Source: https://patents.google.com/patent/DE19936679C2/en
Timestamp: 2020-08-06 11:10:52
Document Index: 95787208

Matched Legal Cases: ['art 5', 'art 6', 'art 6', 'art 6', 'art 5', 'art 6', 'art 5']

DE19936679C2 - X-ray diagnostic device - Google Patents
DE19936679C2
DE19936679C2 DE1999136679 DE19936679A DE19936679C2 DE 19936679 C2 DE19936679 C2 DE 19936679C2 DE 1999136679 DE1999136679 DE 1999136679 DE 19936679 A DE19936679 A DE 19936679A DE 19936679 C2 DE19936679 C2 DE 19936679C2
DE1999136679
DE19936679A1 (en
1999-08-04 Application filed by Siemens AG filed Critical Siemens AG
1999-08-04 Priority to DE1999136679 priority Critical patent/DE19936679C2/en
2001-03-15 Publication of DE19936679A1 publication Critical patent/DE19936679A1/en
2003-06-18 Publication of DE19936679C2 publication Critical patent/DE19936679C2/en
The invention relates to an x-ray diagnostic device with an x-ray source (8), with a two-dimensional detector (9) arranged opposite it for x-ray radiation emanating from the x-ray source (8) as a conical x-ray beam and with one arranged between the x-ray source (8) and the detector (9) Storage device (11) for an examination object (P), the X-ray source (8) with the detector (9) being able to be pivoted together about a system axis (Z), and at the same time the X-ray source (8) and the detector (9) on the one hand and the storage device (11) on the other hand can be adjusted at least essentially in a straight line relative to each other in the direction of the system axis (Z) and a computer (15) reconstructs images of the examination object (P) from the output signals of the detector (9) that occur.
The invention relates to an X-ray diagnostic device with a X-ray source, with one opposite to it arranged two-dimensional, d. H. areal, detector for from the X-ray source as a conical, z. B. cone-shaped or pyramid-shaped, X-ray beam out x-ray radiation and with one between the x-rays radiation source and the detector arranged Storage device for an examination object, the X-ray source together with the detector by one System axis can be swiveled and a computer is used output signals from the detector reconstructed object.
Such X-ray diagnostic devices are known in which the x-ray source and the detector oppose each other are attached to an arcuate support. There thus different from conventional computer tomographs X-ray source and the detector not on one Such a ring is suitable for a closed ring genetic diagnostic devices especially for intraoperative Application, because due to the arched support is on the patient located in the storage device is easily accessible.
The output data of the detector, which is due to the arcuate the shape of the carrier only with a partial and not with a complete circulation of the x-ray source and Detector around the system axis can be obtained with a 3D rear projection algorithm, which is similar to that of the conventional Computer tomography known Feldkamp algorithm (see L.A. Feldkamp, L.C. Davis, J.W. Kress, 'Practical cone beam algorithm ', J. Opt. Soc. Am., Vol. A6, pp. 612-619, 1984) ver turns to images of layers of the object under examination reconstructed. This reconstruction method is suitable for small opening angles of the x-ray beam and thus the detector system. For far out of the middle level, d. H. of those standing at right angles to the system axis Layer containing the focus of the x-ray source lies layers of the object to be reconstructed however, image errors are to be expected. While this in the case of high-contrast applications, for such are at H. Barfuß, 3D digital angiography, VDE technical report Volume 54: The Digi tale Krankenhaus, VDE-Verlag, X-ray slide described in 1998 designed gnostic devices of the type mentioned, not are recognizable, they can be used for low contrast applications not be neglected. This has the consequence that at least least in low-contrast applications with X-ray diagnostics advise of the type mentioned at the beginning of a limited Area of the examination object free of image errors which can be reconstructed.
In the case of conventional computed tomography devices, this can Problem caused by a so-called spiral scan of the subs be solved by taking continuous Rotation of the X-ray source and detector around the System axis the x-ray source and the detector one hand and the storage device with the lying on it The object under examination on the other hand in the direction of the system axis to be shifted in a straight line to each other. Such an example However, it differs in the case of X-ray diagnostic devices ten of the type mentioned with an arcuate support for the X-ray source and the detector, because in the In the case of such a construction, a continuous rotation of X-ray source and detector around the system axis is closed.
The invention has for its object an X-ray diagnosis Stikgerät of the type mentioned in such a way that also without continuous rotation of the X-ray source and Detector larger volume areas around the system axis Examination object can be scanned.
