Abstract: A detection layer (416) for a radiation detector (400) includes a porous silicon membrane (418). The porous silicon membrane includes silicon (419) with a first side (430) and a second opposing side (432), a plurality of pores (420) extending entirely through the silicon from the first side to the second opposing side, each including shared walls (426), at least one protrusion of silicon (424) protruding out and extending from the first side a distance (504, 604, 704). The porous silicon membrane further includes a plurality of radiation sensitive quantum dots (422) in the pores and a quantum dot layer disposed on the first side and having a surface (434) and a thickness (506, 606, 706), wherein the thickness is greater than the distance.

Abstract: A radiation detector (100) includes a photovoltaic layer (102) with first and second opposing sides. The photovoltaic layer is configured to absorb first radiation at the first side and produce electrical charge. The detector further includes a porous silicon quantum dot layer (104) disposed at the second side of the photovoltaic layer and configured to receive second radiation and convert the received second radiation into an electrical signal indicative of an energy level of the received second radiation. The detector further includes an acquisition and communication layer (106) disposed adjacent to the porous silicon quantum dot layer and configured to receive the electrical signal and transmit the electrical signal to a device remote from the radiation detector.

Abstract: An imaging module (114) of an imaging system comprises a porous silicon membrane (116) with a first side (208), a contact side (210) opposite the first side, columns of silicon (212) configured to extend from the first side to the contact side, and columnar holes (214, 502) interlaced with the columns of silicon and configured to extend from the first side to the contact side. The imaging module further includes quantum dots (118) in the columnar holes. The imaging module further includes a metal pad (120) electrically coupled to the columns of silicon of the porous silicon membrane. The quantum dots in the columnar holes are electrically insulated from the metal pad. The imaging module further includes a substrate (122) with an electrically conductive pad (204) in electrical communication with the metal pad that defines a pixel.

Abstract: A detector array (112) includes a detector pixel (206). The detector pixel includes a three dimensional cavity (304 and 306; 432 and 404) having walls (308/602 and 316; 434 and 406/502) that include active regions, which detect light photons traversing within the three dimensional cavity and produce respective electrical signals indicative thereof. The detector pixel further includes a first scintillator (320; 410) disposed in the three dimensional cavity adjacent to a bottom (320; 416) of the at least one detector pixel. The detector pixel further includes a second scintillator (326; 444) disposed in the three dimensional cavity on top of the first scintillator, wherein the first and second scintillators emits the light photons in response to absorbing x-ray photons. At least one of the walls is vertically oriented with respect to detector pixel, maximizing contact area between a corresponding active region and one of the first or second scintillators.

Abstract: A subject support includes a fixed portion and a moveable portion coupled to the fixed portion and configured to move along at least one axis relative to the fixed portion, and the coupling includes one or more points of friction that move during movement of the moveable portion and which wear due to at least movement by the moveable portion. The moveable portion receives and supports at least one of an object or a subject during an imaging procedure with an imaging device. One or more inertial measurement units (IMUs) are affixed to or embedded in the moveable portion that directly measure acceleration of translation of the moveable portion along one or more axes.

Abstract: A static charge filter (522) removes static charge in a cardiac electrical signal. The static charge filter includes a first amplifier (608) configured to amplify an input signal, which includes the cardiac electrical signal and static charge from an electrode, which is in a path of an X-ray beam. The static charge filter further includes a limiter (614) configured to limit a maximum voltage of the signal based on a predetermined clamping threshold, producing a voltage clamped signal. The static charge filter further includes a filter (616) configured to filter high frequency components of the voltage clamped signal, producing a filtered signal. The static charge filter further includes a second amplifier (620) configured to scale an amplitude of the filtered signal so that cardiac electrical signal in an output signal has a same voltage level as a voltage level of the cardiac electrical signal in the input signal.

Abstract: A scintillator layer (206) includes a plurality of scintillator pixels (337), walls of non-scintillation material (336) surrounding each of the plurality of scintillator pixels, and at least one electrically conductive interconnect (224) for a pixel, wherein the at least one electrically conductive interconnect extends within a wall of the pixel along an entire depth of the wall. A multi-energy detector array (114) includes a detector tile (116) with an upper scintillator layer (202), an upper photosensor (204) optically coupled to the upper scintillator layer, a lower scintillator layer (206) electrically coupled to the upper photosensor, and a lower photodetector (208) optically and electrically coupled to the lower scintillator layer.

