Abstract: In one embodiment, the present invention includes a system including a CT system, an NM system, a NM bed operatively coupled to the NM system, and a CT bed operatively coupled to the CT system, with the CT bed coupled to the NM bed when the CT system is used for dual mode imaging.

Abstract: An apparatus and method for the automated positioning of a collimator exchange assembly with a gamma camera system is described. A collimator exchange assembly is coupled to a base. During operation of the gamma camera system, the exchange assembly is positioned to the side of the gamma camera system. Prior to transferring collimators between the exchange assembly and the detector heads of the gamma camera system, the exchange assembly rotates into close proximity with the gamma camera system to allow the transfer of collimators between the exchange assembly and the gamma camera system. Once the collimators have been transferred, the exchange assembly then rotates back to the side of the gamma camera system such that the exchange assembly does not interfere with the gamma camera system during the gamma camera study.

Abstract: A seat cushion cover (20) in combination with a sport seat cushion (22) includes a rectangular pocket (24) defined by a fabric upper panel (26) and a lower panel (28). The upper and lower panels (26, 28) are generally parallel to one another and are joined by side panels (30a,b) and an end panel (32). A fabric flap (34) extends from the upper panel (26). The flap (34) is adapted to retain the cushion (22) within the pocket (24) and provide for securing the cushion (22) on a stadium seat (54). The flap (34) foldably extends over an opening (33) of the pocket (24) and along a portion of lower panel (28). The flap (34) and the portion of the lower panel (28) are separated by a space for receiving the stadium seat bottom (56). The flap (34) is adjustably secured to the side panels (30a,b) with fasteners (42, 44, 46, 48, 50, 52). A resilient band (36) provides tension to retain the cover (20) on the seat bottom (56) when it is in its raised position.

Abstract: An x-ray tube comprising a first electrode and a second electrode. The first and second electrodes are located in operative relationship with one another to generate x-rays when the electrodes are energized at their respective operating potential. An evacuated envelope encloses the first and second electrodes. The evacuated envelope includes a first envelope wall portion, a second envelope wall portion and an envelope weld member comprising an electrical conductor. The envelope weld member is in electrical communication so as to be at operating potential of one of the first and second electrodes when the x-ray tube is energized. The envelope weld member is adapted for vacuum tight joining to the first envelope wall portion and to the second envelope wall portion. The envelope weld member has an integral corona shield portion.

Abstract: An x-ray tube (20) includes an evacuated envelope (26). Mounted within the evacuated envelope are a cathode (23) and a rotatbly supported anode (30). A rotor (70) is included for rotatably driving the anode. The rotor (70) is electrically insulated from the anode (30) by a disk (76) comprised of an insulating material.

Abstract: The invention relates to an X-ray system/generator in which after the end of an X-ray exposure the grid of th X-ray tube is blocke4d as long as the X-ray exposure is read out from a detector (or as long a film or a PCR is removed from the X-rays). After read out, the grid is released so that the system capacitance may be discharged via the X-ray tube. Thereby over-exposure due to energy stored in the sytem- and cable capacities is avoided (which is a problem especially for thin objects), and the system may be switched from a tube with grid to a tube without grid without problems.

Abstract: An x-ray system 20 includes an x-ray tube insert (24) that has an evacuated envelope (34), an anode assembly (38) and a cathode assembly (40). The anode assembly (38) and the cathode assembly (40) are located in operative relationship to one another within the evacuated envelope (34). A temperature indicating member (100) is located in thermally conductive contact with at least one assembly (38, 40, 66) located in the x-ray tube insert (24). The temperature indicating member (100) has a temperature sensitive characteristic which changes in response to adequate thermal exposure to at least one temperature threshold value.

Abstract: A method for cleaning the interior of a heat exchanger includes connecting the heat exchanger (25a-e) to a fluid supply (26) and fluid delivery system (24). Fluid flow is provided from the fluid supply (26) through the interior of the heat exchanger (25a) in a first direction. The fluid flow is pulsed a predetermined number of times to change the pressure within the heat exchanger. The fluid flow is then pulsed a plurality of times through the heat exchanger in a second direction.

Abstract: A gamma camera includes first and second detectors. The first detector is located beneath a patient receiving surface. The second detector is located above the patient receiving surface. The second detector is movable between operating and retracted positions. The second detector includes a plurality of discrete detector portions, each detector portion having a first radiation sensitive face which faces an examination region and a second radiation sensitive face. The patient receiving surface generates signals indicative of pressure applied to the patient receiving surface. A movable transmission radiation source provides transmission radiation, interactions between the transmission radiation and the second detector generating Compton scattered radiation at least a portion of which is received by the first detector, coincident radiation being used to generate a transmission attenuation map. The gamma camera also includes an ultrasound device.

Abstract: A high voltage low inductance resistor (120) includes a resistor body (122) having a perimeter and a center. A first terminal (126) is located away from the center of the resistor near the perimeter of the body (122). A serpentine resistance element (130) includes a first end (136). A conductive ring (124) is located near the perimeter and circumscribes the serpentine resistance element (130). The ring (124) is electrically connected to the first terminal (126). The first end (136) is electrically connected to the conductive ring (124). A first resistance segment (138a) of the resistance element (130) begins at the first end (136) and extends in a first direction generally around the perimeter of the body (122). An apex (142a) has an input portion (143) and an output portion (145). The apex (142a) redirects the resistance element in a generally opposite direction, the input portion (143) transitioning into the first resistance segment (138a).

