CN106580358B - Tomography system and tomography control circuit thereof - Google Patents
Tomography system and tomography control circuit thereof Download PDFInfo
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- CN106580358B CN106580358B CN201611093004.4A CN201611093004A CN106580358B CN 106580358 B CN106580358 B CN 106580358B CN 201611093004 A CN201611093004 A CN 201611093004A CN 106580358 B CN106580358 B CN 106580358B
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computerised tomographs
- A61B6/032—Transmission computed tomography [CT]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/40—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis
- A61B6/4007—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5258—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise
- A61B6/5264—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise due to motion
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/54—Control of apparatus or devices for radiation diagnosis
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/54—Control of apparatus or devices for radiation diagnosis
- A61B6/542—Control of apparatus or devices for radiation diagnosis involving control of exposure
Abstract
The invention belongs to the technical field of X-ray imaging, and provides a tomography system and a tomography control circuit thereof. According to the invention, a tomography scanning control circuit comprising a driving module, a plurality of high-voltage control modules, a cold cathode field X-ray source array and a high-voltage direct-current power supply is adopted in a tomography system, and a detector of the tomography system sends an exposure time sequence signal to the driving module; the driving module outputs a plurality of paths of single pulse signals according to the exposure time sequence signal; the emission time sequence of the X-ray source array caused by the cold cathode fields is controlled by the plurality of high-voltage control modules according to the multi-path single pulse signals respectively, so that the X-ray sources caused by the plurality of cold cathode fields emit X rays to a target object in sequence.
Description
Technical Field
The invention belongs to the technical field of X-ray imaging, and particularly relates to a tomography system and a tomography control circuit thereof.
Background
A Computed Tomography (CT) system is a system that scans a layer of a certain thickness of a certain part of a human body with X-ray beams, receives the X-rays penetrating through the layer of the human body by a detector (i.e., an image sensor), converts photoelectric signals and analog/digital signals, and then inputs the converted X-rays into a computer for processing to form a CT image corresponding to the certain part of the human body. In an X-ray tomography system, an X-ray source is one of the core components of the tomography system, and determines the imaging mode and the imaging performance of the tomography system to some extent.
The X-ray source in the existing fault imaging system adopts a hot cathode electron source, and generates electron beams in a mode of thermally emitting electrons, the X-ray source has high working temperature and high power consumption, and is not beneficial to the miniaturization of the X-ray source, and a plurality of cathodes are difficult to be integrated in a single X-ray source.
However, when the existing tomography system performs multi-angle scanning, because the X-ray source is always in an on state, during the movement process between different angles, invalid radiation dose can be generated, and the total radiation dose of a patient during the scanning process can be increased; moreover, the imaging system has high requirements on imaging precision, so that the investment cost of the rotating rack is increased; meanwhile, motion artifacts are generated during mechanical rotation, the spatial resolution of the image is reduced, and the reconstruction of the image is not facilitated.
In summary, the conventional tomography system has the problems of generating motion artifacts and ineffective radiation doses during the scanning process and high cost.
Disclosure of Invention
The invention aims to provide a tomography system and a tomography control circuit thereof, and aims to solve the problems that the existing tomography system can generate motion artifacts and invalid radiation dose in the scanning process and has higher cost.
