Picker International, Inc.

Koninklijke Philips Corporation N.v.

Other

Philips Medical Systems (cleveland), Inc.

Leonard F Plut

David Nicolay

Dennis K Everett

Joseph S Deucher

Pieter Gerhard Roos

Donald E Negrelli

Kenneth L Freeman

Robert J Vagi

Marc Piscitelli

Zhongmin Lin

Andrew J Ivan

Marc Anthony Chappo

Jerome John Griesmer

Timothy J Crish

Frank C Valentino

Robert E Shroy, Jr

Andrew J Ivan, Jr

Gerhard P Roos

Charles G Cassudakis

William C Widlicka

Louis A Paradiso

William F Nyman

John A Shovary

David L Leong

A diagnostic imaging system () includes an x-ray source (), which is rotated around an examination region () on a rotating gantry (). A subject, disposed on a couch (), is translated longitudinally through the examination region (). The imaging system is standardized such that a common subassembly is adapted to receive a bore () of any selectable diameter. The common subassembly includes a stationary gantry () and a bearing race () supported by bearing members (). Standard motor modules (), standard power slip ring modules (), and standard information transmission modules () are disposed about the race (). The number of the standard modules () is specified by a user.

Open access air bearing gantry

A diagnostic imaging system includes a rotating gantry ( ) which defines a subject receiving aperture ( ). A rotatable source of high energy penetrating radiation ( ) and a corresponding two-dimensional flat panel x-ray detector ( ) are disposed across the subject receiving aperture ( ). A plurality of nuclear detector heads ( ) are movably attached to the rotating gantry ( ) in order to detect radiation emitted by a radiopharmaceutical injected into the subject ( ). Each of the nuclear detector heads ( ) within the system includes a variable radiation shield ( ) disposed adjacent a radiation receiving face on the detector head. The diagnostic imaging system may be operated in a fluoroscopic/radiographic mode in which an isocentric x-ray beam strikes the center of the detector surface or in a volume imaging mode.

Volume cone beam acquisition on a nuclear spect system using a digital flat panel

A diagnostic imaging system with a C-arm ( ) for supporting an x-ray source ( ) and a flat panel image receptor ( ). The C-arm further including a coupler ( ) that permits the C-arm ( ) to be removably attached to different ceiling-mounted support structures ( ), and to a mobile cart ( ) for mobile C-arm imaging applications. A transport cart ( ) is provided to transport the C-arm ( ) from a first operating room to a second operating room. A mobile equipment cart ( ) can accompany the transport cart ( ). Alternately, a central control facility ( ) can provide command and control signals for the C-arm.

Ceiling mounted, transportable, surgical C-arm with flat panel image receptor

A frame (A) of a diagnostic imaging device such as a CT scanner or an MRI device has a bore defining a patient examination region ( ). A first x-ray source (B) is mounted to a frame (C) for rotation around the examination region ( ). An arc of first radiation detectors ( ) detects x-rays which have traversed the examination region. A first image reconstruction processor ( ) reconstructs a tomographic image representation from signals generated by the first radiation detectors. A fluoroscopy device (D) is mechanically coupled to the diagnostic scanner for generating and displaying at least substantially real-time fluoroscopic projection image representations on a display monitor ( ). A second x-ray source ( ) transmits x-rays to an amorphous silicon flat panel radiation detector ( ). A second image reconstruction processor ( ) reconstructs the fluoroscopic projection image representations from signals generated by the flat panel radiation detector ( ). A C-arm ( ) supports the second x-ray source ( ) and the flat panel radiation detector ( ) in a plane offset from a plane of the C-arm. A movable mounting structure (E) is mechanically connected with the gantry (A) and the C-arm ( ) to move the C-arm between a stored position and an operating position adjacent the bore.

Fluoro-assist feature for a diagnostic imaging device

A penetrating radiation source (,) is disposed on one side of a object (,) which is on a object support (,). A flat panel radiation detector (,) is stationarily disposed on the opposite side of the object (,) than the source (,). A moving system (,) moves the source (,) with respect to the object (,). In each position (X,, Y,, Z,) of the source (,) a center ray of the x-ray beam strikes the detector (,) at a corresponding location (x,, y,, 0). For each position (X,, Y,, Z,) of the source (,), the image (x,, y,, 0) of an object located on a focal plane offsets by a vector displacement (D,) relative to a reference position (x,, y,, z,) of the image when the source is at (X,, Y,, Z,). A processor (,) shifts and interpolates each view by the different vector displacements corresponding to each of the focal planes (L,, L,, . . . ) and integrates the images to generate a series of slice image representations which are stored in a volume image memory (,). In this manner, by adjusting the view offset by an amount corresponding to each of the focal planes, (L,, L,, . . . ) the same data set is used to generate all of the slices of the resultant volume image.