According to the invention, this object is achieved by an X-ray Genetic diagnostic device with an x-ray source, with a this two-dimensional detector arranged opposite gate for from the x-ray source as a conical x-ray X-rays emanating from a bundle of genes and with a between the x-ray source and the detector Neten storage device for an examination subject, wherein the x-ray source with the detector together by one System axis is oscillating and at the same time the X-ray source and the detector on the one hand and the Storage device, on the other hand, at least essentially in a straight line relative to each other in the direction of the system axis are adjustable and a computer from the occurring Output signals from the detector Images of the examination object reconstructed.
In contrast to conventional computer tomographs, it takes place in the case of the X-ray diagnostic device according to the invention, a oscillating pivoting of the X-ray source and detector tor around the system axis, while at the same time the X-ray gene radiation source and the detector on the one hand and the Storage device on the other hand in the direction of the system axis can be adjusted relative to each other. That way it is possible, even without continuous rotation of the X-ray beam Oil source and detector larger volumes around the system axis of an examination object. Because of the two dimensional detector and the conical or pyramidal The object to be examined becomes the shape of the X-ray beam ject with sufficient amplitude of the oscillating swings kung and if the speed is not too high Relative movement between the X-ray source and detector on the one hand and storage device on the other hand in the direction the system axis scanned without gaps, so that the X-ray given diagnostic devices of the type mentioned Limitation, image-free images only with respect of being able to generate a limited volume is eliminated.
According to preferred embodiments of the invention, the X-ray source and the detector facing each other gend attached to an arcuate support, in the case a C-shaped curved beam of the Sen central axis with the system axis at least essentially Chen matches and the C-shaped curved arch to Generation of the common oscillating swiveling of Roentgen gene radiation source and detector oscillating around its central axis is pivotable. A C-shaped arc offers as experience from X-ray angiography shows, the medi cinical staff to have good access to a appropriate and possibly treated patients.
To complete a scan of the object under examination enable, according to a variant of the invention oscillating panning with an amplitude that is at least equal to 180 ° plus opening angle of the X-ray beam is, the opening angle of a focus of the X-ray source of outgoing X-rays in the Center plane is measured.
In order to ensure a complete scanning of the object under investigation in the direction of the system axis, it is provided according to a variant of the invention that the x-ray source and the detector on the one hand and the storage device on the other hand per period of the oscillating movement by a measure in the direction of the system axis relative to each other ver that is at most equal to Δz max , where
Δ det : width of the detector measured in the direction of the system axis,
D obj : Extent of the area of the examination object to be scanned, measured transversely to the direction of the system axis,
R f : distance of the focus of the X-ray source from the system axis, and
R d : distance of the detector from the system axis.
According to a preferred embodiment of the invention, calc the computer net in the reconstruction of images of the sub search object individual pixels based on those at different projection angles by the respective X-rays extending towards the pixel, each of which lowest inclination relative to the center plane.
According to a particularly preferred embodiment of the invention calculation calculates when reconstructing images of the Object of examination individual pixels based on different projection angles by the respective X-rays running pixel, whereby per project onswinkel several, different inclinations relative to Center plane, showing X-rays in weighted center telung are taken into account, with the result that the Applied X-ray dose better used becomes.
The invention will now be described with reference to the accompanying scheme table drawings explained in more detail. Show it:
Fig. 1 is a front view of a Röntgendia invention gnostikgerätes,
FIG. 2 shows a side view of the X-ray diagnostic device according to FIG. 1,
Fig. 3 shows a schematic, perspective view of the essential components and movement directions of the X-ray diagnostic device according to FIGS. 1 and 2,
Fig. 4, the movement path of the focus of the X-ray source of the X-ray diagnostic apparatus according to the Fig. 1 relative to the support device
Fig. 5, the terms of a complete scan of the object under examination in the direction of the system axis and in the circumferential direction to be considered geometric standpoint ratios, and
FIGS. 6 and 7, the next in which, in the case of the present invention Rönt genetic diagnosis device used reconstruction method to be considered geometric relationships.
Figs. 1 and 2 show an overall designated 1, according to the invention X-ray diagnostic apparatus comprising a base member 2 on which indicated by means of an only schematically in Fig. 1 elevator 3 a a longitudinal axis E having column is mounted adjustable in height in the direction of the double arrow e 4 , The column 4 is rotatably supported about its longitudinal axis E in the direction of the double arrow.