The invention is realized in this way, a fault scanning control circuit of the fault imaging system, the fault scanning control circuit is connected with a detector of the fault imaging system, the fault scanning control circuit comprises a driving module, a plurality of high-voltage control modules, a cold cathode field X-ray source array and a high-voltage direct current power supply; the cold cathode field X-ray source array comprises a plurality of cold cathode field X-ray sources which are arranged in a linear array, and the number of the cold cathode field X-ray sources is equal to that of the high-voltage control modules;
the signal receiving end and the signal sending end of the driving module are respectively connected with the signal sending end and the signal receiving end of the detector, a plurality of output ends of the driving module are respectively connected with input ends of the plurality of high-voltage control modules, output ends of the plurality of high-voltage control modules are respectively connected with field emission cathodes of the plurality of cold cathode field X-ray sources, grids of the plurality of cold cathode field X-ray sources are commonly connected with the anode of the high-voltage direct-current power supply, and the cathode of the high-voltage direct-current power supply is grounded;
in a tomography mode, the detector sends a preparation signal to the driving module, and sends an exposure time sequence signal to the driving module when receiving a first feedback signal sent by the driving module; the driving module outputs a plurality of paths of single pulse signals according to the exposure time sequence signal; the high-voltage control modules respectively control the emission time sequence of the cold cathode field X-ray source array according to the multi-path single pulse signals, so that the cold cathode field X-ray sources sequentially emit X rays to a target object under the action of anode high voltage; the detector receives the X-ray penetrating through the target object, converts the received attenuated X-ray into two-dimensional projection data and outputs the two-dimensional projection data to a computer of the tomography system.
The invention also provides a tomography system which comprises the detector and a computer and comprises the tomography control circuit.
According to the invention, a tomography scanning control circuit comprising a driving module, a plurality of high-voltage control modules, a cold cathode field X-ray source array and a high-voltage direct-current power supply is adopted in a tomography imaging system, a detector sends a preparation signal to the driving module in a tomography scanning mode, and an exposure time sequence signal is sent to the driving module when a first feedback signal sent by the driving module is received; the driving module outputs a plurality of paths of single pulse signals according to the exposure time sequence signal; the high-voltage control modules respectively control the emission time sequence of the cold cathode field X-ray source array according to the multi-path single pulse signals, so that the cold cathode field X-ray sources sequentially emit X rays to a target object under the action of high anode voltage; the detector receives the X-ray penetrating through the target object, converts the received attenuated X-ray into two-dimensional projection data and outputs the two-dimensional projection data to a computer of a tomography system.
Drawings
FIG. 1 is a schematic block diagram of a tomography control circuit according to an embodiment of the present invention;
FIG. 2 is a schematic block diagram of a tomography control circuit according to another embodiment of the present invention;
fig. 3 is a schematic circuit structure diagram of a tomography control circuit according to an embodiment of the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the present invention is described in further detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention.
Fig. 1 shows a module structure of a tomography control circuit provided in an embodiment of the present invention, and for convenience of description, only the parts related to the embodiment of the present invention are shown, and detailed descriptions are as follows:
as shown in fig. 1, a tomography control circuit of the tomography system is connected to a detector 10 of the tomography system, and the scanning control circuit includes a driving module 20, a plurality of high voltage control modules 30, a cold cathode field-induced X-ray source array 40, and a high voltage DC power supply DC.
The cold cathode X-ray source array 40 includes a plurality of cold cathode X-ray sources 41 arranged in a linear array, and the number of the cold cathode X-ray sources 41 is equal to the number of the high voltage control modules 30.
The signal receiving end and the signal transmitting end of the driving module 20 are connected with the signal transmitting end and the signal receiving end of the detector 10 respectively, a plurality of output ends of the driving module 20 are connected with input ends of a plurality of high-voltage control modules 30 respectively, output ends of the plurality of high-voltage control modules 20 are connected with field emission cathodes of a plurality of cold cathode field emission X-ray sources 41 respectively, grids of the plurality of cold cathode field emission X-ray sources 41 are connected with the positive electrode of a high-voltage direct-current power supply DC in common, and the negative electrode of the high-voltage direct-current power supply DC is grounded.
In the tomography mode, the detector 10 sends a preparation signal to the driving module 20, and sends an exposure timing signal to the driving module 20 when receiving a first feedback signal sent by the driving module 20; the driving module 20 outputs a plurality of single pulse signals according to the exposure time sequence signal; the plurality of high-voltage control modules 30 respectively control the exposure time sequence of the cold-cathode field X-ray source array 40 according to the multi-path single pulse signals, so that the plurality of cold-cathode field X-ray sources 41 sequentially emit X rays to the target object under the action of the anode high voltage; the detector 10 receives X-rays transmitted through a target object, performs photoelectric signal conversion and analog/digital signal conversion on the received attenuated X-rays to obtain a two-dimensional projection image, and outputs the two-dimensional projection image to a computer of a tomographic imaging system, and the computer processes the received two-dimensional projection image to form a Computed Tomography (CT) image corresponding to the target object (e.g., a certain part of a human body).
