EP0612024B1 - Verfahren zur Erzeugung von Schichtbildern und Anordnung zur Durchführung des Verfahrens - Google Patents
Verfahren zur Erzeugung von Schichtbildern und Anordnung zur Durchführung des Verfahrens Download PDFInfo
- Publication number
- EP0612024B1 EP0612024B1 EP94200229A EP94200229A EP0612024B1 EP 0612024 B1 EP0612024 B1 EP 0612024B1 EP 94200229 A EP94200229 A EP 94200229A EP 94200229 A EP94200229 A EP 94200229A EP 0612024 B1 EP0612024 B1 EP 0612024B1
- Authority
- EP
- European Patent Office
- Prior art keywords
- image
- slice
- radiation source
- images
- values
- 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.)
- Expired - Lifetime
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Classifications
-
- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05G—X-RAY TECHNIQUE
- H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
- H05G1/08—Electrical details
- H05G1/60—Circuit arrangements for obtaining a series of X-ray photographs or for X-ray cinematography
Definitions
- the invention relates to a method for generating layer images of a Examining area from a variety of radiation source positions for the purpose of generating separate individual images with X-rays is enforced, with image values being saved for each individual image correspond to the absorption in its pixels and where slice images are generated in the layer image values from the image values of the pixels of the individual images are derived from a layer pixel geometrically assigned.
- a finite - preferably - is used as the pixel and in the following referred to as the square area of a single image, while as Layer image point, a corresponding area is designated in the layer image.
- Such a method and such an arrangement are known, for example from U.S. Patent 3,499,146.
- the individual images are created using a X-ray emitter, which is successively in different Radiation source positions is brought.
- the radiation relief is from one Image converter, e.g. by an image intensifier, whose Output screen is scanned using a television camera.
- the the video signal thus generated is digitized.
- the emerging digital Data words correspond to the image values of the single image. You will be in one preferably stored digital storage device.
- the layer image values for the different layer pixels are derived from the image values of Pixels derived, the geometrical layer pixel in question are assigned, that is to say from those pixels which are generated when the Layer image on the connecting line of the relevant layer pixel with the different radiation source positions.
- Both methods require an intervention in the X-ray generator, which is the X-ray tube feeds, and assume that the current during a Layer recording can be regulated quickly enough.
- the object of the present invention is a method of the beginning mentioned type so that without intervention in the X-ray generator the contrast reversal or the pseudo resolution in slice images can be at least partially eliminated, and an arrangement for To indicate implementation of the procedure.
- the derivative of Slice image values are carried out by a weighted summation, in which the Weight with which the image values of the individual images are included in the summation, the smaller the distance between the radiation source position at the Generation of the relevant image from a medium one Radiation source position was.
- the image processing unit is a Computing unit that uses the image values to generate slice images one from the radiation source position when generating the associated one Single image dependent weighting factor multiplied and the weighted Image values of the image elements geometrically assigned to a layer pixel summed up.
- the Image processing unit contains a memory in which several of each other different sets of weighting factors are stored and that Selection means for - preferably interactive - selection of a set of Weighting factors are provided. The user can then each Choose set of weighting factors that make the most favorable compromise between reducing the undesirable effects on the one hand and the Blurring of details outside of the layer level on the other hand.
- the layer recording device shown partly and purely schematically in FIG. 1 comprises an x-ray emitter 1 which has an x-ray beam 2 on it Input screen of an X-ray image intensifier 3 is emitted.
- the X-ray emitter 1 and X-ray image intensifier 3 along parallel paths in opposite directions to one another a first solid line shown end position in a second Movable end position, which is indicated by dashed lines.
- X-rays are switched on briefly and a single image generated.
- the shift to the different radiation source positions takes place in such a way that the central rays of the beams 2 in all Cut positions in the same point 4. This can be done be ensured that X-ray tube 1 and image intensifier 3 by a Rod to be coupled to each other by one through point 4 horizontal axis perpendicular to the plane of the drawing is pivotable.
- the one containing point 4 and parallel to the directions of movement Level EF is called the Fulcrum level.
- the output image of the X-ray image intensifier 3 is obtained from a video camera 5 converted into an electrical signal by an analog-digital converter 6 digitized and stored in a memory 7, which is sufficient Has capacity to the digitized video signals of all frames to record.
- Each frame can e.g. 256 x 256 or 512 x 512 pixels include.
- the number of frames must be large enough; for one Swivel angle from -20 ° to + 20 ° (opposite the vertical) has one between 30 and 50 number of single images has been shown to be sufficient.
- the memory 7 for each pixel of each frame digital form stores an image value that indicates the absorption of the X-ray radiation in the examination area that represents point 4 surrounds.
