CN105105782A - CT system and imaging method - Google Patents
CT system and imaging method Download PDFInfo
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- CN105105782A CN105105782A CN201510639423.2A CN201510639423A CN105105782A CN 105105782 A CN105105782 A CN 105105782A CN 201510639423 A CN201510639423 A CN 201510639423A CN 105105782 A CN105105782 A CN 105105782A
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Abstract
The invention provides a CT system which comprises a CT bulb tube, a detector, a data collecting module, a control module and an image reconstruction module. The CT bulb tube is used for generating X-ray signals. The detector is used for receiving the X-ray signals, converting the X-ray signals into corresponding electric signals and inducting and acquiring temperature of itself. The data collecting module is connected with the detector and used for converting the electric signals output by the detector into projection data and converting the temperature information of the detector into a detector temperature value. The control module is used for controlling the detector temperature value within a target temperature range and starting the CT bulb tube to work. The image reconstruction module is connected with the data collecting module and used for reconstructing a tomography image according to the projection data. The acquired temperature information is directly from the interior of the detector, and the interference of temperature fluctuation with scanning imaging can be fast and efficiently adjusted. In addition, the invention provides an imaging method of the CT system.
Description
[technical field]
The present invention relates to medical image system, particularly relate to CT system and formation method.
[background technology]
Computed tomography (ComputedTomography, CT) be an important breakthrough of x-ray imaging technology, medically can be used to blood clot, gastrointestinal disease and human body soft tissue injury etc. in swollen sick, the brain of diagnosis of vertebral and head injury, intracranial.The primary structure of current computed tomograph scanner system comprises two large divisions: x-ray tomography device and computer installation.The former is primarily of the detector composition producing the high tension generator of X-ray beam and bulb and reception, detection x-ray, the latter mainly comprises the auxiliary facilities such as data collecting system, central processing system, operating board, image display, X-ray bulb and detector are arranged on respectively by the both sides of scanning tissue, and direction is relative.Its principle is roughly: CT utilizes human body different tissues to the absorption of X-ray not etc., tested for human body aspect is divided into many cube fritters (voxel), CT records density and the gray scale (pixel) of each voxel, the decay total amount of X-ray after selected aspect is the summation of each voxel X-ray attenuation amount, rotate bulb, x-ray is from different perspectives through selected aspect, rotate repeatedly, simultaneous equations can be obtained, in this equation, x-ray decay total amount is given value, each voxel x-ray pad value is unknown quantity, each voxel X-ray attenuation value (corresponding each pixel) is obtained in machine computing as calculated, the faultage image of a width two dimension is made up of these pixels, different two dimensional images is combined into a secondary 3-D view in a computer.
In CT data collecting system, detector is the core component of whole system, its structure is very complicated, it directly receives X-ray beam through the photon signal after measured object, the corresponding signal of telecommunication is converted to by the characteristic of himself, a typical CT detector mainly comprises medium (as gas scintillator etc.), photoelectric conversion array and electronics, also has collimator, power lights auxiliary facilities in addition.In detector work process, X-ray signal is irradiated to plane of crystal meeting generating portion heat energy, and X-radiation energy can be converted to the energy of thermal motion of lattice subsequently, thus causes detector crystal temperature to raise.But the material that detector uses is as very responsive for temperature in cadmium tungstate crystal, and the change of ambient temperature can cause photopeak value drift, affects opto-electronic conversion performance.Worse, if variations in temperature is excessive, crystal counter performance will be caused to change, and rebuild image and occur striped, thus affect diagnosis and distinguish.
In prior art, CT detector system is mostly arranged on a larger metallic matrix, maintenance level is maintained in order to make detector temperature, usually some semiconductor temperature sensors, heater element and cooling device are set on metallic matrix, carry out the work of controlled cooling model fan or heater element according to the temperature of temperature sensor feedback metal base surface, thus maintain detector temperature within the specific limits.But, the variations in temperature that the thermal resistance of the inside of temperature sensor or the thermal inertia of thermal coupling can make temperature sensor detect lags behind the change of detector self-temperature, and hygrosensor to detect not be the true temperature of detector, but the temperature around metallic matrix or detector.And in CT imaging system running, the frame of high speed rotating, send the high pressure bulb of X-ray, the sensor of high integration all can produce amount of heat, thus cause the rising of whole system temperature, and the acquisition environment around temperature sensor is also inevitably subject to the impact of above-mentioned factors, thus causing temperature sensor to detect temperature value and detector actual temperature is variant, the final image generated also can produce artifact.Given this, be necessary to propose effectively to avoid temperature fluctuation to produce the CT formation method of artifact.