In the embodiment of the present invention, the detector 10 may be an amorphous selenium digital flat panel detector, which is specifically configured according to actual requirements, and is not limited herein.
In practical application, the cold cathode field-induced X-ray source array 40 and the X-ray receiving surface of the detector 10 (i.e., the imaging position of the detector 10) may be adjusted in advance, so that the detector 10 may receive the X-rays emitted by the cold cathode field-induced X-ray source 41, and the plurality of cold cathode field-induced X-ray sources 41 are arranged in a linear array, and the plurality of cold cathode field-induced X-ray sources 41 may be arranged in a horizontal linear array, a vertical linear array, or a linear array of other forms, which is specifically set according to practical situations, and is not limited herein. The plurality of cold cathode fields causes the X-ray source 41 to be oriented differently relative to the detector 10.
In the embodiment of the present invention, the cold cathode field X-ray source 41 may be a cold cathode carbon nano X-ray tube. The cold cathode field X-ray source 41 includes a field emission cathode, a grid and an anode (not shown in the figure), if the voltage applied between the field emission cathode and the grid is higher than the voltage required by the field emission cathode for electron escape, the field emission cathode emits electron beams, and meanwhile, the electron beams are accelerated by the anode high voltage (the anode high voltage is connected in the same way as the prior art, so the anode high voltage is not shown in the figure), and the electron beams bombard the target surface of the anode, thereby generating X-rays. In order for the cold cathode field emission electron source 41 to be able to operate, the high voltage direct current power supply DC needs to supply a direct current having a voltage up to several thousand volts.
In the embodiment of the invention, the high-voltage direct current power supply DC can adopt a constant current source. Meanwhile, the output voltage of the high-voltage direct current power supply DC needs to be limited to about 2000V to prevent the device from being damaged due to too high voltage in the constant current mode.
In the embodiment of the present invention, when the detector 10 works in the tomography mode, the detector 10 is powered on and then actively sends a preparation signal to the driving module 20, the driving module 20 receives the preparation signal and then sends a first feedback signal to the detector 10, the detector 10 receives the first feedback signal and then sends an exposure timing signal to the driving module 20, the driving module 20 processes the exposure timing signal and generates a continuous pulse signal to be fed back to the detector 10, and meanwhile, the driving module 20 decomposes the continuous pulse signal into multiple paths of single pulse signals and outputs the signals through multiple output ends of the single pulse signals; the high-voltage control modules 30 respectively control the exposure time sequence of the cold cathode field X-ray source array 40 according to the multi-path single pulse signals; specifically, when the pulse of the single pulse signal arrives, the high voltage loop of the field emission cathode of the cold cathode field-induced X-ray source 41 connected to the inside of the high voltage control module 30 is turned on, and at this time, because the voltage between the field emission cathode and the grid of the cold cathode field-induced X-ray source 41 is higher than the voltage required for electron escape of the field emission cathode, the field emission cathode emits an electron beam, and at the same time, the electron beam is accelerated by the high voltage of the anode, and the electron beam bombards the target surface of the anode to generate X-rays, and the detector 10 converts the energy of the X-rays after passing through the object to be scanned into an electrical signal, and outputs the electrical signal to the computer for processing after analog/digital conversion.
In the embodiment of the present invention, the times of emitting X-rays by each of the cold cathode field X-ray sources 41 do not overlap with each other, that is, only one single pulse signal is valid when each exposure time window comes, and the times of emitting X-rays by each of the cold cathode field X-ray sources are different.
