference in intensity between a minimum point and its adjacent maximum points should be
  • each S-pattern there is a total score which equals the sum of the scores of all the scan lines which intersect it.
  • each of the remaining below-listed constraints is applied to each of the S-patterns.
  • the system selects the single S- pattern which a) meets all of the below-listed constraints and b) has the highest above-defined score of all the S- patterns which meet all of the below-listed constraints.
  • the average intensity of a line segment is defined to be the sum of the intensities of all pixels along the line segment, divided by the total number of such pixels; in effect, total intensity divided by total length.
  • a Region of Interest is constructed on the basis of the lines corresponding to the interventricular septum and the left ventricle.
  • the definition of the ROI is shown in Fig. 7.
  • the height of the ROI is approximately equal to the height of the septum line or the height of the left ventricle line, whichever is greater.
  • the width of the bottom of the ROI is approximately twice the maximum distance between the detected septum line and the detected left ventricle line.
  • the left edge of the ROI is the septum line.
  • the details of the top, the bottom, and the right boundaries of the ROI are shown in Fig. 7. The thus-defined ROI isolates only the left ventricle.
  • the ROI only encompasses a relatively small area and isolates only the left ventricle, it is comparatively easy to locate the boundary of the left ventricle. This is done by using intensity information along the line segment corresponding to the interventricular septum; the intensity along the detected interventricular septum represents the radionuclide activities in heart muscles which immediately adjoin the
  • the boundary of the left ventricle is determined adaptively.
  • the maximum intensity along the line segment which corresponds to the interventricular septum is SMAX
  • the minimum intensity is SMIN
  • the length of the line segment is LNT.
  • an adjustment ratio ADJ is set to equal (SMAX-SMIN)/LNT.
  • the image within the ROI is scanned line-by-line, from the top down.
  • an adaptive threshold value is set to equal (SMAX-ADJ*N) , where N ranges from 0 (top of the ROI) to the bottom of the ROI in integral increments.
  • the pixel is treated as belonging to the left ventricular blood pool region.
  • the left ventricular blood pool region within the ROI is adaptively segmented and a one-pixel-wide edge of the blood pool is determined by labeling the boundary of the segmented region.
  • Figs. 8 - 17 are formed using clinical gated SPECT data which were acquired for approximately one real-time minute per camera stop.
  • Fig. 8 which is taken at approximately 30 degrees LAO
  • the right ventricle partially overlaps the left ventricle.
  • Fig. 9 shows the anatomical landmarks detected from Fig. 8.
  • Fig. 10 which is taken at approximately 50 degrees LAO
  • the right ventricle is partially overlapped by the left ventricle.
  • Fig. 11 shows the corresponding anatomical landmarks detected from Fig. 10.
  • Fig. 12 which is taken at approximately 40 degrees LAO
  • the right ventricle is relatively clearly separated from the left ventricle.
  • Fig. 13 shows the corresponding anatomical landmarks detected from Fig. 12.
  • Figs. 14 - 17 use the parameter relationships of the detected interventricular septum line as an example, and they relate the parameter of interest to the position of the camera (expressed as the camera stop number) .
  • the detected interventricular septum line is indicated in each of Figs. 9, 11, and 13. If a camera is optimally positioned (such that there is a maximal separation between the left ventricle and the right ventricle) then the average intensity (or event counts) in the interventricular septum line should be at a minimum.
  • Figs. 14 - 16 show the actual measurements of these three parameters (length, average intensity and end point position vs. camera stop position number) for the above- mentioned SPECT data.
  • Fig. 17 shows how these three parameters correlate with each other, and clearly suggests that camera stop position number 18 (frame 18) is the optimal camera position. This result is consistent with the optimal position determined independently by an experienced clinic technician unaware of the above analysis. Based upon the combination of the above- mentioned spatial relationships between the detected landmarks, the current camera position can be deduced and the optimal camera position can be inferred. This allows the technician to reposition the patient to avoid finishing the study at a suboptimal angle.
  • the camera may be stepped to a new suggested position determined by the computer in accordance with the present invention. Then, a second set of data can be collected and a new camera position relative to the heart can be determined. The computer can then suggest a final and optimized camera position by comparing the two sets of information which have been accumulated. If necessary, this process can then be repeated until an optimum position has been reached. This is shown in Fig. 18. Positioning of the Patient
  • a cardiac SPECT study is conducted upon a patient 2.
  • a radioisotope is administered to the patient 2 and the heart 4 of the patient 2 is imaged using a scintillation camera generally indicated by reference numeral 6.
  • a number of frames of planar images collected by the camera 6 is routed to a computer 8, and the planar image itself may be displayed upon a display 10.
  • the patient is placed in position and the technician displays, on display 10, a persistence image of the patient's heart to confirm that the positioning is proper (or to detect mispositioning and to correct it) .
  • the technician will usually look for particular anatomical landmarks, such as the boundary of the patient's heart.