- Fig. 2 shows the - for clarification compared to Fig. 1 - changed geometric relationships when recording the individual images.
- Three radiation source positions are shown, the radiation source position P 0 being in the middle of the range of motion and the radiation source positions P -N and P + N being at the ends of the range of motion.
- the individual images B 0 , B -N and B + N are generated in the three positions. For the sake of simplicity, it is assumed that each individual image contains only five pixels which (at their center) are connected to the associated radiation source position by straight lines.
- the image values for each slice pixel must be superimposed by those pixels that are geometrically assigned to this slice pixel.
- the slice image value for the slice pixel S 01 must be determined from the slice image value of the pixel on the far left in each of the individual images.
- the other slice image values for the fulcrum level can be determined analogously.
- it applies to this layer image plane that a layer image point with the coordinates x and y is assigned a layer image value S 0 (x, y) from the individual images the image values B n (x, y) of the image points with the coordinates x, y.
- the value n ranges from -N to + N.
- a different combination of image values from the other image values must be used for the other layers.
- the image value of the left pixel in the individual image B -N the image value of the second image point from the left in the individual image B 0 and the image value of the central image point in the individual image B + N are used.
- the layer image value S 1 (x, y) is composed of the image values B n (x + n, y) for a pixel with the coordinates x, y.
- the coordinates x, y count from the straight line G which connects the central radiation source position P 0 to the center of the single image B 0 generated from this position. It is further assumed that the x-direction coincides with the direction of movement of the radiation sources and y represents the horizontal direction perpendicular thereto (perpendicular to that to the plane of the drawing in FIGS. 1 and 2).
- the layer S -1 this is the first layer above the Fulcrum plane EF
- its layer image values S -1 (x, y) are derived from the pixels B n (xn, y).
- the layer image values S i (x, y) result from one another Derive image values B n (xi • n, y).
- a layer image S i is generated from the individual images stored in the image memory 7 by an image processing unit 8 and displayed on a suitable display unit 9, for example a video monitor.
- the user can on the one hand specify the position i of the layer S i to a suitable setting unit 10 and on the other hand set the extent to which he wants to eliminate contrast reversal and resolution effects.
- the image processing unit 8 contains a computing and control unit 80, which determines the address for the calculation of layer image values of layer image points with the coordinates x, y in a layer i, under which the image value B n (x + i • n, y ) is saved.
- This image value is called up from the memory 7 and fed to a multiplier 81.
- the image value is multiplied by a weighting factor g j (n). This weighting factor is the same for all pixels of the single image B n .
- the weighting factor is taken from a memory 82.
- the image processing unit 8 further contains a layer image memory 83, in which - after the reconstruction of a layer image has been completed - the layer image values S i (x, y) are stored.
- the computing and control unit 80 forms the address x, y of these slice image values and calls up the value stored under this address. At the beginning of the reconstruction, this value is zero. It is added to the value calculated by the multiplier 81 with an adder 84, and the sum thus formed is stored in the memory 83 at the previously called address.
- the arithmetic and control unit 80 then calculates the addresses in the memories 7 and 83 for a different value of x until all x values of a layer image line have been processed.
- the Multiplication and addition by hardware units 81 and 84 carried out.
- the Image processing unit can contain a microcomputer that the Address calculations, multiplications and additions in software performs.
- the described image processing method would lead to the same images that result from the method mentioned at the beginning, in which the image values of the various individual images geometrically assigned to a layer pixel are added to one another.
- 5e has negative values, that is to say that the contrast is reversed (areas of strong absorptions are therefore imaged as if only a small absorption would take place there and vice versa).
- the spatial frequency range between 2 and 3 there is again a normal contrast - although not as great as in the range between 0 and 1. Since the contrast is already zero at the local frequency 1, this course of the modulation transfer function leads to one in the spatial frequency range between two and three Pseudo resolution. In the spatial frequency range above three, the modulation transfer function shows further negative and positive vibrations, the amplitude of which is however becoming smaller and smaller.
- Fig. 5e applies in principle to all layers outside of the Reconstruction of sharply rendered slice.
- the limit of real Resolution shifts all the more to low values of the spatial frequency towards, the greater the distance of the respective structures from the sharp pictured layer is in the examination area. If you do that Takes into account that one varies the unit of the spatial frequency, 5e applies to all of these layers.
- the weighting factors provided for the various images must depend on the radiation source position when the individual image in question is generated, so that the greater the distance between the radiation source position and the mean radiation source position (P 0 ), the smaller the weighting factor .
- G j (n) 1 + a j1 • b 1 + a j2 • b 2
- the index j is intended to indicate that there are several sets of weighting factors (with their own factors a j1 and a j2 ), one of which can be selected for a slice image .