Arranged on the column 4 is a holding part 5 , on which in turn a bearing part 6 for storing a C-shaped curved and thus open support, which is adjustable in the manner to be described below about an isocenter I and is referred to below as C-arm 7 , is appropriate.
On the C-arm 7 , an X-ray source 8 and a detector 9 are mounted opposite one another, in such a way that the central beam M extending through the isocenter I is one of a focus F of the X-ray source 8 starting in FIGS . 1 and 2 by its dashed-in edge rays RS indicated X-ray beam hits the detector 9 approximately in the center. The detector 9 is an area detector, for example an X-ray image intensifier or, as in the case of the exemplary embodiment presented, a so-called flat-panel detector. A flat-panel detector has a plurality of detector elements, which are arranged in a matrix-like manner in, for example, orthogonal detector columns and rows in a detector plane and are not shown in the figures. The detector 9 is arranged relative to the X-ray emitter 8 on the C-arm 7 such that the central point M is perpendicular to the detector plane and the detector columns run parallel to a system axis Z running through the isocenter I.
The C-arm 7 is mounted in a manner known per se in the direction of the double arrow α along its circumference by means of a drive device 10 shown only schematically around the isocenter I and thus about the system axis Z on the bearing part 6 . The system axis Z is perpendicular to the plane of the drawing in FIG. 1 and thus perpendicular to the plane in which the focus of the X-ray source 8 moves in the α direction when the C-arm is adjusted. The latter level is referred to below as the center level. The drive device 10 contains, for example, an electric motor and a coupling which couples this with the C-arm.
The C-arm 7 can be rotated with the bearing part 6 in a manner known per se about a common axis B of the holding part 5 and the bearing part 6 running through the isocenter I and perpendicular to the system axis Z in the direction of the curved double arrow β and in the direction the axis B according to the double arrow b transverse to the system axis Z and thus parallel to the x-axis of the rectangular coordinate system shown in FIG. 3, slidably mounted on the holding part 5 .
For an examination object to be examined by means of the X-ray diagnostic device according to the invention, for example a patient P, a positioning device 11 is provided which has a positioning plate 12 for the patient P, which is attached to a base 13 by means of a drive device 14 adjustable in the direction of its longitudinal axis , which is illustrated by a double arrow labeled z.
The X-ray diagnosis apparatus 1 according to the invention allows a volume of the patient P by receiving zweidimensio dimensional projections from different projection angles α scan, wherein a computer 15 from the corresponding the received projected measurement data, ie for each Pro jection a measurement per detector element comprising from crossing signals of the Detector 9 , three-dimensional image information relating to the scanned volume of the patient P is reconstructed, which can be represented, for example, in the form of sectional images on a monitor 17 attached to the device trolley 2 by means of a holder 16 and connected to the computer 15 . On the holder 16 , a keyboard 18 is also attached, which is connected to the computer 15 and serves to operate the X-ray diagnostic device 1 , which is why the computer 15 is also connected to the X-ray source 8 in order to be able to control it.
To record projections from different projection angles α, the C-arm 7 with the X-ray source 8 and the detector 9 is pivoted along its circumference in the direction of the double arrow α over an angular range which is equal to 180 ° plus fan angle γ. This pivoting takes place in the case of the X-ray diagnostic device 1 according to the invention, unlike in X-ray diagnostic devices according to the prior art, not once, but periodically oscillating, and in addition the mounting plate 11 in the direction of the system axis Z, ie in one direction or another in the direction of the double arrow z , and thus parallel to the z axis of the rectangular coordinate system entered in Fig. 3 is pushed ver. The computer 15 controls the Antriebsein devices 11 and 15 such that there is a preferably constant path speed of the focus F of the X-ray source 8 relative to the bearing plate 12 .
As a result of the periodic oscillating pivoting of the C-arm 7 in the α-direction illustrated in FIG. 4 in an angular range 0 ° ≦ α ≦ α max about the system axis Z - this applies due to the attachment of the X-ray source 8 and detector 9 to the C -Bow 7 α max <360 ° - and the linear relative movement also illustrated in FIG. 3 between the X-ray generator 8 and detector 9 on the one hand and the support plate 12 and patient P on the other hand in the direction of the system axis Z, that is to say in the z direction, results in one spiral portions zigzag composite scan for the path of the focus F of the X-ray source is light 8 illustrate in Fig. 4, with λ the respective period of the pivoting characterizing features and in Fig. 4, the periods of λ = 0,. , , 4 are illustrated.
