Abstract: The present invention relates to a 2,3-dihydro-1H-pyrrolo[3,2-b]pyridine derivative, a preparation method therefor, and an application thereof, and in particular to an EGFR inhibitor having the structure of formula (I), a preparation method therefor, a pharmaceutical composition containing same, a use of same as an EGFR inhibitor, and a use of same in the treatment and/or prevention of cancers, tumors, or metastatic diseases at least partially related to EGFR exon 20 insertion or deletion mutations, especially a use in the treatment of hyperproliferative diseases and dysfunction in cell death induction. The definition of each substituent in formula (I) is the same as that in the description.

Abstract: The present application relates to one-motor-duel-drive synchronous drive device. The drive device includes: a housing, wherein the housing is hollow, a telescopic mechanism is connected to the housing, the telescopic mechanism includes a screw rod, and one end of the screw rod extends into the housing; a transmission mechanism, wherein the transmission mechanism comprises a first transmission component rotatably connected to an inner wall of the housing, a second transmission component is fixedly connected to the screw rod, and the first transmission component and the second transmission component are staggered gears engaged with each other; a linkage lever provided between the housings, wherein two ends of the linkage lever are connected to the first transmission component, respectively; and a drive mechanism configured to act on the linkage lever to rotate the linkage lever.

Abstract: The present invention provides a cup holder. The cup holder includes a cup holder body having a receiving part and a charging assembly. The charging assembly includes a wireless charging module. The wireless charging module is mounted on the cup holder body and configured to charge a smart electronic device. The cup holder can charge the smart electronic devices, thereby improving user experience.

Abstract: Medical detectors and medical imaging devices are provided. In one aspect, a medical detector includes: a photoelectric conversion device, a first crystal array layer disposed over the photoelectric conversion device, and a second crystal array layer disposed over the first crystal layer. The first crystal array layer includes a plurality of first scintillation crystals arranged in a first crystal array, and a first coupling medium being filled between every adjacent two of the first scintillation crystals. The second crystal array layer includes a plurality of second scintillation crystals arranged in a second crystal array, and a second coupling medium being filled between every adjacent two of the second scintillation crystals. A light transmittance of the second coupling medium is different from a light transmittance of the first coupling medium.

Abstract: A crystal array, a detector, a medical detection device and a method for manufacturing a crystal array are provided. The crystal array includes a plurality of crystals arranged in an array, each of the crystals having a light incident surface, a light exit surface, and a connection surface connecting the light incident surface to the light exit surface, where the connection surface of at least one of two adjacent crystals includes a rough surface and a smooth surface connected to the rough surface, and the rough surface and the smooth surface are arranged along a length direction of the crystal.

Abstract: The present invention provides a cup holder. The cup holder includes a cup holder body having a receiving part and a charging assembly. The charging assembly includes a wireless charging module. The wireless charging module is mounted on the cup holder body and configured to charge a smart electronic device. The cup holder can charge the smart electronic devices, thereby improving user experience.

Abstract: Medical detectors and medical imaging devices are provided. In one aspect, a medical detector includes: a photoelectric conversion device, a first crystal array layer disposed over the photoelectric conversion device, and a second crystal array layer disposed over the first crystal layer. The first crystal array layer includes a plurality of first scintillation crystals arranged in a first crystal array, and a first coupling medium being filled between every adjacent two of the first scintillation crystals. The second crystal array layer includes a plurality of second scintillation crystals arranged in a second crystal array, and a second coupling medium being filled between every adjacent two of the second scintillation crystals. A light transmittance of the second coupling medium is different from a light transmittance of the first coupling medium.

Abstract: A crystal array, a detector, a medical detection device and a method for manufacturing a crystal array are provided. The crystal array includes a plurality of crystals arranged in an array, each of the crystals having a light incident surface, a light exit surface, and a connection surface connecting the light incident surface to the light exit surface, where the connection surface of at least one of two adjacent crystals includes a rough surface and a smooth surface connected to the rough surface, and the rough surface and the smooth surface are arranged along a length direction of the crystal.

Abstract: A method of calibrating time in a Positron Emission Tomography (PET) device includes obtaining original time information and energy information of a first pulse signal collected by a detecting module during a scanning process of the PET device. A detector of the PET device includes a plurality of detecting modules. The original time information of the first pulse signal includes a moment at which an amplitude of the first pulse signal begins to be greater than a threshold. The method includes determining a pulse time calibration amount corresponding to the energy information of the first pulse signal according to stored information indicative of a correspondence between the pulse time calibration amount and the energy information of each detecting module. The method includes generating calibrated time information of the first pulse signal by calibrating the original time information with the pulse time calibration amount; and reconstructing a PET image based on the generated calibrated time information.