Abstract: An x-ray tube apparatus includes a housing defining a chamber and an x-ray tube mounted therein. The x-ray tube includes an envelope defining an evacuated void in which an anode assembly is rotatably mounted to a bearing assembly. The anode assembly interacts with a cathode assembly for the production of x-rays. The bearing assembly includes a cooling channel that is defined within the bearing assembly to direct cooling fluid, such as oil, across an inner surface of the bearing housing. A flow director is located in a fluid input port in the housing and has a fluid input aperture for connecting the flow director to the heat removal system. A cavity is defined by the housing of the flow director and two fluid output apertures are in fluid communication with each other and the fluid input opening. One of the fluid output apertures supplies cooling fluid to the cooling channel in the bearing assembly and the other fluid output aperture supplies cooling fluid to the chamber in the housing.

Abstract: The present invention describes an apparatus for an improved patient support table for use in nuclear medical studies. The table provides regions, such as a slot or hole, where there is lowered radiation attenuation for particular regions of the body. By supporting and aligning the patient with these regions of lowered radiation attenuation, better image quality and/or lowered radiation dosage may be achieved.

Abstract: A system for exchanging and storing collimators for medical imaging devices includes a first frame having a first receptacle and a second frame having a first docking member. A collimator can be attached to and removed from the first receptacle. The first docking member can be positioned adjacent to the first receptacle such that the first docking member can contact the collimator to remove the collimator from the first receptacle. The collimator is coupled to the first docking member while the collimator is removed from the first receptacle.

Abstract: A method of correcting for deadtime and for emission contamination of a transmission scan in a nuclear camera system is provided. The transmission scan is used to correct positron emission tomography (PET) images for attenuation. The camera system includes two detectors and two corresponding single-photon point sources that are collimated to produce fanbeam illumination profiles. A transmission detection window and an emission contamination detection window is defined on each detector. Radiation from each source is scanned axially across the field of view of the corresponding detector in synchronization with the corresponding transmission detection window to acquire transmission projection data. The emission contamination detection windows are also scanned axially concurrently with, but offset from, the transmission detection windows to acquire emission data.

Abstract: A nuclear medicine imaging system includes the capability to correct for the deadtime, including the capability to correct for spatial variations in deadtime across the imaging surface of a detector. The imaging system includes one or more radiation detectors, each using a large, monolithic scintillation crystal. Each detector has deadtime associated with it. A given detector is used to acquire an energy profile of a patient based on emission radiation. The detector includes a number of timing channels. The energy profile is used to select a zone influence map indicating the extent of spatial overlap in response between the various timing channels. Emission data of the patient is then acquired during an emission scan. During acquisition of the emission data, a rate meter assigned to each timing channel samples the number of counts associated with each timing channel to acquire deadtime data.

Abstract: In a magnetic resonance imaging apparatus in which excitation pulses are applied to a restricted region 5 of a magnetic resonance imaging magnet bore, in which the field is uniform, and the data samples collected are Fourier transformed to form a volumetric image of the restricted region, a motor 6 continuously moves a patient couch 3 so that a region of interest passes through the region of good field, and the data samples collected are corrected to compensate for the motion so that a volumetric image is formed of greater length than that of the restricted region.

Abstract: An x-ray tube (20) comprising a cathode (23) and an anode (24) in operative relationship with the cathode (23). The anode (24) is mounted on a stem (32). The x-ray tube includes at least one bearing (58) rotatably receiving the stem (32). The at least one bearing (58) has an outer bearing race (66) in an outer race member, an inner bearing race (62) and a plurality of bearing members (64) operatively disposed between the inner and outer bearing races. The x-ray tube (20) also includes an evacuated envelope (78) which encloses the tube components and receives the outer race member of the at least one bearing (58) in thermally conductive contact along an inner surface (79).

Abstract: Magnetic resonance imaging apparatus uses magnetic field gradients X, Y, Z to spatially encode the magnetic signals arising from a patient on a couch 2 in bore 1 of a main magnet. Thermal stresses arising from aggressive gradients during multiple acquisitions result in imperfectly repeated gradients and resulting image artefacts. The invention uses a probe 4 provided with a gradient coil set similar to that for imaging, and fed by currents derived from the imaging gradient coils, connected so as to produce an opposing gradient surrounding an MR active substance in the probe. This enables a probe with a sufficiently large amount of MR active substance to produce a useful signal to be used to monitor the gradient, while overcoming the de-phasing problem. which would otherwise occur. Closed loop control of gradients thereby becomes possible.

Abstract: An RF coil structure for intra-cavity use includes a pair of conductors (7, 8) separated by a support such as a web (9) which come together at positions separated along the length of the coil structure such as (A, B). Previous coils have included two parallel conductors. If the conductors (7) and (8) were parallel, while the structure could be flexed transverse to the plane of the web (9) about the arrow (10), it could not be flexed in the plane of the web (9) about arrows (12, 13). Because the conductors come together at points (A) and (B), it can be so flexed. A second coil may be provided including conductors (4, 5) and flexing about the same points as for the first coil is still possible because the points of closest approach for one pair come between those for the other pair.

Abstract: A patient bed (1) of an MR imaging apparatus is provided with a tube (17) through which pre-polarised fluid can be injected into a patient in order to improve contrast when imaging veins, arteries or other vessels in the body. Fluid is delivered from pump (2) into a high field polarising magnet (3) and along a tube (4) to the patient. Valve (5) is provided so that fluid in the tube (4) downstream of the pre-polarised fluid can be discarded rather than being injected in the patient, and is associated with a reservoir into which the fluid to be discarded and the pre-polarised fluid can be rapidly injected. Then, when the pre-polarised fluid is injected into the patient, its magnetisation has not deteriorated by as much as it would have done if the tube (4) had been directly connected into the patient.