Since the patient P is irradiated by a cone-like X-ray beam from any position of the focus F of the X-ray source 8 in the manner shown in FIGS. 1 and 2 in conjunction with FIG. 3 due to the areal detector 9 , the patient P or an area ROI of interest in each case is scanned in the z direction, as can be seen in FIG. 5, provided the feed in the z direction does not exceed a maximum permissible value Δz max per period of the pivoting. It applies
Here, in FIG. 5
Δ det : width of the detector measured in the direction of the system axis Z,
D obj : Extent of the area ROI of the patient to be scanned, measured transversely to the direction of the system axis Z,
R f : distance of the focus of the X-ray source from the system axis Z, and
R d : distance of the detector from the system axis Z.
The amplitude of the oscillating pivoting of the C-arm 7 and thus the maximum projection angle α max should be at least 180 ° + γ fan , where γ fan is the fan angle, ie the opening angle of the X-ray beam in the center plane. After scanning over such a projection angle range, the patient P is completely scanned in the α direction. However, the scanning density is different, so that an adjustment must be effected by using a suitable weight function. One then speaks of the so-called 'shortscan' reconstruction (see DL Parker, 'Optimal short scan convolution reconstruction for fanbeam CT', Med. Phys. 9, pp. 254-257, 1982). This type of reconstruction and weighting is mandatory in the case of the x-ray diagnostic device according to the invention, since the projection angle range is necessarily less than 360 ° due to the attachment of x-ray source 8 and detector 9 to an open C-arm 7 .
In the event that the patient P is completely captured by the X-ray beam in the central plane, a method is given below by way of example by means of which the computer 15 uses the cone-shaped X-ray beam in the projection angle range 0 ° ≦ α ≦ α max , so-called cone-shaped measurement data reconstructed to image data.
This procedure is similar to the Feldkamp algorithm (see L.A. Feldkamp, L.C. Davis, J.W. Kress, 'Practical cone beam algorithm ', J. Opt. Soc. Am., Vol. A6, pp. 612-619, 1984) Processing of conical measurement data based on a complete Circulation were measured. There it becomes two Dimensional convolution rear projection methods for two-dimensional inversion of the radon formula to natural Expanded into a three-dimensional rear projection.
In the case of Röntgendiagnostikgerä described above TES is in image reconstruction based on in the manner described by means of FIG. 6 lines, the detector q z q z = 1 to N z and per row N s detector elements, also called channels, comprising detector 9 measurement data obtained proceed as follows:
Referring now referred to in Fig. Reconstruction geometry shown 6 α the projection angle s of -1 / 2N s to + 1 / 2N s current equidistant Abtastkoordi a nate to the detector line q z of the detector 9 belonging planar X-ray fan beam in FIG. 6 Note, however, that in the special case considered here, as a result of the design of the detector 9 used as a flat-panel detector, in contrast to a detector curved around the focus of the X-ray source, the scanning coordinate over the opening angle of an X-ray fan belonging to a detector line q z of the detector 9 is not equidistant.
The x-ray fan of the conical x-ray beam belonging to the middle detector line q m in the middle plane of the detector 9 is not inclined to the detector plane, since it lies in the middle plane z img = 0. The density value f (r, Φ, z img ) to be reconstructed of a pixel r 0 = (r, Φ, z img ) lying in the central plane can be found by the two-dimensional radon inversion (see AC Kak, M. Slaney, 'Principles of Computerized Tomographic Imaging ', IEEE Press, New York, 1988, pp. 87-91, where r, Φ and z img denote the coordinates of an image element.
Here g = 1 / 2h, where h is the Shepp and Designated Logan convolution kernel.
R α (s ', q m ) is the logarithmic projection value determined for the virtual detector coordinate s' in the center plane (detector line q m ). The virtual detector coordinate s' is the projection from the focus through the image point (r, Φ, z img ) into the detector line q m onto a virtual detector, the detector plane of which contains the system axis Z and runs parallel to the detector plane of the detector 9 . In general, the elements 9 of the detector 9 must be determined by interpolation from measurement signals from adjacent detector elements.