- FIG. 5a represents the modulation transfer function for a plane lying outside the sharply depicted layer plane if the layer image is created with this set of weighting factors. It can be seen on the one hand that there is no reversal of contrast and no pseudo resolution, because the contrast decreases monotonically as a function of the spatial frequency. However, it can also be seen that only structures above a spatial frequency of 2 no longer produce any contrast in the sharply imaged layer, that is to say the blurring effect is only about half as great as in the modulation transfer function according to FIG. 5e, where the spatial frequency 1 already Contrast disappears.
- the curve (c) in FIG. 4 represents the associated envelope and FIG. 5c the modulation transfer function.
- the blurring effect is stronger than, for example, in FIG. 5b, but phase reversal and pseudo-resolution effects can also be stronger - but not as strong as in FIG. 5e, which shows an even stronger blurring effect.
- FIG. 5d shows a modulation transfer function in which the disturbing or desired effects are more pronounced than in FIG. 5c, but not yet as strong as in FIG. 5e.
- a certain weighting factor set g j (n) can initially be provided by the setting unit 10 by presetting j, for example that according to curve (a) in FIG. 4 or according to equations (1) to (3).
- This weighting factor set like the other possible weighting factor sets, is stored in the memory 82, and the weighting factor g j (n) that belongs to the respective individual image B n is called up by the computing and control unit.
- the radiation source positions were symmetrical with respect to point 4 (FIG. 1) in the Fulcrum plane, their distance from one another was the same, and their number was odd. Although these requirements are expedient, they can be omitted individually or as a whole.
- the "mean radiation source position" in the sense of the invention is then the geometric center between the two outer positions; this position does not have to be identical to one of the radiation source positions for the individual images.
- the expression n / N in equation (2) must then be replaced by x / x o , where x denotes the distance of the respective radiation source position from the center and x o the center distance of the outer two radiation source positions .
Landscapes
- Apparatus For Radiation Diagnosis (AREA)
- Image Processing (AREA)
- Image Analysis (AREA)
Description
- Fig. 1
- Teile eines Schichtaufnahmegerätes, mit dem die Erfindung ausführbar ist,
- Fig. 2
- die geometrischen Verhältnisse bei einer Schichtaufnahme,
- Fig. 3
- ein Blockschaltbild einer Einheit zur Durchführung des Verfahrens,
- Fig. 4
- die Abhängigkeit der Gewichtungsfaktoren von der Strahlenquellenposition bei verschiedenen Gewichtungsfaktorsätzen,
- Fig. 5a bis 5e
- die mit den verschiedenen Gewichtungsfaktorsätzen einhergehenden Modulatiosübertragungsfunktionen.
Claims (3)
- Verfahren zum Erzeugen von Schichtbildern eines Untersuchungsbereichs, der aus einer Vielzahl von Strahlenquellenpositionen zwecks Erzeugung voneinander getrennter Einzelbilder mit Röntgenstrahlung durchsetzt wird, wobei für jedes Einzelbild Bildwerte gespeichert werden, die der Absorption in seinen Bildpunkten entsprechen und wobei Schichtbilder erzeugt werden, in dem Schichtbildwerte aus den Bildwerten der Bildpunkte der Einzelbilder abgeleitet werden, die einem Schichtbildpunkt geometrisch zugeordnet sind,
dadurch gekennzeichnet, daß die Ableitung der Schichtbildwerte durch eine gewichtete Summierung erfolgt, bei der das Gewicht, mit dem die Bildwerte der Einzelbilder in die Summierung eingehen, umso kleiner ist, je größer der Abstand der Strahlenquellenposition bei der Erzeugung des betreffenden Einzelbildes von einer mittleren Strahlenquellenposition war. - Anordnung zur Durchführung des Verfahrens nach Anspruch 1 mit wenigstens einem Röntgenstrahler zur Durchstrahlung eines Untersuchungsbereichs aus einer Vielzahl von in einer Ebene liegenden Strahlenquellenpositionen, einem Bildwandler zur Umsetzung der in den Strahlenquellenpositionen aufgenommenen Enzelbilder in Bildwerte, eine Bildspeicheranordnung zum Speichern der Bildwerte der Einzelbilder, eine Bildverarbeitungseinheit zur Erzeugung von Schichtbildern aus den Bildwerten der Einzelbilder,