  • anatomical landmarks such as the boundary of the patient's heart.
  • a focussing collimator such as collimator 11, shown attached to the
  • SUBSTITUTE SHEET detector of the camera 6 the persistence images of these landmarks may appear distorted and the technician may not be able to recognize them.
  • the camera 6 is set up at an initial position with respect to the patient 2 and acquisition of a persistence image (which may be displayed on display 10) is commenced.
  • a predetermined time perhaps 1 or 2 minutes, but this is not a part of the invention
  • the accumulated data in the persistence image is analyzed in accordance with the method and apparatus described previously.
  • the analysis is carried out in such a manner as to computer-identify a set of anatomical landmarks which define the position of the camera with respect to the organ of interest; in the present instance, wherein the heart 4 is the organ of interest, the computer 8 is programmed to computer-identify the muscles of the left ventricle.
  • one or more plots of the landmarks of interest is computer-generated. Then, these plots are displayed and superimposed upon the corresponding locations in the persistence image. This highlights the features of interest. If the feature is mispositioned within the desired Region of Interest, the orientation of the camera 6 may be changed, either manually by the technician (not shown) with or without a suggested new position calculated by the computer 8, or automatically, under the control of the computer 8. After repositioning, the identification, plotting and superimposition steps are repeated for the new position.
  • Fig. 3A which shows a low-statistics (less than 30 seconds) persistence image on the display 10 that includes the patient's heart 4 and that is formed using a parallel-hole collimator, it can be ⁇ difficult to identify the location of the patient's heart 4 merely by examining the persistence
  • Fig. 4A is another low-statistics (less than 30 seconds) persistence image on the display 10 that includes the patient's heart 4 and that is formed using a focussing collimator 11 (in this instance, a fan-beam collimator) .
  • a focussing collimator 11 in this instance, a fan-beam collimator
  • a plot 12 is generated showing those landmarks as identified from data acquired using a parallel-hole collimator and a plot 14 is generated showing that those landmarks as identified from data acquired using a fan-beam collimator.
  • These plots 12 and 14 may then be displayed on the display 10, superimposed on the respective persistence images at the correct locations (see Figs. 3B and 4B) .
  • Figs. 3B and 4B were not in fact generated using persistence data.
  • planar images were used, and the left ventricular cardiac muscles were identified by scanning the image and locating the line segments of local maxima, which were taken to represent these muscles.
  • a line segment of local minima was also located, and was taken to lie along the long axis of the left, ventricle.
  • the position of the camera with respect to these detected anatomical landmarks can be determined from them because the geometrical relationships between them are already known.
  • the resulting computer-identified anatomical landmarks were then plotted and the plots were superimposed upon persistence images.
  • the relative positions of the patient 2 and the detector 6 of the scintillation camera are adjusted by the technician so that the plot is located in a particular predetermined position on the display 10.
  • the centroid, of the patient's left ventricle may be centered on the display 10, so that when (as in a
  • a nuclear medicine study is conducted upon a patient 2.
  • a radioisotope is administered to the patient 2 and the a target organ such as the heart 4 of the patient 2 is imaged using a scintillation camera generally indicated by reference numeral 6.
  • a number of frames of planar images collected by the camera 6 is routed to a computer 8, and the planar image itself may be displayed upon a display 10.
  • the scintillation camera 6 includes a focussing collimator generally indicated by reference numeral 11.
  • the focussing collimator 11 in the illustrated instance is a so-called "fan-beam" collimator with focal length F which magnifies the image in one direction only, but this is not a part of the invention.
  • the focussing collimator 11 may be a collimator which magnifies the image in more than one direction, and need not be of the fan-beam type.
  • FIG. 22B when the patient 2 is closer to the focussing collimator 11, the image of the interventricular septum 14 of the heart 4 as projected upon the sensitive surface of the crystal (not shown) is smaller than when the patient 2 is further away from the sensitive surface of the crystal.
  • the preferred embodiment of the invention utilizes this property to determine-the depth X of the patient's heart 4 (X being defined as the distance between the center of the
  • the method and apparatus are used to determine the intraventricular septum 14 of the patient's heart 4 as that septum 14 appears in each of the two images. (As is set forth above, this determination can be made even with low- statistics and noisy image data. Thus, even though there may be insufficient data for the two images to be diagnostically useful in and of themselves, there will still be sufficient data to determine the intraventricular septum 14 of the heart 4. )
  • triangle ABC is a right triangle wherein side AB (the length LI of the interventricular septum 14 in the image) forms the shortest side, and side CA has length F.
  • Another triangle DEC is similar to triangle ABC, and by similar triangles:
  • triangle A'B'C* is a right triangle wherein side A'B' (the projection L2 of the interventricular septum 14 in the image) forms the shortest side, and side CA' has length F.
  • Another triangle D'E'C is similar to triangle A'B'C, and by similar triangles:

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  • Engineering & Computer Science (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Physics & Mathematics (AREA)
  • General Physics & Mathematics (AREA)
  • Theoretical Computer Science (AREA)
  • Nuclear Medicine (AREA)

Abstract

Une image obtenue en médecine nucléaire est balayée et des pixels d'une intensité maximale et minimale sont identifiés et corrélés les uns avec les autres à l'aide de contraintes qui sont empiriquement déterminées pour se rapporter à la caractéristique à étudier (tel que le coeur). L'information ainsi obtenue est utilisée pour définir une région à étudier dans laquelle une caractéristique anatomique à étudier peut se trouver, et pour positionner un détecteur à caméra de scintillation permettant d'effectuer une étude en médecine nucléaire dans des positions optimales. Afin de positionner correctement un patient, des repères anatomiques se rapportant à un organe cible sont automatiquement identifiés par un ordinateur. Les repères sont superposés sur une image persistante de l'organe cible. Ceci rend plus aisée l'identification de l'organe cible par un technicien, ainsi que la répétition d'études telles que des études de perfusion myocardique pour lesquelles deux études doivent être effectuées sur un seul patient à deux moments différents. Un repère anatomique associé à l'organe cible est identifié par ordinateur dans chacune des images, et la profondeur de l'organe cible est géométriquement déterminée à l'aide des différences en taille entre les images du repère identifié, ainsi que des différences en hauteur.
PCT/US1992/008497 1992-03-10 1992-10-06 Identification de caracteristiques anatomiques a partir de donnees WO1993018470A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
JP5515634A JPH07504506A (ja) 1992-03-10 1992-10-06 核医学検査にて収集されたデータからの被検対象の解剖学的特徴の自動識別・特定および分析，およびそのような検査を最適位置で実行するための、シンチレーションカメラの自動位置決め，およびそのような特徴の，持続スコープディスプレイ上への重畳
EP92923056A EP0630503A1 (fr) 1992-03-10 1992-10-06 Identification de caracteristiques anatomiques a partir de donnees

Applications Claiming Priority (6)

Application Number Priority Date Filing Date Title
US848,769 1992-03-10
US07/848,769 US5381791A (en) 1992-03-10 1992-03-10 Automatic indentification of anatomical features of interest from data acquired in nuclear medicine studies and automatic positioning of scintillation cameras to carry out such studies at optimal positions
US86083592A 1992-03-31 1992-03-31
US860,835 1992-03-31
US89669292A 1992-06-10 1992-06-10
US896,692 1992-06-10

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WO1997035212A1 (fr) * 1996-03-21 1997-09-25 Siemens Medical Systems, Inc. Detection automatique du deplacement d'un organe du corps, et particulierement d'un deplacement du coeur dans des examens de medecine nucleaire et correction automatique par rapport a ce deplacement
US7047061B2 (en) 2000-12-05 2006-05-16 Koninklijke Philips Electronics N.V. Method of localizing the myocardium of the heart and method of determining perfusion parameters thereof
US7983457B2 (en) 2005-11-23 2011-07-19 General Electric Company Method and system for automatically determining regions in a scanned object
US9066707B2 (en) 2010-08-25 2015-06-30 Koninklijke Philips N.V. Heart location and verification in emission images
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US7711160B2 (en) * 2003-05-28 2010-05-04 Siemens Medical Solutions Usa, Inc. Automatic optimal view determination for cardiac acquisitions
JP5675167B2 (ja) * 2010-05-17 2015-02-25 株式会社東芝 核医学診断装置
CN101856236B (zh) * 2010-06-13 2012-07-04 苏州瑞派宁科技有限公司 一种应用适应性的正电子发射断层成像方法及装置

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EP0630503A1 (fr) 1994-12-28
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