The following applies to U:
In order to be able to use the two-dimensional radon inversion equation (equation (1)), the extent of the detector 9 transversely to the direction of the system axis Z must be so large that the patient P is completely covered by the x-ray beam. For X-ray diagnostic devices of the type described here with an X-ray source 8 and detector 9 attached to an open C-arm 7 , this prerequisite is generally not fulfilled, so that, according to FIG. 5, only a limited region of interest ROI of the patient P can be mapped. This in turn has ramifications for the convolution kernel h. Since this is not local, but in principle has infinite dimensions, it can be used because of the problem of 'truncated projections' (see RM Lewitt, RHT Bates, 'Image Reconstructions from Projections I: General Theoretical Considerations', Optik, 50, (1978 Rather, a folding core with a short range must be used, for example a folding core based on recursive filtering (U. Barth, K. Wiesent in DE 198 02 850 A1).
If the pixel r 0 = (r, Φ, z img ) to be reconstructed is not in the center plane, a weighting factor must be introduced in equation (1), similar to the Feldkamp method, which slants the volume scanned in the center plane inclined course of the X-ray beam imaging this pixel and belonging to an X-ray fan inclined to the center plane is taken into account.
q 'denotes the z coordinate projected onto the virtual detector, which is assigned to the x-ray beam passing through r 0 . R s' is the length of the vertical projection of this X-ray beam on the center plane. The following applies:
The reconstruction equation is then
The coordinates (s ', q') are given on the virtual detector by the projected coordinates of the image point r 0 = (r, Φ, z img ):
For the coordinates projected onto the virtual detector with respect to the actual detector, the following results:
m s ' = s' / Δs s + (N s - 1) / 2
and m q ' = q' / Δs d + (N z - 1) / 2 + Δs d / 2.
N z is again the number of detector lines and N s is the number of channels in a detector line. Δs s is the scanning unit measured on the virtual detector transverse to the direction of the system axis Z, ie the distance measured in the direction of the scanning coordinate between two adjacent detector elements of a detector line of the virtual detector.
The current position z f of the focus of the X-ray source depends on the period λ of the pivoting and is given in the projection angle α by:
Here, z f, 0 denotes the position of the focus at the start of the scan and pitch the feed measured in mm in the z direction per period λ of the swivel.
The measured values measured for a projection angle α and assigned to the coordinates projected onto the virtual detector (s ', q' (λ)) can be used by the computer 15 in various ways for image reconstruction.
On the one hand, for each pixel for image reconstruction, the measured value associated with those coordinates projected onto the virtual detector can be selected from the period λ of the oscillation for which the z-spacing | q m - q '(λ) | and thus the inclination of the associated X-ray beam to the center plane takes the smallest value.
On the other hand, alternatively, provided that it is sufficiently low is worked according to the feed in the z direction, in the course of a weighted averaging for each pixel for the same projection angle using different Measured values obtained from X-rays for image reconstruction can be used (see S. Schauer, 'Practical Image Recon struction for Cone Beam Computed Tomography ', dissertation, Erlangen, 1998), which shows better use of the patient P X-ray dose supplied allowed. The following applies:
The x-ray beam assigned to the detector line q, the s'-coordinate of which is identical to the vertical projection of the pixel P to be reconstructed onto the center plane, intersects the straight line in point parallel to the system axis Z at point P ". The difference of the z- The value of P "for the z-value of the picture element P defines the z-distance d z (α, λ, q) for the period of oscillation λ. Referring to FIG. 7, this is given by
d z (α, λ, q) = z (α, λ, q) - z img
A weight function h, which may have a triangular shape, for example, is used for the weighted averaging of the measurement values obtained by means of a plurality of X-rays.
The interpolation width w controls the width of the Weight function h in the z direction.
The corresponding normalized weight function h 'is:
The reconstruction is now carried out using generalized projections using the weighted averaging method. These are calculated as:
Depending on the interpolation width w, measured values from different periods λ contribute to the pivoting to the respective projection value R α (s', z img ).
By choosing the interpolation width w, the image roughness rule and the resolution in the z direction are influenced, whereby the noise decreases with increasing interpolation width w and with decreasing interpolation width w the resolution in z Direction increases.
In the case of the described embodiment is a Number of adjustment options for the C-arm provided. It is only essential for the invention that the C-arm is pivotable about the system axis and the C-arm and the Storage plate so aligned relative to each other can that the displacement of the support plate parallel to Direction of the system axis.
Incidentally, the relative movement between the C-arm and position rungsplatte not necessarily take place in that the Storage plate is adjusted. It exists within the Rather, the invention also enables the C-arm to be relative to move to the storage plate or both the C-arm as well as to move the storage plate.