[summary of the invention]
Technical problem to be solved by this invention proposes a kind of CT formation method can effectively avoiding temperature fluctuation to produce artifact.
The present invention solves the problems of the technologies described above adopted technical scheme: a kind of CT system, comprising:
CT bulb, for generation of X-ray signal;
Detector, for receiving X-ray signal, and is converted to the corresponding signal of telecommunication and induction acquisition detector own temperature information by described X-ray signal;
Data acquisition module, is connected with described detector, and the signal of telecommunication for being exported by described detector is converted to data for projection and is detector temperature value by detector own temperature convert information;
Control module, for detector temperature value being controlled in target temperature range, and starts the work of CT bulb;
Image reconstruction module, is connected with described data acquisition module, for according to described reconstructs projection data tomographic image.
Further, also comprise temperature adjustment module, under controlling in described control module, regulate the temperature of described detector in target temperature range.
Further, described temperature adjustment module be arranged at detector carriage surface several heating units or/and cooling unit.
Further, when lower limit lower than target temperature range of the temperature of detector, then described control module controls described heating unit and heats up to described detector; When higher limit higher than target temperature range of the temperature of detector, then described control module controls described cooling unit and lowers the temperature to described detector.
Further, described detector carriage being gone back scattering device has several temperature sensors, for obtaining air themperature.
The present invention also provides a kind of formation method of CT system, before image scanning, according to detector own temperature acquisition of information detector transition temperature value, and before judging scanning detector temperature value whether in target temperature range, if condition meets, then perform CT scan; Otherwise, then regulate the temperature of the front detector of scanning in target temperature range.
Further, in CT scan process, according to detector own temperature acquisition of information detector transition temperature value, and judge that the temperature of detector in scanning process is whether in target temperature range, if condition meets, then continue to perform CT scan; Otherwise, then control described CT system and enter standby adjustment state, regulate the temperature of detector in scanning to target temperature range.
Further, describedly to be realized by following relational expression according to detector own temperature acquisition of information detector transition temperature value:
T＝(S-S
0)/R+T
0
Wherein, T represents detector transition temperature value, T
0represent air temperature value, S
0represent detector initialize temperature information, S represent detector power on after temperature information, R represents yield value.
Further, R=10.
Further, be also included in scanning process, adopt PID control method to make described detector temperature maintain target temperature range.
Compared with prior art, beneficial effect of the present invention is: detector obtains internal temperature information by inner thermo-responsive first physical parameter variation sensing, linear graduation conversion detector true temperature value can be obtained by this temperature information, temperature information feedback is efficient, quick, avoids the impact of ambient temperature on measuring tempeature; Before image scanning, detect the temperature of the hygrosensor of detector, the detector being in room temperature is adjusted to target temperature range, eliminate the interference of room temperature to imaging; The temperature of PID regulating and controlling detector is adopted to maintain target temperature range in scan period, if the temperature anomaly of monitoring, then control CT system is to standby adjustment state, until detector temperature reaches target temperature just carry out image scanning, both overcome the interference of temperature fluctuation to scanning imagery, turn avoid unnecessary X-radiation.
[accompanying drawing explanation]
Fig. 1 is CT system structure schematic diagram;
Fig. 2 is the layout of the detector of embodiment of the present invention and heating on it, cooling unit;
Fig. 3 is CT system imaging method flow diagram.
[detailed description of the invention]
For enabling above-mentioned purpose of the present invention, feature and advantage more become apparent, and are described in detail the specific embodiment of the present invention below in conjunction with drawings and Examples.
In order to intactly understand the present invention, please refer to Fig. 1, representing CT system structure schematic diagram.Wherein, high tension generator is for the work of the order control CT bulb that receive control module, CT bulb is also called x-ray source, provides the fladellum of X-ray or conical beam X-ray namely to produce X-ray signal, this X-ray through be positioned at scanning bed on human body and generating portion decay, the X-ray signal that detector receiving unit is decayed also is converted to the corresponding signal of telecommunication, the array of multiple detector composition is installed on the detector carriage inside of metallic substrates composition, and is installed on the relative both sides of frame with CT bulb, the data acquisition module (dataacquisitionsystem, DAS) be connected with detector obtains the signal of telecommunication that detector exports, and above-said current signal is converted to digital signal (data for projection) through A/D converter, control module connection data acquisition module, there is memorizer and CPU (centralprocessingunit), it receives the data for projection of DAS, and carry out necessary data compression and reformatting process, subsequently by the data buffer storage image re-construction system after process, be connected with control system, data for projection after control module process is dispensed to the unit of back projection's version by the back projection's controller in image re-construction system, the data that each back projection unit is held can project to six projections from one, and stored simultaneously, then image data is sent to each back projection plate and carries out summation operation resulting pixel data together with the result of each back projection unit, can rebuild and obtain tomographic image, and show in the display.
