Abstract:
A detector array (112) includes at least one detector pixel (306) with a cavity (400) that defines a three dimensional volume. A surface of the cavity includes at least two photosensitive regions and a non-photosensitive region there between, defining at least two sub-pixels (306i, 3062) which detect light photons traversing within the three dimensional cavity and produce respective signals indicative thereof. The detector array further includes a scintillator (302), including a first sub-portion that is located in the cavity and which emits the light photons in response to absorbing x-ray photons. Light photons emitted by the first sub-portion are detected by both of the at least two sub-pixels
Abstract:
An imaging system (300) includes a detector array (314) with direct conversion detector pixels that detect radiation traversing an examination region of the imaging system and generate a signal indicative of the detected radiation, a pulse shaper (316) configured to alternatively process the signal indicative of detected radiation generated by the detector array or a set of test pulses having different and known heights that correspond to different and known energy levels and to generate output pulses having heights indicative of the energy of the processed detected radiation or set of test pulses, and a thresholds adjuster (330) configured to analyze the heights of the output pulses corresponding to the set of test pulses in connection with the heights of set of test pulses and a set of predetermined fixed energy thresholds and generate a threshold adjustment signal indicative of a baseline based on a result of the analysis.
Abstract:
An ECG electrode is provided which can be placed within the direct path of x-rays during an imaging scan without inducing an x-ray induced erroneous current. The ECG electrode has a support element with a conductive post on one side electrically connected to a conductive plate on the other side. A dissipative anti-static element in or near the ECG electrode dissipates static electricity which forms on the surfaces of the insulating components in the ECG electrode. The dissipative anti-static element may be, for example, a slightly conductive property of the bulk material used to make the insulating material, or a conductive coating added to the insulating material surfaces. The dissipative anti-static element may also be incorporated in the clamp attached to the conductive post. In a further embodiment, an ion blower aimed at the ECG electrode may be used to remove static electricity.
Abstract:
A detector array (112) includes at least one detector pixel (306) with a cavity (400) that defines a three dimensional volume. A surface of the cavity includes at least two photosensitive regions and a non-photosensitive region there between, defining at least two sub-pixels (306i, 3062) which detect light photons traversing within the three dimensional cavity and produce respective signals indicative thereof. The detector array further includes a scintillator (302), including a first sub-portion that is located in the cavity and which emits the light photons in response to absorbing x-ray photons. Light photons emitted by the first sub-portion are detected by both of the at least two sub-pixels
Abstract:
An imaging apparatus (400) includes a detector array (412) with at least one detector tile (418). The detector tile includes a photosensor array (422) with a two dimensional array of individual photosensitive detector pixels (424) located within a non-photosensitive area (426). The imaging apparatus also includes readout electronics (432) coupled to the photosensor array and including individual readout channel wells (602, 604) corresponding to the individual detector pixels. The imaging apparatus also includes an anti-aliasing filter (800) for a detector pixel that is located in at least one of a region of the photosensor array corresponding to the detector pixel or a region of the readout electronics corresponding to the detector pixel.
Abstract:
A method includes obtaining a photosensor substrate (236) having two opposing major surfaces. One of the two opposing major surfaces includes at least one photosensor row (230) of at least one photosensor element (232, 234), and the obtained photosensor substrate has a thickness equal to or greater than one hundred microns. The method further includes optically coupling a scintillator array (310) to the photosensor substrate. The scintillator array includes at least one complementary scintillator row (224) of at least one complementary scintillator element (226, 228), and the at least one complementary scintillator row is optically coupled to the at least one photosensor row (230) and the at least one complementary scintillator element is optically coupled to the at least one photosensor element. The method further includes thinning the photosensor substrate optically coupled to the scintillator producing a thinned photosensor substrate that is optically coupled to the scintillator and that has a thickness on the order of less than one hundred microns.
Abstract:
An imaging apparatus (400) includes a detector array (412) with at least one detector tile (418). The detector tile includes a photosensor array (422) with a two dimensional array of individual photosensitive detector pixels (424) located within a non-photosensitive area (426). The imaging apparatus also includes readout electronics (432) coupled to the photosensor array and including individual readout channel wells (602, 604) corresponding to the individual detector pixels. The imaging apparatus also includes an anti-aliasing filter (800) for a detector pixel that is located in at least one of a region of the photosensor array corresponding to the detector pixel or a region of the readout electronics corresponding to the detector pixel.
Abstract:
A method includes performing a contrast enhanced computed tomography (CT) scan of tissue of interest of a subject, with an imaging system having a radiation source and a detector array, in which a peak contrast enhancement of the tissue of interest, a full range of motion of the tissue of interest, and an entire volume of interest of the tissue of interest are concurrently imaged during a single rotation of the radiation source and the detector array of the imaging system over an entire or a predetermined sub-portion of a breathing cycle.
Abstract:
An imaging apparatus (400) includes a detector array (412) with at least one detector tile (418). The detector tile includes a photosensor array (422) with a two dimensional array of individual photosensitive detector pixels (424) located within a non-photosensitive area (426) and readout electronics (432) coupled to the photosensor array. The readout electronics includes individual analog readout channel wells (602, 604) corresponding to the individual detector pixels, wherein an analog readout channel well electrically isolates analog electrical components therein from analog electrical components in other analog readout channel wells. Decoupling circuitry optionally is located in at least one of metal layers of the individual analog readout channels or in the individual analog readout channel wells.
Abstract:
An imaging apparatus (400) includes a detector array (412) with at least one detector tile (418). The detector tile includes a photosensor array (422) with a two dimensional array of individual photosensitive detector pixels (424) located within a non-photosensitive area (426) and readout electronics (432) coupled to the photosensor array. The readout electronics includes individual analog readout channel wells (602, 604) corresponding to the individual detector pixels, wherein an analog readout channel well electrically isolates analog electrical components therein from analog electrical components in other analog readout channel wells. Decoupling circuitry optionally is located in at least one of metal layers of the individual analog readout channels or in the individual analog readout channel wells.