In the embodiment of the present invention, the number of the cold cathode field-induced X-ray sources 41 may be set according to actual requirements, for example, the number of the cold cathode field-induced X-ray sources 41 may be 25, correspondingly, the number of the high voltage control modules 20 is 25, the continuous pulse signal generated by the driving module 20 includes 25 pulses, and the driving module 20 outputs 25 paths of single pulse signals, and the detector 10 may acquire at most 25 frames of images at one time in the tomography mode.
In the embodiment of the present invention, the detector 10 can also operate in a single frame scanning module in addition to the tomography mode, and the exposure timing signal is determined by the scanning mode of the detector 10, and the exposure timing signal can be preset and stored in the detector 10.
As can be seen from the above, the tomography control circuit provided by the embodiment of the invention adopts an electronic full-static scanning mode to replace the mechanical scanning in the existing tomography system, so that the cost of the high-precision rotating rack is saved; in addition, the tomography scanning control circuit provided by the embodiment of the invention does not have the problem of motion artifacts caused by mechanical motion in the prior art in the imaging process, thereby improving the spatial resolution of the image; meanwhile, because the embodiment of the invention adopts a pulse exposure mode, the exposure time of each cold cathode field X-ray source is not overlapped, so that invalid radiation dose can not be generated when different cold cathode field X-ray sources are switched, and the total radiation dose received by a patient in the scanning process is correspondingly reduced.
Fig. 2 shows a module structure of a tomography control circuit according to another embodiment of the present invention, and for convenience of description, only the parts related to the embodiment of the present invention are shown, and the details are as follows:
as shown in fig. 2, as an embodiment of the present invention, a first signal transmitting end, a second signal transmitting end, a first signal receiving end, and a second signal receiving end of the detector 10 are respectively connected to the first signal receiving end, the second signal receiving end, the first signal transmitting end, and the second signal transmitting end of the driving module 20, and the driving module 20 includes a signal transferring unit 21 and a control unit 22.
The first signal receiving end, the second signal receiving end, the first signal transmitting end and the second signal transmitting end of the signal switching unit 21 are respectively a first signal receiving end, a second signal receiving end, a first signal transmitting end and a second signal transmitting end of the driving module 20, the third signal transmitting end, the fourth signal transmitting end, the third signal receiving end and the fourth signal receiving end of the signal switching unit 21 are respectively connected with the first signal receiving end, the second signal receiving end, the first signal transmitting end and the second signal transmitting end of the control unit 22, and a plurality of output ends of the control unit 22 are respectively a plurality of output ends of the driving module 20.
The signal transfer unit 21 is used for signal transmission between the detector 10 and the control unit 22.
The control unit 22 is configured to process the exposure timing signal output by the detector 10, output a continuous pulse signal and feed back the continuous pulse signal to the detector 10, and at the same time, the control unit 22 decomposes the continuous pulse signal and outputs a plurality of single pulse signals to the plurality of high voltage control modules 30. The pulse number of the continuous pulse signals is equal to the number of the multiple paths of single pulse signals.
As an embodiment of the present invention, the high voltage control module 30 includes a high voltage isolation unit 31 and a high voltage pulse driving unit 32.
The input end of the high voltage isolation unit 31 is the input end of the high voltage control module 30, the output end of the high voltage isolation unit 31 is connected with the input end of the high voltage pulse driving unit 32, and the output end of the high voltage pulse driving unit 32 is the output end of the high voltage control module 30.
The high voltage isolation unit 31 is used for electrically isolating the driving module 20 from the high voltage pulse driving unit 32, that is, electrically isolating the low voltage side from the high voltage side, so as to prevent the kilovolt high voltage in the high voltage loop from entering the low voltage loop to burn out the control unit 22.
The high-voltage pulse driving unit 32 is used for performing pulse exposure control on the cold cathode field-induced X-ray source 41 according to a single pulse signal.