In above process, high tension generator, detector, DAS (data acquisition module) and image reconstruction module are all controlled by control module (central control system).In CT system scan process, because in the irradiation of X-ray and photoelectric conversion process, the change of energy can make the temperature of detector raise, and the fluctuation of detector working environment can affect its photoelectric transformation efficiency, the image that final reconstruction obtains also can produce artifact, therefore, stability and the concordance of system is ensured in needing reimaging to scan.Detector in CT system of the present invention, while X-ray signal is converted to corresponding electric signal, can be responded to and obtain detector own temperature information.Detector (X-ray detection unit) in the embodiment of the present invention comprising with some scintillation crystals of array way layout, being positioned at the asic chip of scintillation crystal lower floor and the chip substrate for carrying asic chip and scintillation crystal.In the present invention, the acquisition of detector own temperature information is mainly through the thermo-responsive unit (being integrated in asic chip) of detector crystal inside, when being in different temperatures, can produce different physical parameters, and these physical parameters exactly can as detector temperature information.It should be noted that, integrated circuit technology can also be adopted in detector at the inner set temperature sensing device of detector, directly obtain the temperature of detector.As the layout that Fig. 2 is the detector in embodiment of the present invention and the heating on it, cooling unit, the detector carriage inside that multiple detector is arranged side by side in being made up of metallic substrates forms detector array, in the present embodiment, based on the existing good heat radiation of aluminum and conducting effect, the material selection metallic aluminium of detector carriage.For the ease of regulating the temperature of detector, the present invention's detector used is also provided with temperature adjustment module, this temperature adjustment module be arranged at detector carriage surface several heating units or/and cooling unit, when lower limit lower than target temperature range of the temperature of detector, then control module controls heating unit and heats up to detector; When higher limit higher than target temperature range of the temperature of detector, then control module controlled cooling model unit is lowered the temperature to detector, be specially: be arranged on fire-bar on metallic substrates framework as heating unit, be arranged on the fan of detector carriage side as cooling unit, in practical operation, fire-bar is provided with 6 tunnels, wherein 2 tunnel (not shown) for subsequent use, and the number of fan is specially 6 (F1-F6).In addition, in the metallic substrates of detector carriage, correspondingly with fire-bar position be provided with multiple temperature sensor, respectively at detector carriage outer setting S1 for obtaining system outside air temperature; S2 is set near fire-bar H1, for obtaining fire-bar H1 ambient air temperature; S3 is set near fire-bar H2-2, for obtaining fire-bar H2-2 ambient air temperature; S4 is set near fire-bar H3-2, for obtaining fire-bar H3-2 ambient air temperature; Near fire-bar H4-2, arrange S5, for obtaining fire-bar H4-2 and fan ambient air temperature, the Temperature numerical of each detector acquisition is basically identical under a cold state.It is pointed out that fire-bar used in the present embodiment is copper sheet, its scattering device, in the position, inside edge of detector carriage, saves the heat of copper sheet generation by changing the current adjustment flowing through copper sheet during work.When needs heat detector, airflow direction as shown in Figure 2, the fire-bar H1 that first air (18-25 DEG C) of extraneous lower temperature arrives detector carriage front end carries out one-level heating, temperature is now elevated to 28 ± 2 DEG C, air through one-level heating carries out secondary heating at fire-bar H2-1H2-2, H3-1, H3-2, H4-1, H4-2 respectively, it is 36 ± 1 DEG C that air themperature now has raised, and constantly carries out exchange heat and can be elevated in target temperature range between detector and air.When detector causes temperature to exceed target zone higher limit due to absorption of x-rays, now need to carry out radiating and cooling to detector, fire-bar quits work, fan running increases the air circulation inside and outside detector carriage, thus accelerate the exchange heat of detector and extraneous Cryogenic air, reduce the temperature of detector.Adopt electric heating bar (copper sheet) as heating unit in the embodiment of the present invention, but other modes also can be adopted as heating unit.Adopt fan (air-cooled) as cooling unit in the embodiment of the present invention, but other modes also can be adopted as cooling unit.