Abstract: A radiation detector (100) includes a photovoltaic layer (102) with first and second opposing sides. The photovoltaic layer is configured to absorb first radiation at the first side and produce electrical charge. The detector further includes a porous silicon quantum dot layer (104) disposed at the second side of the photovoltaic layer and configured to receive second radiation and convert the received second radiation into an electrical signal indicative of an energy level of the received second radiation. The detector further includes an acquisition and communication layer (106) disposed adjacent to the porous silicon quantum dot layer and configured to receive the electrical signal and transmit the electrical signal to a device remote from the radiation detector.

Abstract: A radiation detector array (112) of an imaging system (100) comprises a plurality of detector modules (114). Each of the plurality of detector modules includes a plurality of detector pixel (116). Each of the plurality of detector pixels includes an integral pixel border (202, 204, 206, 208) and a direct conversion active area within the integral pixel border. A method comprises receiving radiation with a nano-material detector pixel that includes an integral pixel border, generating, with the detector pixel, a signal indicative of an energy of the received radiation, while reducing pixel signal crosstalk, and reconstructing the signal to construct an image.

Abstract: A module assembly device (402) is configured for assembling a module assembly (114) for a detector array (110) of an imaging system (100). The module assembly device includes a base (400) having a long axis (401). The module assembly device further includes a first surface (406) of the base and side walls (408) protruding perpendicular up from the first surface and extending in a direction of the long axis along at least two sides of the base. The first surface and side walls form a recess (404) configured to receive the module substrate on the surface and within the side walls. The module assembly device further includes protrusions (403) protruding from the side walls in a direction of the side walls. The protrusions and side walls interface forming a ledge which serves as a photo-detector array tile support (410) configured to receive the photo-detector array tile (118) over the ASIC and the module substrate.

Abstract: A subject support (12) includes a fixed portion (22) and a moveable portion (11) coupled to the fixed portion and configured to move along at least one axis relative to the fixed portion (22), and the coupling includes one or more points of friction (32) that move during movement of the moveable portion (11) and which wear due to at least movement by the moveable portion (11). The moveable portion (11) receives and supports at least one of an object or a subject during an imaging procedure with an imaging device (18). One or more inertial measurement units (IMUs) (50) are affixed to or embedded in the moveable portion (11) that directly measure acceleration of translation of the moveable portion (11) along one or more axes.

Abstract: A scintillator layer (206) includes a plurality of scintillator pixels (337), walls of non-scintillation material (336) surrounding each of the plurality of scintillator pixels, and at least one electrically conductive interconnect (224) for a pixel, wherein the at least one electrically conductive interconnect extends within a wall of the pixel along an entire depth of the wall. A multi-energy detector array (114) includes a detector tile (116) with an upper scintillator layer (202), an upper photosensor (204) optically coupled to the upper scintillator layer, a lower scintillator layer (206) electrically coupled to the upper photosensor, and a lower photodetector (208) optically and electrically coupled to the lower scintillator layer.

Abstract: A radiation detection system of an imaging system (100) includes a radiation sensitive detector array (112). The array includes a detector pixel with an optically transparent encapsulate material (114) with one or more particles (116) supporting one or more different scintillation materials (118), wherein each scintillation material is in the form of a nanometer to micrometer quantum dot. A method includes receiving radiation with a detector pixel, wherein the detector pixel includes an encapsulate with one or more quantum dots, wherein each of the quantum dots includes a scintillation material, generating, with the detector pixel, a signal indicative of the received radiation, and reconstructing the signal to construct an image.

Abstract: A module assembly device (402) is configured for assembling a module assembly (114) for a detector array (110) of an imaging system (100). The module assembly device includes a base (400) having a long axis (401). The module assembly device further includes a first surface (406) of the base and side walls (408) protruding perpendicular up from the first surface and extending in a direction of the long axis along at least two sides of the base. The first surface and side walls form a recess (404) configured to receive the module substrate on the surface and within the side walls. The module assembly device further includes protrusions (403) protruding from the side walls in a direction of the side walls. The protrusions and side walls interface forming a ledge which serves as a photo-detector array tile support (410) configured to receive the photo-detector array tile (118) over the ASIC and the module substrate.