Fig. 3 shows a circuit configuration of a tomography control circuit provided in an embodiment of the present invention, and for convenience of description, only the portions related to the embodiment of the present invention are shown, and detailed descriptions are as follows:
as shown in fig. 3, as an embodiment of the present invention, the signal transferring unit 21 includes a first resistor R1, a second resistor R2, a third resistor R3, and a fourth resistor R4.
The first end and the second end of the first resistor R1 are respectively a first signal sending end and a third signal receiving end of the signal switching unit 21, the first end and the second end of the second resistor R2 are respectively a second signal sending end and a fourth signal receiving end of the signal switching unit 21, the second end of the third resistor R3 is simultaneously a first signal receiving end and a third signal sending end of the signal switching unit 21, the second end of the fourth resistor R4 is simultaneously a second signal receiving end and a fourth signal transmitting end of the signal switching unit 21, and the first end of the third resistor R3 and the first end of the fourth resistor R4 are connected to a first power source VCC in common.
As an embodiment of the present invention, the control unit 22 is a programmable logic control device U1, the first signal receiving pin I1, the second signal receiving pin I2, the first signal sending pin O1, and the second signal sending pin O2 of the programmable logic control device U1 are a first signal receiving terminal, a second signal receiving terminal, a first signal sending terminal, and a second signal sending terminal of the control unit 22, respectively, and the plurality of output pins (OUT 1 to OUTn) of the programmable logic control device U1 are a plurality of output terminals of the control unit 22, respectively.
In practical applications, the control unit 22 may also be implemented by a single chip, a microcontroller, or the like, and is specifically configured according to actual requirements, which is not limited herein.
In the embodiment of the present invention, when the detector 10 works in the tomography mode, the detector 10 is powered on and then actively sends a preparation signal to the first signal receiving pin I1 of the programmable logic control device U1, the programmable logic control device U1 receives the preparation signal and then sends a first feedback signal to the detector 10 through the first signal sending pin O1, the detector 10 receives the first feedback signal and then sends an exposure timing signal to the second signal receiving pin I2 of the programmable logic control device U1, the programmable logic control device U1 processes the exposure timing signal and generates a continuous pulse signal, and the continuous pulse signal is fed back to the detector 10 through the second signal sending pin O2, and meanwhile, the programmable logic control device U1 decomposes the continuous pulse signal into multiple single pulse signals and outputs the multiple single pulse signals through the multiple output pins (OUT 1 to OUTn).
In the embodiment of the present invention, the voltage of the first power supply is +3.3V, two paths of signals (a preparation signal and an exposure timing signal) output by the detector 10 are pulled up by a +3.3V level matched with an input/output pin of the programmable logic controller U1, and are clamped and current-limited by the third resistor R3 and the fourth resistor R4, and then are respectively input to the first signal receiving pin I1 and the second signal receiving pin I2 of the programmable logic controller U1, and two paths of signals (a first feedback signal and a continuous pulse signal) output by the programmable logic controller U1 through the first signal sending pin O1 and the second signal sending pin O2 are respectively current-limited by the first resistor R1 and the second resistor R2, and then are input to the first signal receiving terminal and the second signal receiving terminal of the detector 10.
As an embodiment of the present invention, the high voltage isolation unit 31 includes a fifth resistor R5, a photocoupler U2 and a sixth resistor R6.
The first end of the fifth resistor R5 is the input end of the high-voltage isolation unit 31, the second end of the fifth resistor R5 is connected with the second input end of the photoelectric coupler U2, the first input end and the first output end of the photoelectric coupler U2 are respectively connected with the second power supply VDD and the third power supply VEE, the second output end of the photoelectric coupler U2 and the first end of the sixth resistor R6 are jointly connected as the output end of the high-voltage isolation unit 32, and the second end of the sixth resistor R6 is grounded.
In the embodiment of the invention, the photoelectric coupling device U2 is used for electrically isolating the low-voltage side from the high-voltage side so as to prevent the high-voltage kilovolt in the high-voltage loop from entering the low-voltage loop to burn the programmable logic control device U1.
As an embodiment of the present invention, the high voltage pulse driving unit 32 includes a seventh resistor R7, a switching device Q1 and an eighth resistor R8.