Be illustrated in figure 3 the flow chart of the formation method adopting CT system of the present invention, be specially:
Under cold state (before image scanning), control module issues temperature scale order to data acquisition module, and the temperature sensor being arranged on metal substrate surface obtains detector system ambient air temperature value T
0, this air temperature value is the data mean value that S1-S5 detector obtains, T in the present embodiment
0=25 DEG C.
The temperature information of perception under cold state is sent to data acquisition module by the thermo-responsive unit of detector inside, and data now only comprise temperature information S before image scanning
0, S in this embodiment
0=350, now temperature information S before image scanning
0with air temperature value T
0corresponding.Detector is now operated in temperature scale pattern, and before first judging scanning, whether temperature value is in target temperature range, if condition meets, then performs CT scan; Otherwise, then the temperature of detector is regulated, until condition meets.Information when temperature value is 25 DEG C during the temperature information now stored in data acquisition chip, comparatively large with target temperature value 36 DEG C of gaps of detector, need the temperature raising detector.Control module is after receiving the temperature information of temperature sensor detection of metal substrate surface, that can strengthen the fire-bar electric current in temperature adjustment module passes into generation heat, raise detector ambient air temperature, the temperature of detector also can raise gradually due to the exchange heat with surrounding.In heating process, the physical parameter of the thermo-responsive unit in detector also can constantly change, thus produces the information S of reaction temperature change.Data acquisition module constantly accepts from detector own temperature information, and by " coretemp " function according to detector own temperature acquisition of information detector transition temperature value, concrete formula is: T=(S-S
0)/R+T
0, R represents yield value, and the scope of R can change in 5-15 according to practical situation, is preferably R=10 in the present embodiment.Before regulating detector scanning by said process, temperature value is to (36 ± 1.5 DEG C) in target temperature range, and CT system enters the image scanning phase, thus gets rid of the impact of imaging initial stage room temperature.It should be noted that, what data acquisition module adopted is non-volatile Flash memory chip, also can preserve data for a long time, enhance the reliability of system under the condition not having electric current supply.
Control module sends after scanning imagery order sends, high tension generator control CT bulb sends X-ray signal, simultaneously detector detects the X-ray signal that sends and produces the signal of telecommunication and produce detector own temperature information continuously, it will detector own temperature convert information be now detector temperature value (temperature information conversion process is identical with temperature inversion process noted earlier) that the signal of telecommunication is changed generation data for projection through A/D by data acquisition module simultaneously, comprise imaging data and temperature data in the data that namely data acquisition module stores simultaneously.The data for projection of storage and detector temperature value are sent to control module by data communication interface (DIF) plate by data acquisition module, then control module adopts PID regulating and controlling temperature adjustment module according to detector temperature value, and detector temperature is maintained in target temperature range.The ultimate principle that wherein PID controls is: the measuring-signal controlled as PID using the detector temperature value that detector own temperature convert information is next, using target temperature as set-point, deviation according to measuring-signal and set-point carries out ratio (Proportional, P), integration (Integral, I), differential (Derivative, D) computing, in this particular embodiment, the concrete formula of employing is:
Wherein, H represents that the temperature of output controls variable quantity, and e represents the difference of set-point and measuring-signal, and P, I, D are respectively the adjustment factor in ratio, integration and differentiation computing, and t is regulating time.By said process, control module exports certain appropriate control signal to temperature adjustment module (in fire-bar or fan at least one), the temperature of detector is maintained in target zone all the time, reaches the effect automatically controlled.In whole adjustment process, the thermo-responsive unit in detector successively produces detector own temperature information, and feeds back to control module.