The X-ray source and the detector need not be necessary conveniently attached to a C-arm. Essential is only for the invention that the X-ray source and the detector oscillates together around the system axis can be pivoted, with such solutions being preferred are that have good access to medical staff too allow a patient lying on the bed plate. Instead of that in the case of the described embodiment provided storage plate can be the storage device other means of recording the examination exhibit jektes.
Instead of that in the case of the described embodiment provided flat panel detector can also flä another Chenlike detector, for example an X-ray image intensifier ker, be provided.
The exemplary embodiment described is a stationary X-ray diagnostic device. The invention can however, also for use in X-ray diagnostic devices men, where at least the C-arm is more mobile than one Equipment cart running base part is attached. A one X-ray diagnostic device having such a device cart can both with a stationary and with a self-mobile Find patient support device if only it is ensured that the described scanning movement kor can be executed right.
1. X-ray diagnostic device with an X-ray source, with one of these two-dimensionally arranged Nale detector for from the X-ray source as a cone shaped x-ray beam outgoing x-rays and with one between the x-ray source and the Detector arranged storage device for a Untersu Object, the X-ray source with the Detek gate can be pivoted together oscillating about a system axis and at the same time the x-ray source and the detector on the one hand and the storage device on the other hand little Mostly straight in the direction of the system axis are adjustable relative to each other and a computer from the output signals of the detector that occur Reconstructed object of examination.
2. X-ray diagnostic device according to claim 1, wherein the X-ray gene radiation source and the detector opposite each other are attached to an arcuate support.
3. X-ray diagnostic device according to claim 1 or 2, the Trä ger is designed as a C-shaped curved arc, the Mit telachse with the system axis at least essentially matches and that for generating the common oscillie around pivoting of the X-ray source and detector its center axis is oscillating.
4. X-ray diagnostic device according to one of claims 1 to 3, whose X-ray source has a focus from which an x-ray beam emanates that is at right angles to the system axis, the focus of the x-ray plane containing the source of the oil source has an opening angle, and where the oscillating panning with an amplitude takes place, which is at least equal to 180 ° plus opening angle.
5. X-ray diagnostic device according to one of claims 1 to 4, in which the X-ray source and detector on the one hand and the storage device on the other hand are shifted relative to each other by a measure in the direction of the system axis per period of the oscillation, which is at most equal to Δz max , where applicable
Δ det : width of the detector measured in the direction of the system axis
Δ obj : Extent of the area of the examination object to be scanned, measured transversely to the direction of the system axis
R f : distance of the focus of the X-ray source from the system axis
R d : distance of the detector from the system axis
6. X-ray diagnostic device according to one of claims 1 to 5, in which the computer when reconstructing images of the Object to be examined individual pixels based on those at different projection angles by the respective X-rays running towards the pixel are calculated each have the slightest inclination relative to the center plane sen.
7. X-ray diagnostic device according to one of claims 1 to 5, in which the computer when reconstructing images of the Object of examination individual pixels based on different projection angles by the respective X-rays extending pixel, where per Projection angle several different inclinations relative weighted x-rays to the detector Averaging are taken into account.
DE1999136679 1999-08-04 1999-08-04 X-ray diagnostic device Expired - Fee Related DE19936679C2 (en)
DE1999136679 DE19936679C2 (en) 1999-08-04 1999-08-04 X-ray diagnostic device
US09/624,230 US6435714B1 (en) 1999-08-04 2000-07-24 X-ray diagnostic device
JP2000230714A JP2001061826A (en) 1999-08-04 2000-07-31 X-ray diagnostic system
DE19936679A1 DE19936679A1 (en) 2001-03-15
DE19936679C2 true DE19936679C2 (en) 2003-06-18
ID=7917144
DE1999136679 Expired - Fee Related DE19936679C2 (en) 1999-08-04 1999-08-04 X-ray diagnostic device
US (1) US6435714B1 (en)
JP (1) JP2001061826A (en)
DE (1) DE19936679C2 (en)
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1999-08-04 DE DE1999136679 patent/DE19936679C2/en not_active Expired - Fee Related
2000-07-24 US US09/624,230 patent/US6435714B1/en active Active
2000-07-31 JP JP2000230714A patent/JP2001061826A/en not_active Abandoned
H. Barfuß, Digitale 3D-Angiographie, VDE-Fachber- icht Bd. 54: Das Digitale Krankenhaus, VDE-Verlag,1998 *
L.A. Feldkamp, L.C. Davis,J.W. Kress, Practical cone beam algorithm', J.Opt. Soc. Am., Vol. A6, pp. 612-619, 1984 *
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