The first end of the seventh resistor R7 is an input end of the high-voltage pulse driving unit 32, the second end of the seventh resistor R7 is connected to the control end of the switching device Q1, the low potential end of the switching device Q1 is grounded, the high potential end of the switching device Q1 is connected to the first end of the eighth resistor R8, and the second end of the eighth resistor R8 is an output end of the high-voltage pulse driving unit 32.
In the embodiment of the present invention, the switching device Q1 may be an Insulated Gate Bipolar Transistor (IGBT), a Gate of the IGBT is a control terminal of the switching device Q1, a source of the IGBT is a low potential terminal of the switching device Q1, and a drain of the IGBT is a high potential terminal of the switching device Q1. Of course, the switching device Q1 may also adopt other types of switching devices, such as a metal oxide semiconductor field effect transistor (MOSFET, abbreviated as MOS transistor), and the like, which are specifically set according to actual requirements and are not limited herein.
In the embodiment of the invention, the insulated gate bipolar transistor is used as a switch device, has the characteristics of high voltage resistance, higher working frequency and larger capacity, and can obtain higher switching speed and stronger current carrying capacity.
In the embodiment of the invention, as the on-state voltage of the insulated gate bipolar transistor is generally between 5 and 15V, the photoelectric coupling device U2 can raise the +3.3V level signal (i.e. single pulse signal) output by the programmable logic control device U1 to a 12V level signal while realizing isolation, so as to drive the insulated gate bipolar transistor.
In the embodiment of the present invention, the fifth resistor R5 is used for limiting the input current of the photo-coupler U2, and the sixth resistor R6 is used for clamping the output voltage of the photo-coupler U2.
In the embodiment of the present invention, the output of the low-voltage pulse-driven control gate high-voltage power supply is realized by the switching device Q1, that is, when the switching device Q1 is turned on, the field emission cathode of the cold-cathode field-induced X-ray source 41 is grounded through the resistor R8 to form a high-voltage loop, at this time, under the action of the high-voltage DC power supply DC, the field emission cathode of the cold-cathode field-induced X-ray source 41 emits an electron beam, and at the same time, the electron beam is accelerated by the high voltage of the anode, and bombards the target surface of the anode to generate X-rays.
In the embodiment of the invention, the seventh resistor R7 is connected to the control end of the switching device Q1 to inhibit the influence of the high-voltage loop surge voltage on the low-voltage pulse signal, and the eighth resistor R8 is connected to the high potential end of the switching device Q1 to limit the current. The eighth resistor R8 is a high-voltage resistor, and may be a glass glaze rod-shaped high-voltage resistor.
The embodiment of the invention also provides a tomography system which comprises a detector and a computer, and the tomography system also comprises the tomography control circuit.
In practical applications, the tomography system may be a digital breast tomography system, and may be other tomography systems, which are determined according to practical situations, and are not limited herein.
In the embodiment of the invention, a fault scanning control circuit comprising a detector, a driving module, a plurality of high-voltage control modules, a cold cathode field X-ray source array and a high-voltage direct-current power supply is adopted in a fault imaging system, and in a fault scanning mode, the detector sends a preparation signal to the driving module and sends an exposure time sequence signal to the driving module when receiving a first feedback signal sent by the driving module; the driving module outputs a plurality of paths of single pulse signals according to the exposure time sequence signal; the high-voltage control modules respectively control the emission time sequence of the cold-cathode field X-ray source array according to the multi-path single pulse signals so that the cold-cathode field X-ray sources sequentially emit X rays to a target object under the action of high anode voltage; the detector receives the X-ray penetrating through the target object, converts the received attenuated X-ray into two-dimensional projection data and outputs the two-dimensional projection data to the computer of the tomography system.
The above description is only for the purpose of illustrating the preferred embodiments of the present invention and is not to be construed as limiting the invention, and any modifications, equivalents and improvements made within the spirit and principle of the present invention are intended to be included within the scope of the present invention.