Abstract: A detector array (112) of an imaging system (100) includes a radiation sensitive detector (202/204/206) configured to detect radiation and generates a signal indicative thereof and electronics (208) in electrical communication with the radiation sensitive detector. The electronics include a current-to-frequency converter (300) configured to convert the signal into a pulse train having a frequency indicative of a charge collected during an integration period. The electronics further include a residual charge collection circuit (322) electrically coupled to current-to-frequency converter. The residual charge collection circuit is configured to store charge collected by the integrator for an end portion of the integration period that does not results in a pulse of the pulse train, utilizing much of the electronics already in the current-to-frequency converter electronics.

Abstract: An imaging system (102) includes a detector array (104) with a ring (106) with a first layer (110i) that detects gamma radiation and X-ray radiation and a second layer (110N) that detects only gamma radiation, wherein the first and second layers are concentric closed rings. A method includes detecting gamma radiation with a first layer of a dual layer detector in response to imaging in PET mode, detecting gamma radiation with a second layer of the dual layer detector in response to imaging in PET mode, and generating PET image data with the radiation detected with the first and second layers. The method further includes detecting X-ray radiation with the first layer in response to imaging in CT mode and generating CT image data the radiation detected with the first layer. The method further includes displaying the image data. The imaging system allows a single gantry for both PET/CT imaging.

Abstract: A module assembly device (402) is configured for assembling a module assembly (114) for a detector array (110) of an imaging system (100). The module assembly device includes a base (400) having a long axis (401). The module assembly device further includes a first surface (406) of the base and side walls (408) protruding perpendicular up from the first surface and extending in a direction of the long axis along at least two sides of the base. The first surface and side walls form a recess (404) configured to receive the module substrate on the surface and within the side walls. The module assembly device further includes protrusions (403) protruding from the side walls in a direction of the side walls. The protrusions and side walls interface forming a ledge which serves as a photo-detector array tile support (410) configured to receive the photo-detector array tile (118) over the ASIC and the module substrate.

Abstract: A radiation detector array (112) of an imaging system (100) comprises a plurality of detector modules (114). Each of the plurality of detector modules includes a plurality of detector pixel (116). Each of the plurality of detector pixels includes an integral pixel border (202, 204, 206,208) and a direct conversion active area within the integral pixel border. A method comprises receiving radiation with a nano-material detector pixel that includes an integral pixel border, generating, with the detector pixel, a signal indicative of an energy of the received radiation, while reducing pixel signal crosstalk, and reconstructing the signal to construct an image.

Abstract: A static charge filter (522) removes static charge in a cardiac electrical signal. The static charge filter includes a first amplifier (608) configured to amplify an input signal, which includes the cardiac electrical signal and static charge from an electrode, which is in a path of an X-ray beam. The static charge filter further includes a limiter (614) configured to limit a maximum voltage of the signal based on a predetermined clamping threshold, producing a voltage clamped signal. The static charge filter further includes a filter (616) configured to filter high frequency components of the voltage clamped signal, producing a filtered signal. The static charge filter further includes a second amplifier (620) configured to scale an amplitude of the filtered signal so that cardiac electrical signal in an output signal has a same voltage level as a voltage level of the cardiac electrical signal in the input signal.

Abstract: An imaging system (102) includes a detector array (104) with a ring (106) with a first layer (110i) that detects gamma radiation and X-ray radiation and a second layer (110N) that detects only gamma radiation, wherein the first and second layers are concentric closed rings. A method includes detecting gamma radiation with a first layer of a dual layer detector in response to imaging in PET mode, detecting gamma radiation with a second layer of the dual layer detector in response to imaging in PET mode, and generating PET image data with the radiation detected with the first and second layers. The method further includes detecting X-ray radiation with the first layer in response to imaging in CT mode and generating CT image data the radiation detected with the first layer. The method further includes displaying the image data. The imaging system allows a single gantry for both PET/CT imaging.