Abstract: A method of calibrating time in a Positron Emission Tomography (PET) device includes obtaining original time information and energy information of a first pulse signal collected by a detecting module during a scanning process of the PET device. A detector of the PET device includes a plurality of detecting modules. The original time information of the first pulse signal includes a moment at which an amplitude of the first pulse signal begins to be greater than a threshold. The method includes determining a pulse time calibration amount corresponding to the energy information of the first pulse signal according to stored information indicative of a correspondence between the pulse time calibration amount and the energy information of each detecting module. The method includes generating calibrated time information of the first pulse signal by calibrating the original time information with the pulse time calibration amount; and reconstructing a PET image based on the generated calibrated time information.

Abstract: A method of calibrating time in a Positron Emission Computed Tomography (PET) device includes determining a rising edge slope of an electrical signal corresponding to a photon which is detected by a detector of the PET device when the PET device is used to scan a part of a subject to be examined. The method includes determining a time shift corresponding to the rising edge slope based on a correspondence between the rising edge slope and the time shift; calibrating time information of the photon based on the time shift; and reconstructing a PET image of the part of the subject to be examined based on the calibrated time information of the photon.

Abstract: A method of calibrating time in a Positron Emission Computed Tomography (PET) device includes determining a rising edge slope of an electrical signal corresponding to a photon which is detected by a detector of the PET device when the PET device is used to scan a part of a subject to be examined. The method includes determining a time shift corresponding to the rising edge slope based on a correspondence between the rising edge slope and the time shift; calibrating time information of the photon based on the time shift; and reconstructing a PET image of the part of the subject to be examined based on the calibrated time information of the photon.

Abstract: Methods and devices for calibrating a gain of a scintillator detector are disclosed, where a scintillation crystal of the scintillator detector includes two or more energy regions. In an example, the scintillation crystal of the scintillator detector is adopted as a radiation source for calibrating. Electric signals outputted from a rear end of the scintillator detector are collected, and actual counts of the electric signals from each of at least two energy regions of the scintillation crystal at a specified position are obtained, respectively. Then, a gain of the scintillator detector may be adjusted according to the obtained actual counts of the electric signals from the at least two energy regions.

Abstract: A method of adjusting a gain of a detector is provided in the present disclosure. According to an example, whether a gain of a photomultiplier tube in the detector meets a gain determination condition may be determined, where the gain determination condition may indicate that an absolute of a difference between the gain of the photomultiplier tube and a target gain is within a predetermined numerical range. When the gain of the photomultiplier tube does not meet the gain determination condition, a voltage of the photomultiplier tube may be adjusted, such that the gain of the photomultiplier tube meets the gain determination condition.

Abstract: A method of adjusting a gain of a detector is provided in the present disclosure. According to an example, whether a gain of a photomultiplier tube in the detector meets a gain determination condition may be determined, where the gain determination condition may indicate that an absolute of a difference between the gain of the photomultiplier tube and a target gain is within a predetermined numerical range. When the gain of the photomultiplier tube does not meet the gain determination condition, a voltage of the photomultiplier tube may be adjusted, such that the gain of the photomultiplier tube meets the gain determination condition.

Abstract: Methods and devices for calibrating a gain of a scintillator detector are disclosed, where a scintillation crystal of the scintillator detector includes two or more energy regions. In an example, the scintillation crystal of the scintillator detector is adopted as a radiation source for calibrating. Electric signals outputted from a rear end of the scintillator detector are collected, and actual counts of the electric signals from each of at least two energy regions of the scintillation crystal at a specified position are obtained, respectively. Then, a gain of the scintillator detector may be adjusted according to the obtained actual counts of the electric signals from the at least two energy regions.

Abstract: A multimodality imaging system, comprising: a first imaging system for forming a first image; a second imaging system for forming a second image; and a rotating device on which the first imaging system and the second imaging system are fixed so that the first imaging system and the second imaging system are selectively rotated to a scanning position.

Abstract: A multimodality imaging system, comprising: a first imaging system for forming a first image; a second imaging system for forming a second image; and a rotating device on which the first imaging system and the second imaging system are fixed so that the first imaging system and the second imaging system are selectively rotated to a scanning position.