Claims (8)
1. The tomography control circuit of the tomography system is characterized by being connected with a detector of the tomography system and comprising a driving module, a plurality of high-voltage control modules, a cold cathode field X-ray source array and a high-voltage direct-current power supply; the cold cathode field X-ray source array comprises a plurality of cold cathode field X-ray sources which are arranged in a linear array, and the number of the cold cathode field X-ray sources is equal to that of the high-voltage control modules;
the signal receiving end and the signal sending end of the driving module are respectively connected with the signal sending end and the signal receiving end of the detector, a plurality of output ends of the driving module are respectively connected with input ends of the plurality of high-voltage control modules, output ends of the plurality of high-voltage control modules are respectively connected with field emission cathodes of the plurality of cold cathode field X-ray sources, grids of the plurality of cold cathode field X-ray sources are commonly connected with the anode of the high-voltage direct-current power supply, and the cathode of the high-voltage direct-current power supply is grounded;
in a tomography mode, the detector sends a preparation signal to the driving module, and sends an exposure time sequence signal to the driving module when receiving a first feedback signal sent by the driving module; the driving module outputs a plurality of paths of single pulse signals according to the exposure time sequence signal; the high-voltage control modules respectively control the emission time sequence of the cold cathode field X-ray source array according to the multi-path single pulse signals, so that the cold cathode field X-ray sources sequentially emit X rays to a target object under the action of anode high voltage; the detector receives the X-ray penetrating through the target object, converts the received attenuated X-ray into two-dimensional projection data and outputs the two-dimensional projection data to a computer of the tomography system;
the cold cathode field X-ray source is a cold cathode carbon nano X-ray tube;
the high-voltage direct current power supply is a constant-current high-voltage direct current power supply.
2. The tomography control circuit as claimed in claim 1, wherein the first signal transmitting end, the second signal transmitting end, the first signal receiving end and the second signal receiving end of the detector are respectively connected with the first signal receiving end, the second signal receiving end, the first signal transmitting end and the second signal transmitting end of the driving module, and the driving module comprises a signal switching unit and a control unit;
a first signal receiving end, a second signal receiving end, a first signal sending end and a second signal sending end of the signal transfer unit are respectively a first signal receiving end, a second signal receiving end, a first signal sending end and a second signal sending end of the driving module, a third signal sending end, a fourth signal sending end, a third signal receiving end and a fourth signal receiving end of the signal transfer unit are respectively connected with the first signal receiving end, the second signal receiving end, the first signal sending end and the second signal sending end of the control unit, and a plurality of output ends of the control unit are respectively a plurality of output ends of the driving module;
the signal switching unit is used for realizing signal transmission between the detector and the control unit; the control unit is used for processing the exposure time sequence signal output by the detector, outputting a continuous pulse signal and feeding back the continuous pulse signal to the detector, and meanwhile, decomposing the continuous pulse signal and outputting a plurality of paths of single pulse signals to the plurality of high-voltage control modules respectively; the pulse number of the continuous pulse signal is equal to the number of the multiple paths of single pulse signals.
3. The tomography control circuit of claim 1, wherein the high voltage control module comprises a high voltage isolation unit and a high voltage pulse drive unit;
the input end of the high-voltage isolation unit is the input end of the high-voltage control module, the output end of the high-voltage isolation unit is connected with the input end of the high-voltage pulse driving unit, and the output end of the high-voltage pulse driving unit is the output end of the high-voltage control module;
the high-voltage isolation unit is used for electrically isolating the driving module from the high-voltage pulse driving unit; and the high-voltage pulse driving unit is used for carrying out pulse exposure control on the cold cathode field X-ray source according to the single pulse signal.
