Abstract: Saturation in at least one saturated ray is in a method including identifying a saturated ray corresponding to a first ray of a radiation source received at a radiation detector after passing through a reference point during a current view of the radiation detector, identifying at least one non-saturated ray corresponding to a second ray of the radiation source received at the radiation detector, and responsive to the identifying, adjusting a value for the saturated ray based on a value of the at least one non-saturated ray. The non-saturated ray can be a ray from an adjacent view of a current rotation, an adjacent view of a previous or subsequent rotation, or a conjugate ray. Methods of selecting a gain level to avoid saturation are also disclosed.

Abstract: A one-dimensional multi-element photo detector includes a photodiode array with a first upper row of photodiode pixels and a second lower row of photodiode pixels. The photodiode array is part of the photo detector. A scintillator array includes a first upper row and a second lower row of scintillator pixels. The first upper and second lower rows of scintillator pixels are respectively optically coupled to the first upper and second lower rows of photodiode pixels. The photo detector also includes readout electronics, which are also part of the photo detector. Electrical traces interconnect the photodiode pixels and the readout electronics.

Abstract: A one-dimensional multi-element photo detector includes a photodiode array with a first upper row of photodiode pixels and a second lower row of photodiode pixels. The photodiode array is part of the photo detector. A scintillator array includes a first upper row and a second lower row of scintillator pixels. The first upper and second lower rows of scintillator pixels are respectively optically coupled to the first upper and second lower rows of photodiode pixels. The photo detector also includes readout electronics, which are also part of the photo detector. Electrical traces interconnect the photodiode pixels and the readout electronics.

Abstract: A one-dimensional multi-element photo detector (120) includes a photodiode array (122) with a first upper row of photodiode pixels and a second lower row of photodiode pixels. The photodiode array (122) is part of the photo detector (120). A scintillator array (126) includes a first upper row and a second lower row of scintillator pixels. The first upper and second lower rows of scintillator pixels are respectively optically coupled to the first upper and second lower rows of photodiode pixels. The photo detector (120) also includes readout electronics (124), which are also part of the photo detector (120). Electrical traces (512) interconnect the photodiode pixels and the readout electronics (124).

Abstract: A detector tile (116) of an imaging system (100) includes a photosensor array (204) and electronics (208) electrically coupled to the photosensor array (204), wherein the electronics includes a dose determiner (402) that determines a deposited dose for the detector tile (116) and generates a signal indicative thereof. In one non-limiting instance, this signal is utilized to correct parameters such as gain and thermal coefficients, which may vary with radiation dose.

Abstract: An imaging detector includes a scintillator array (202), a photosensor array (204) optically coupled to the scintillator array (202), a current-to-frequency (I/F) converter (314), and logic (312). The I/F converter (314) includes an integrator (302) and a comparator (310), and converts, during a current integration period, charge output by the photosensor array (204) into a digital signal having a frequency indicative of the charge. The logic (312) sets a gain of the integrator (302) for a next integration period based on the digital signal for the current integration period. In one instance, the gain is increased for the next integration period, relative to the gain for the current integration period, which allows for reducing an amount of bias current injected at an input of the I/F converter (314) to generate a measurable signal in the absence of radiation, which may reduce noise such as shot noise, flicker noise, and/or other noise.

Abstract: A radiation detector module (22) particularly well suited for use in computed tomography (CT) applications includes a scintillator (200), a photodetector array (202), and signal processing electronics (205). The photodetector array (202) includes a semiconductor substrate (208) having a plurality of photodetectors and metalization (210) fabricated on non-illuminated side of the substrate (208). The metalization routes electrical signals between the photodetectors and the signal processing electronics (205) and between the signal processing electronics (205) and an electrical connector (209).

Abstract: An imaging detector includes processing electronics with a thermal coefficient about equal to a negative of a summation of thermal coefficients of a photosensor array and a scintillator array of the detector. In another instance, the imaging detector includes an A/D converter that alternately converts first charge corresponding to impinging radiation into a first signal and second charge corresponding to decaying charge into a second signal and a logic unit that corrects the first signal based on the second signal. In another instance, the imaging detector includes an A/D converter, an integrator offset voltage signal determiner, and a logic unit, wherein the determiner induces an electrical current via an offset voltage, the A/D converter measures the current, and the logic unit calculates a resistance of the photosensor array based on the reference voltage and the measured current.

Abstract: An imaging detector includes processing electronics with a thermal coefficient about equal to a negative of a summation of thermal coefficients of a photosensor array and a scintillator array of the detector. In another instance, the imaging detector includes an A/D converter that alternately converts first charge corresponding to impinging radiation into a first signal and second charge corresponding to decaying charge into a second signal and a logic unit that corrects the first signal based on the second signal. In another instance, the imaging detector includes an A/D converter, an integrator offset voltage signal determiner, and a logic unit, wherein the determiner induces an electrical current via an offset voltage, the A/D converter measures the current, and the logic unit calculates a resistance of the photosensor array based on the reference voltage and the measured current.

Abstract: An imaging system (100) includes a radiation source (108) that emits radiation that traverses an examination region (106) and a detection system (114) that detects radiation that traverses the examination region (106) and generates a signal indicative thereof. The detection system (114) includes a first detector array (1141-114N) and a second detector array (1141-114N). The first and second detector arrays (1141-114N) are separately distinct detector arrays and at least one of the detector arrays (1141-114N) is moveable with respect to the radiation beam. A reconstructor (116) reconstructs the signal and generates volumetric image data indicative thereof.