dadurch gekennzeichnet, daß die Bildverarbeitungseinheit eine Recheneinheit umfaßt, die zur Erzeugung von Schichtbildern die Bildwerte mit einem von der Strahlenquellenposition bei der Erzeugung des zugehörigen Einzelbildes abhängigen Gewichtungsfaktor multipliziert und die so gewichteten Bildwerte der einem Schichtbildpunkt geometrisch zugeordneten Bildpunkte summiert. - Anordnung nach Anspruch 2,
dadurch gekennzeichnet, daß die Bildverarbeitungseinheit einen Speicher enthält, in dem mehrere voneinander abweichende Sätze von Gewichtungsfaktoren gespeichert sind und daß Selektionsmittel zur - vorzugsweise interaktiven - Auswahl eines Satzes von Gewichtungsfaktoren vorgesehen sind.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE4304332A DE4304332A1 (de) | 1993-02-13 | 1993-02-13 | Verfahren zur Erzeugung von Schichtbildern und Anordnung zur Durchführung des Verfahrens |
DE4304332 | 1993-02-13 |
Publications (3)
Publication Number | Publication Date |
---|---|
EP0612024A2 EP0612024A2 (de) | 1994-08-24 |
EP0612024A3 EP0612024A3 (de) | 1995-07-12 |
EP0612024B1 true EP0612024B1 (de) | 2001-10-24 |
Family
ID=6480361
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP94200229A Expired - Lifetime EP0612024B1 (de) | 1993-02-13 | 1994-02-07 | Verfahren zur Erzeugung von Schichtbildern und Anordnung zur Durchführung des Verfahrens |
Country Status (4)
Country | Link |
---|---|
US (1) | US5473653A (de) |
EP (1) | EP0612024B1 (de) |
JP (1) | JPH0793525A (de) |
DE (2) | DE4304332A1 (de) |
Families Citing this family (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6222902B1 (en) * | 1998-11-25 | 2001-04-24 | Picker International, Inc. | Real-time tomographic system with flat panel detectors |
GB0309387D0 (en) * | 2003-04-25 | 2003-06-04 | Cxr Ltd | X-Ray scanning |
GB0525593D0 (en) | 2005-12-16 | 2006-01-25 | Cxr Ltd | X-ray tomography inspection systems |
US8243876B2 (en) | 2003-04-25 | 2012-08-14 | Rapiscan Systems, Inc. | X-ray scanners |
US10483077B2 (en) | 2003-04-25 | 2019-11-19 | Rapiscan Systems, Inc. | X-ray sources having reduced electron scattering |
US6885724B2 (en) * | 2003-08-22 | 2005-04-26 | Ge Medical Systems Global Technology Company, Llc | Radiographic tomosynthesis image acquisition utilizing asymmetric geometry |
US7236834B2 (en) * | 2003-12-19 | 2007-06-26 | Medtronic, Inc. | Electrical lead body including an in-line hermetic electronic package and implantable medical device using the same |
JP2006305198A (ja) * | 2005-04-28 | 2006-11-09 | Morita Mfg Co Ltd | 歯科用クロス断層x線撮影方法及び歯科用クロス断層x線撮影装置 |
US9046465B2 (en) | 2011-02-24 | 2015-06-02 | Rapiscan Systems, Inc. | Optimization of the source firing pattern for X-ray scanning systems |
US11551903B2 (en) | 2020-06-25 | 2023-01-10 | American Science And Engineering, Inc. | Devices and methods for dissipating heat from an anode of an x-ray tube assembly |
Family Cites Families (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3499146A (en) * | 1966-10-10 | 1970-03-03 | Albert G Richards | Variable depth laminagraphy with means for highlighting the detail of selected lamina |
DE3442448A1 (de) * | 1984-11-22 | 1986-05-22 | Philips Patentverwaltung Gmbh, 2000 Hamburg | Verfahren und anordnung zum erzeugen von schichtbildern eines objektes |
FR2648304B1 (fr) * | 1989-06-12 | 1991-08-30 | Commissariat Energie Atomique | Procede de determination d'un espace a partir d'un espace discret connu pour la reconstruction d'images bi ou tridimensionnelles, dispositif de mise en oeuvre et application du procede |
-
1993
- 1993-02-13 DE DE4304332A patent/DE4304332A1/de not_active Withdrawn
-
1994
- 1994-02-07 EP EP94200229A patent/EP0612024B1/de not_active Expired - Lifetime
- 1994-02-07 DE DE59409913T patent/DE59409913D1/de not_active Expired - Fee Related
- 1994-02-10 JP JP6016578A patent/JPH0793525A/ja active Pending
- 1994-02-14 US US08/195,412 patent/US5473653A/en not_active Expired - Fee Related
Also Published As
Publication number | Publication date |
---|---|
JPH0793525A (ja) | 1995-04-07 |
DE59409913D1 (de) | 2001-11-29 |
US5473653A (en) | 1995-12-05 |
EP0612024A2 (de) | 1994-08-24 |
DE4304332A1 (de) | 1994-08-18 |
EP0612024A3 (de) | 1995-07-12 |
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