4. The tomography control circuit as claimed in claim 2, wherein the signal switching unit comprises a first resistor, a second resistor, a third resistor and a fourth resistor;
the first end and the second end of the first resistor are respectively a first signal sending end and a third signal receiving end of the signal transfer unit, the first end and the second end of the second resistor are respectively a second signal sending end and a fourth signal receiving end of the signal transfer unit, the second end of the third resistor is simultaneously a first signal receiving end and a third signal sending end of the signal transfer unit, the second end of the fourth resistor is simultaneously a second signal receiving end and a fourth signal transmitting end of the signal transfer unit, and the first end of the third resistor and the first end of the fourth resistor are connected to a first power supply in a sharing mode.
5. The tomography control circuit as claimed in claim 2, wherein the control unit is a programmable logic control device, the first signal receiving pin, the second signal receiving pin, the first signal sending pin and the second signal sending pin of the programmable logic control device are respectively a first signal receiving end, a second signal receiving end, a first signal sending end and a second signal sending end of the control unit, and the plurality of output pins of the programmable logic control device are respectively a plurality of output ends of the control unit.
6. The tomography control circuit as claimed in claim 3, wherein the high voltage isolation unit comprises a fifth resistor, a photocoupler and a sixth resistor;
the first end of the fifth resistor is the input end of the high-voltage isolation unit, the second end of the fifth resistor is connected with the second input end of the photoelectric coupling device, the first input end and the first output end of the photoelectric coupling device are respectively connected with the second power supply and the third power supply, the second output end of the photoelectric coupling device and the first end of the sixth resistor are jointly connected to serve as the output end of the high-voltage isolation unit, and the second end of the sixth resistor is grounded.
7. The tomography control circuit according to claim 3, wherein the high voltage pulse driving unit includes a seventh resistor, a switching device, and an eighth resistor;
the first end of the seventh resistor is an input end of the high-voltage pulse driving unit, the second end of the seventh resistor is connected with a control end of the switching device, a low-potential end of the switching device is grounded, a high-potential end of the switching device is connected with the first end of the eighth resistor, and the second end of the eighth resistor is an output end of the high-voltage pulse driving unit.
8. A tomography system comprising a detector and a computer, characterized in that the tomography system further comprises a tomography control circuit as claimed in any of claims 1 to 7.
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| EP3795081A1 (en) * | 2019-09-20 | 2021-03-24 | Siemens Healthcare GmbH | Computer tomograph and method for operating a computer tomograph |
| CN111508814B (en) * | 2020-04-24 | 2023-03-31 | 北京卫星环境工程研究所 | Control circuit of electron source device of satellite-borne in-situ atmospheric composition detector |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101472525A (en) * | 2006-06-22 | 2009-07-01 | 皇家飞利浦电子股份有限公司 | Multi-source encoded x-ray imaging |
| CN103315761A (en) * | 2013-06-17 | 2013-09-25 | 深圳先进技术研究院 | Cone beam CT (computed tomography) system based on linear array ray source |
| CN103337443A (en) * | 2013-04-27 | 2013-10-02 | 中国人民解放军北京军区总医院 | X-ray source for medical testing and mobile CT (computer tomography) scanner |
| CN103340641A (en) * | 2013-04-27 | 2013-10-09 | 中国人民解放军北京军区总医院 | System and method for pulse imaging of CT scanner |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7227924B2 (en) * | 2000-10-06 | 2007-06-05 | The University Of North Carolina At Chapel Hill | Computed tomography scanning system and method using a field emission x-ray source |
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2016
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Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101472525A (en) * | 2006-06-22 | 2009-07-01 | 皇家飞利浦电子股份有限公司 | Multi-source encoded x-ray imaging |
| CN103337443A (en) * | 2013-04-27 | 2013-10-02 | 中国人民解放军北京军区总医院 | X-ray source for medical testing and mobile CT (computer tomography) scanner |
| CN103340641A (en) * | 2013-04-27 | 2013-10-09 | 中国人民解放军北京军区总医院 | System and method for pulse imaging of CT scanner |
| CN103315761A (en) * | 2013-06-17 | 2013-09-25 | 深圳先进技术研究院 | Cone beam CT (computed tomography) system based on linear array ray source |
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