2D and 3D tomographic X-ray imaging using flat panel detectors

An object (,) is positioned on an object support (,). A radiation source (,) projects a beam of radiation through a region of interest (,) of the object. A plurality of focal planes (F,, F,, . . . , F,) mark the center of selected slice images through the region of interest. A gantry (,) rotates the radiation source (,) around a circular trajectory (,) as an encoder (,) monitors a radius (r) of the trajectory and an angular position (&phgr;) of the radiation source (,) around the trajectory (,). A look-up table (,) is addressed with the selected focal plane(s) (F,, F,, . . . , F,) and (r, &phgr;) to generate a correction or shift value (S,, . . . , S,.) for each selected focal plane (F,, F,, . . . , F,). A flat panel detector (,) is read out a plurality of times to generate a plurality of electronic data views as the radiation source rotates. Each view is corrected with a corresponding correction or shift value and integrated in a summation circuit (,) with preceding views to generate an image representation of the slice(s) through the selected focal plane(s) (F,, F,, . . . , F,) or a 3D volume. The slice image or 3D volume image representation is converted into a human-readable display (,) substantially in real-time, e.g., each time a preselected number of views has been summed.

Real-time tomographic system with flat panel detectors

A frame (A) of a diagnostic imaging device such as a CT scanner or an MRI device has a bore defining a patient examination region (12). A first x-ray source (B) is mounted to a frame (C) for rotation around the examination region (12). An arc of first radiation detectors (14) detects x-rays which have traversed the examination region. A first image reconstruction processor (18) reconstructs a tomographic image representation from signals generated by the first radiation detectors. A fluoroscopy device (D) is mechanically coupled to the diagnostic scanner for generating and displaying at least substantially real-time fluoroscopic projection image representations on a display monitor (60). A second x-ray source (32) transmits x-rays to an amorphous silicon flat panel radiation detector (36). A second image reconstruction processor (58) reconstructs the fluoroscopic projection image representations from signals generated by the flat panel radiation detector (36). A C-arm (30) supports the second x-ray source (32) and the flat panel radiation detector (36) in a plane offset from a plane of the C-arm. A movable mounting structure (E) is mechanically connected with the gantry (A) and the C-arm (30) to move the C-arm between a stored position and an operating position adjacent the bore.

A TV camera (22) generates a low level video signal which represents a sensed image pattern from an image intensifier (18). A preamplifier circuit (24) boosts the low level video signal. The preamplifier is selectively switched between feedback paths (74,76) to select the gain of the preamplifier, and between various filter paths (84,88) to select the bandwidth. Various display processing components such as a digital acquisition system (42) and video tape or video disc recorder (44) are provided to process video signals from the preamplifier circuit. A monitor (26) containing circuitry to generate synchronization signals, to adjust brightness, to adjust images aspect ratio, and to adjust image resolution is provided to convert the video signals into a man readable display. A video switch (40) selectively routes the video signals from the preamplifier to one of the display processing components and from these components to the monitor. The route, the gain, and the bandwidth are controlled by input from a console (30).

Dual bandwidth/gain video preamplifier

A patient (12) is irradiated with x-rays (10) from an x-ray tube (A). X-rays that have passed through a region of interest of the patient are converted to a light image by a phosphor screen (14) on the dome shaped input face (16) of an image intensifier (B). The dome shaped input face causes the output optical image (20) of the image intensifier to be distorted with pin cushion distortion. The sweep pattern of the electron beam of a video pick up tube (24) of a video camera (C) is controlled by deflection plates (26a, 26b, 26c, 26d). A sweep control circuit (D) alters the sweep pattern such that electronic image representations generated by the video camera are distorted in a manner that is complementary to and cancels the image intensifier tube distortion. In this manner, the two distortions cancel and a man-readable image (28) displayed on a video monitor (22) is substantially distortion-free. The sweep control circuit alters conventional vertical sweep control voltage ramps (V) and horizontal control voltage ramps (H) by adding third order, parabolic terms:

Geometric distortion-free image intensifier system

Improved apparatus, circuitry and method is disclosed for control of a television camera in a radiographic imaging system. The system includes a radiation source, an image intensifier tube and several associated components for acquiring analog radiation representing images in one or more of several prime analog study modes. The analog acquisition components include any one or a combination of a cine camera, a spot film camera and a spot film device. Radiation is directed from the source through a subject to the intensifier tube input and to selected analog acquisition components. As the analog images are acquired, a television camera views the image tube output to produce another image, by way of a monitor, in verification that the radiation exposure is of a character suitable for the selected analog image acquisition mode. Sets of representations of camera operating parameter value decisions are stored in non-volatile random access memory circuitry coupled to the camera. Each set of representations corresponds to a different analog study mode, or combination of modes. Means is provided for selection of one or a combination of analog study modes. In response to that selection, the corresponding set of camera operating parameter decision respresentations is applied to the camera, in order to optimize camera performance for the particular x-ray mode, or combination of modes, which has been selected. In another embodiment, apparatus and circuitry is provided for suppressing the camera video signal in response to a selection of a predetermined video camera scan rate, while maintaining transmission of synchronization signals from the camera to the monitor.

Television camera control in radiation imaging

A radiographic imaging system and method is disclosed having improved monitor control for enhancing the flexibility of a monitor so that one monitor can perform optimally under several system operating modes. The monitor automically detects the line rate most suitable for producing an image in the selected mode. Brightness compensation is accomplished as a function of the scan line rate at which the monitor is operating. Aspect ratio of the monitor produced image is also adjusted automatically in accordance with the operating mode selected. The system incorporates monitor brightness adjustment as a function of aspect ratio as well. Where the system incorporates a video tape or disk recorder, a time constant of the monitor is adjusted to optimize the monitor's compatibility with the video data output from the recorder in response to the selection of an operating mode wherein the recorder feeds the monitor with video information.

Radiation imaging monitor control improvement

An x-ray imaging system incorporating a television imaging chain is disclosed. The system includes automatic gain control circuitry, operable upon the video signal produced by the camera of the television imaging chain. The gain control circuitry affords automatic gain control capability for increasing the video gain in response to an undesired decrease in video output signal level. The gain control circuitry, however, is constrained in that it includes circuitry for establishing a minimum video gain which is always maintained during a study, irrespective of increases in brightness of an overall sample window area of the image, which could otherwise cause undesirable darkening of areas of interest in the image when the sample window also includes uninteresting structure which happens to exhibit a bright field.

Radiation imaging automatic gain control

An x-ray tube is enclosed in a housing 14, with a detachable x-ray cone 22 having an outward extending flange member 42, a cone holder 18 for receiving the flange member 42, a latch button 50 projecting from the holder for selectively releasing the cone 22 from the holder 18, and a safety plate assembly 26. The safety plate assembly is mounted between the cone holder and the housing 14 and has first and second tabs 28 which project from a periphery of a planar portion 30 of the safety plate substantially at right angles therewith. Each tab 28 has a projection 34 that is directed inward toward the other end generally at right angles with the tabs whereby a resting place is provided for the released cone 22 until the cone is manually removed.

X-ray cone safety plate for x-ray system

A medical diagnostic television imaging system is disclosed having an x-ray source, an image intensifier tube and a video camera positioned to view the output face of the image tube. A monitor is coupled to receive video and synchronization signals from the camera. Means is associated with the video camera for controlling the camera to scan at a selected one of a plurality of scan rate formats. Circuitry is provided for suppressing the delivery of video to the monitor in response to the selection of at least one of the plurality of scan rates. During video suppression, transmission of synchronization signals to the monitor continues.

Improved apparatus, circuitry and method is disclosed for control of a television camera in a radiographic imaging system. The system includes a radiation source, an image intensifier tube and several associated components for acquiring analog radiation representing images in one or more of several prime analog study modes. The analog acquisition components include any one or a combination of a cine camera, a spot film camera and a spot film device. Radiation is directed from the source through a subject to the intensifier tube input and to selected analog acquisition components. As the analog images are acquired, a television camera views the image tube output to produce another image, by way of a monitor, in verification that the radiation exposure is of a character suitable for the selected analog image acquisition mode. Sets of representations of camera operating parameter value decisions are stored in non-volatile random access memory circuitry coupled to the camera. Each set of representations corresponds to a different analog study mode, or combination of modes. Means is provided for selection of one or a combination of analog study modes. In response to that selection, the corresponding set of camera operating parameter decision representations is applied to the camera, in order to optimize camera performance for the particular x-ray mode, or combination of modes, which has been selected. In another embodiment, apparatus and circuitry is provided for suppressing the camera video signal in response to a selection of a predetermined video camera scan rate, while maintaining transmission of synchronization signals from the camera to the monitor.

Growing community of inventors

Mentor, OH, United States of America

Leonard F Plut