In scanning process, if control module monitors the temperature value of the temperature information conversion of detector not in target temperature range, then now control module controls x-ray source stopping and producing X-ray signal and stopping image-forming data acquisition, CT system enters standby adjustment state, be specially: when control module monitors the higher limit of the next temperature value of detector temperature convert information higher than target temperature range, control module control CT bulb stops launching X-ray, detector only produces temperature information by the responsive unit of internal heat, control module then controls fan and runs, the outer cold air of increase system flows in CT system, promote that the heat inside and outside CT system is mutual, reduce the temperature of detector in target temperature range, and be scanning mode by the mode of operation of CT system from standby adjustment state transfer, when control module monitors the lower limit of the next temperature value of detector temperature convert information lower than target temperature range, control module control CT bulb stops launching X-ray, detector only produces temperature information by the responsive unit of internal heat, control module controls fire-bar and runs, detector ambient air is heated, raise detector temperature gradually until arrive in target temperature range, and be scanning mode by the mode of operation of CT system from standby adjustment state transfer.It is to be noted, need judge while above-mentioned adjustment process whether scanning completes, if now scan-data collection completes, then control module controls X-ray stopping transmitting X-ray signal, image data acquiring and temperature acquisition data stop, and whole system work stops.Above adjustment process continues whole imaging interval, until imaging terminates, the thermo-responsive unit induction that the variations in temperature of period detector inside all can be detected in device produces temperature information, be different from the method that tradition needs sensor senses detector ambient temperature completely, not easily by the impact of device conductivity of materials, avoid the time delay that detector temperature change is delivered to temperature sensor, obtain real-time property higher, more accurately; In scanning process, the variations in temperature of continuous monitoring detector, when monitoring temperature anomaly, then stops scanning entering standby adjustment state, both ensure that image not turn avoid the unnecessary x radiation x of testee by the impact of temperature fluctuation.
It should be noted that, the temperature of the multiple hygrosensors being arranged at metallic substrates framework surface in whole temperature adjustment process also around continuous feedback detector, the temperature value that the temperature value obtained by temperature sensor and data acquisition chip are changed compares by control module, if both have big difference, such as: the temperature value of data acquisition chip conversion is in target temperature range, and the temperature value that temperature sensor obtains exceedes maximum set temperature value, then illustrate that the thermo-responsive unit in detector may break down, and now should stop scanning.
The foregoing is only preferred embodiment of the present invention, not in order to limit the present invention, within the spirit and principles in the present invention all, any amendment made, equivalent replacement, improvement etc., all should be included within protection scope of the present invention.
Claims (10)
1. a CT system, is characterized in that, comprising:
CT bulb, for generation of X-ray signal;
Detector, for receiving X-ray signal, and is converted to the corresponding signal of telecommunication and induction acquisition detector own temperature information by described X-ray signal;
Data acquisition module, is connected with described detector, and the signal of telecommunication for being exported by described detector is converted to data for projection and is detector temperature value by detector own temperature convert information;
Control module, for detector temperature value being controlled in target temperature range, and starts the work of CT bulb;
Image reconstruction module, is connected with described data acquisition module, for according to described reconstructs projection data tomographic image.
2. CT system as claimed in claim 1, is characterized in that, also comprise temperature adjustment module, under controlling in described control module, regulate the temperature of described detector in target temperature range.
3. CT system as claimed in claim 2, is characterized in that, described temperature adjustment module be arranged at detector carriage surface several heating units or/and cooling unit.
4. CT system as claimed in claim 3, is characterized in that, when lower limit lower than target temperature range of the temperature of detector, then described control module controls described heating unit and heats up to described detector; When higher limit higher than target temperature range of the temperature of detector, then described control module controls described cooling unit and lowers the temperature to described detector.
5. the CT system as described in claim 3 or 4, is characterized in that, described detector carriage being gone back scattering device has several temperature sensors, for obtaining air themperature.
6. one kind adopts the formation method of CT system as claimed in claim 1, it is characterized in that, before image scanning, according to detector own temperature acquisition of information detector transition temperature value, and before judging scanning detector temperature value whether in target temperature range, if condition meets, then perform CT scan; Otherwise, then regulate the temperature of the front detector of scanning in target temperature range.
7. formation method as claimed in claim 6, it is characterized in that, also comprise, in CT scan process, according to detector own temperature acquisition of information detector transition temperature value, and judge that the temperature of detector in scanning process is whether in target temperature range, if condition meets, then continue to perform CT scan; Otherwise, then control described CT system and enter standby adjustment state, regulate the temperature of detector in scanning to target temperature range.
8. formation method as claimed in claims 6 or 7, it is characterized in that, described is realized by following relational expression according to detector own temperature acquisition of information detector transition temperature value:
T＝(S-S
0)/R+T
0
Wherein, T represents detector transition temperature value, T
0represent air temperature value, S
0represent detector initialize temperature information, S represent detector power on after temperature information, R represents yield value.
9. CT formation method as claimed in claim 8, is characterized in that, R=10.
10. formation method as claimed in claim 8, is characterized in that, be also included in scanning process, adopts PID control method to make described detector temperature maintain target temperature range.