Abstract: An imaging detector includes processing electronics (208) with a thermal coefficient about equal to a negative of a summation of thermal coefficients of a photosensor array (204) and a scintillator array (202) of the detector. In another instance, the imaging detector includes an A/D converter (302) that alternately converts first charge corresponding to impinging radiation into a first signal and second charge corresponding to decaying charge into a second signal and a logic unit (308) that corrects the first signal based on the second signal. In another instance, the imaging detector includes an A/D converter (302), an integrator offset voltage signal determiner (318), and a logic unit (308), wherein the determiner (318) induces an electrical current via an offset voltage, the A/D converter (302) measures the current, and the logic unit (308) calculates a resistance of the photosensor array (204) based on the reference voltage and the measured current.

Abstract: An imaging detector includes a radiation sensitive region having first and second opposing sides. One of the first or second sides senses impinging radiation. The detector further includes electronics located on the other of the first or second sides of the radiation sensitive region. The electronics includes a thermal controller that regulates a temperature of the imaging detector.

Abstract: A detector tile (116) of an imaging system (100) includes a photosensor array (204) and electronics (208) electrically coupled to the photosensor array (204), wherein the electronics includes a dose determiner (402) that determines a deposited dose for the detector tile (116) and generates a signal indicative thereof. In one non-limiting instance, this signal is utilized to correct parameters such as gain and thermal coefficients, which may vary with radiation dose.

Abstract: An imaging detector includes a scintillator array (202), a photosensor array (204) optically coupled to the scintillator array (202), a current-to-frequency (I/F) converter (314), and logic (312). The I/F converter (314) includes an integrator (302) and a comparator (310), and converts, during a current integration period, charge output by the photosensor array (204) into a digital signal having a frequency indicative of the charge. The logic (312) sets a gain of the integrator (302) for a next integration period based on the digital signal for the current integration period. In one instance, the gain is increased for the next integration period, relative to the gain for the current integration period, which allows for reducing an amount of bias current injected at an input of the I/F converter (314) to generate a measurable signal in the absence of radiation, which may reduce noise such as shot noise, flicker noise, and/or other noise.

Abstract: An imaging system (100) includes a radiation source (108) that emits radiation that traverses an examination region (106) and a detection system (114) that detects radiation that traverses the examination region (106) and generates a signal indicative thereof. The detection system (114) includes a first detector array (1141-114N) and a second detector array (1141-114N). The first and second detector arrays (1141-114N) are separately distinct detector arrays and at least one of the detector arrays (1141-114N) is moveable with respect to the radiation beam. A reconstructor (116) reconstructs the signal and generates volumetric image data indicative thereof.

Abstract: An imaging detector includes processing electronics with a thermal coefficient about equal to a negative of a summation of thermal coefficients of a photosensor array and a scintillator array of the detector. In another instance, the imaging detector includes an A/D converter that alternately converts first charge corresponding to impinging radiation into a first signal and second charge corresponding to decaying charge into a second signal and a logic unit that corrects the first signal based on the second signal. In another instance, the imaging detector includes an A/D converter, an integrator offset voltage signal determiner, and a logic unit, wherein the determiner induces an electrical current via an off-set voltage, the A/D converter measures the current, and the logic unit calculates a resistance of the photosensor array based on the reference voltage and the measured current.

Abstract: A one-dimensional multi-element photo detector (120) includes a photodiode array (122) with a first upper row of photodiode pixels and a second lower row of photodiode pixels. The photodiode array (122) is part of the photo detector (120). A scintillator array (126) includes a first upper row and a second lower row of scintillator pixels. The first upper and second lower rows of scintillator pixels are respectively optically coupled to the first upper and second lower rows of photodiode pixels. The photo detector (120) also includes readout electronics (124), which are also part of the photo detector (120). Electrical traces (512) interconnect the photodiode pixels and the readout electronics (124).

Abstract: An imaging detector includes a radiation sensitive region having first and second opposing sides. One of the first or second sides senses impinging radiation. The detector further includes electronics located on the other of the first or second sides of the radiation sensitive region. The electronics includes a thermal controller that regulates a temperature of the imaging detector.

Abstract: A radiographic imaging apparatus (10) comprises a primary radiation source (14) which projects a beam of radiation into an examination region (16). A detector (18) converts detected radiation passing through the examination region (16) into electrical detector signals representative of the detected radiation. The detector (18) has at least one temporally changing characteristic such as an offset B(t) or gain A(t). A grid pulse means (64) turns the primary radiation source (14) ON and OFF at a rate between 1000 and 5000 pulses per second, such that at least the offset B(t) is re-measured between 1000 and 5000 times per second and corrected a plurality of times during generation of the detector signals. The gain A(t) is measured by pulsing a second pulsed source (86, 100, 138) of a constant intensity (XRef) with a second pulse means (88). The gain A(t) is re-measured and corrected a plurality of times per second during generation of the detector signals.

Abstract: A computed tomography method includes rotating an electron beam along an anode (104) disposed about an examination region (112) for a plurality of sampling intervals in which x-ray projections are sampled. The electron beam is swept during each sampling interval to generate a plurality of successive focal spots at different focal spot locations during each sampling interval, wherein the focal spots generated in a given sampling interval include a sub-set of the focal spots generated in a previous sampling interval. The x-ray projections radiated from each of the plurality of focal spots is sampled during each sampling interval. The resulting data is reconstructed to generate volumetric image data.