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| CN107307878A (en) * | 2017-06-30 | 2017-11-03 | 上海联影医疗科技有限公司 | A kind of CT system temprature control method |
| CN108378864A (en) * | 2018-03-19 | 2018-08-10 | 沈阳东软医疗系统有限公司 | The detector temperature control method and Medical Devices of Medical Devices |
| CN108652655A (en) * | 2018-04-28 | 2018-10-16 | 沈阳东软医疗系统有限公司 | Control method, apparatus, equipment and the machine readable storage medium of thermal capacity |
| CN109199425A (en) * | 2018-09-29 | 2019-01-15 | 天津金曦医疗设备有限公司 | A kind of mobile plate CT imaging system for the detection of brain soft tissue |
| CN111317495A (en) * | 2020-02-25 | 2020-06-23 | 沈阳先进医疗设备技术孵化中心有限公司 | CT image data processing method and CT imaging system |
| CN112022180A (en) * | 2020-09-09 | 2020-12-04 | 上海联影医疗科技股份有限公司 | Portable DR |
| CN112098686A (en) * | 2020-09-18 | 2020-12-18 | 深圳市德林科科技有限公司 | Modularized wire harness assembly universal detection die frame |
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| CN107307878A (en) * | 2017-06-30 | 2017-11-03 | 上海联影医疗科技有限公司 | A kind of CT system temprature control method |
| CN108378864A (en) * | 2018-03-19 | 2018-08-10 | 沈阳东软医疗系统有限公司 | The detector temperature control method and Medical Devices of Medical Devices |
| CN108378864B (en) * | 2018-03-19 | 2024-06-28 | 东软医疗系统股份有限公司 | Detector temperature control method for medical equipment and medical equipment |
| CN108652655B (en) * | 2018-04-28 | 2022-05-10 | 东软医疗系统股份有限公司 | Method, device, equipment and machine readable storage medium for controlling heat capacity |
| CN108652655A (en) * | 2018-04-28 | 2018-10-16 | 沈阳东软医疗系统有限公司 | Control method, apparatus, equipment and the machine readable storage medium of thermal capacity |
| CN109199425A (en) * | 2018-09-29 | 2019-01-15 | 天津金曦医疗设备有限公司 | A kind of mobile plate CT imaging system for the detection of brain soft tissue |
| WO2020063379A1 (en) * | 2018-09-29 | 2020-04-02 | 杨舰 | Mobile flat-panel ct imaging system for brain parenchyma detection |
| CN111317495B (en) * | 2020-02-25 | 2023-03-31 | 沈阳先进医疗设备技术孵化中心有限公司 | CT image data processing method and CT imaging system |
| CN111317495A (en) * | 2020-02-25 | 2020-06-23 | 沈阳先进医疗设备技术孵化中心有限公司 | CT image data processing method and CT imaging system |
| CN112022180A (en) * | 2020-09-09 | 2020-12-04 | 上海联影医疗科技股份有限公司 | Portable DR |
| CN112098686A (en) * | 2020-09-18 | 2020-12-18 | 深圳市德林科科技有限公司 | Modularized wire harness assembly universal detection die frame |
| CN112748752A (en) * | 2020-12-21 | 2021-05-04 | 上海联影医疗科技股份有限公司 | Cooling system temperature adjusting method and device, computer equipment and storage medium |
| CN112741642A (en) * | 2020-12-28 | 2021-05-04 | 明峰医疗系统股份有限公司 | Temperature balancing device of CT detector |
| CN112741642B (en) * | 2020-12-28 | 2024-05-28 | 明峰医疗系统股份有限公司 | CT detector temperature equalizing device |
| CN113712582A (en) * | 2021-09-17 | 2021-11-30 | 江苏康众数字医疗科技股份有限公司 | Flat panel detector with temperature control function and temperature control method thereof |
| WO2024002309A1 (en) * | 2022-06-29 | 2024-01-04 | Shanghai United Imaging Healthcare Co., Ltd. | Methods and systems for controlling an imaging device, and detecting parameters of a detector |
| CN116649999A (en) * | 2023-07-25 | 2023-08-29 | 赛诺威盛科技(北京)股份有限公司 | Temperature control method and system for detector |
| CN116649999B (en) * | 2023-07-25 | 2023-11-07 | 赛诺威盛科技(北京)股份有限公司 | Temperature control method and system for detector |
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