Patent Grant
11064960
The present disclosure generally relates to a system and method for digital radiography imaging. Particularly, the present disclosure relates to a system and method for X-ray imaging.
Digital radiography (DR) is an advanced imaging technology, which combines the computer digital image processing and the X-ray emission technology. According to its advantages of low radiation doses, high image quality, high detection rate, and high accuracy, digital radiography has been widely used in many fields, such as aerospace, security, healthcare, etc. In medical digital radiography, X-ray signal is generated by a generator, and radiated to an imaging target such as a human body or other subjects. Then the X-ray signal can be detected by an X-ray detector, such as a flat panel detector. After a series of processes, an image of the radiated area can be formed, which may be used in disease diagnosis, medical research and other aspects.
According to one aspect of the present disclosure, provided herein is a digital radiography system. Particularly, in some embodiment, the digital radiography system comprises an X-ray generation module, an X-ray acquisition module, a support module, a power supply module and a control module. In some embodiments, one or more of modules of the system comprise at least one moving component, the moving component comprising a sensing unit; the sensing unit is configured to obtain positional information of the moving component, and the control module is configured to control motion of the moving component based on said positional information.
In some embodiments, the positional information comprises distance between the moving component and a nearby object, and the control module further comprises a judgment unit capable of comparing the distance to a threshold; and the control module is configured to adjust speed of the motion, route of the motion or both, when the distance reaches the threshold.
In some embodiments, the moving component may be an X-ray detector, an X-ray tube, a ceiling suspension unit, a beam limiting device or a tube stand, and wherein the tube stand connects the X-ray tube and the ceiling suspension unit.
In some embodiments, the sensing unit is a photoelectric sensor or a linear proximity sensor.
In some embodiments, the control module digital radiography system further comprises a setting unit configured to set a target position for the moving component; a position unit configured to obtain instant position of the moving component and instant position of at least one obstacle; a calculation unit configured to calculate all axial speeds for the moving component, when the instant position of the moving component is different from the target position; and a control unit configured to move the moving component under the calculated axial speeds.
In some embodiments, the calculation unit calculates the axial speeds by determining a first collision area for the moving component and a second collision area for the obstacle; calculating a repulsive force by the obstacle; calculating an attractive force by the target position; calculating a net force of the attractive force and the repulsive force; and determining all axial speeds for the moving component.
In some embodiments, determining the first collision area and the second collision area is performed by finding a first rotating center of the moving component and a second rotating center of the obstacle; defining a first spherical space as the first collision area, the first spherical space having the first rotating center as spherical center, and the first spherical space enclosing the moving component; and defining a second spherical space as the second collision area, the second spherical space having the second rotating center as spherical center, and the second spherical space enclosing the obstacle.
In some embodiments, calculating the repulsive force is performed by calculating the repulsive force when DFT≤Dmax. Particularly,FTX=KF
FTX/DFT2
FTZ=KF
FTZ/DFT2
where DFT is distance between the first collision area and the second collision area; FTX is X component of DFT;
FTZ is Z component of DFT; Dmax is a threshold distance where the obstacle starts to exert the repulsive force;
FTX is X component of the repulsive force;
FTZ is Z component of the repulsive force; and KF is a proportionality coefficient.
In some embodiments, calculating the attractive force is performed by calculating the attractive force when Dg≥Dmin. Particularly,
where goalX is X component of the attractive force;
goalZ is Z component of the attractive force; Kg is a proportionality coefficient; Dmin is a threshold distance between the target position and the current position of the moving component; Dgoal is a distance between the target position and the current position of the moving component, Drun is a minimum threshold for the attractive force;
goalX is X component of Dgoal; and
goalZ is Z component of Dgoal.
In some embodiments, determining all axial speeds for the moving component is performed by
where x is X axial speed;
z is Z axial speed;
x is net force in X axis;
z is net force in Z axis; Kv is transformation proportionality coefficient between force and speed;
maxX is maximum speed in X axis; and
maxX is maximum speed in Z axis.
In some embodiments, both the moving component and the obstacle are components of the digital radiography system. Particularly, in some embodiments, the obstacle is another moving component of the system.
In some embodiments, the system, when determining the motion path of a moving component, may treat another moving components of the system as an obstacle. For example, in some embodiments, the moving component is the X-ray acquisition module and the obstacle is the X-ray generation module. In some embodiments, the moving component is the X-ray generation module and the obstacle is the X-ray acquisition module.
In some embodiments, the X-ray acquisition module comprises a chest board enclosing the X-ray detector, and the X-ray generation module comprises the X-ray tube and the beam limiting device.
According to one aspect of the present disclosure, provided herein are device and method for path planning of an object with respect to an obstacle. Particularly, In some embodiments, the device comprises a setting unit configured to set a target position for the object; a position unit configured to obtain instant position of the object and instant position of the obstacle; a calculation unit configured to calculate all axial speeds for the object, when the instant position of the object is different from the target position; and a control unit configured to move the object under the calculated axial speeds.
In some embodiments, the method comprises setting an target position for the object; obtaining instant position of the object and instant position of the obstacle; determining a first collision area for the object and a second collision area for the obstacle; calculating a repulsive force by the obstacle; calculating an attractive force by the target position; calculating a net force of the attractive force and the repulsive force; and determining all axial speeds for the object.
According to one aspect of the present disclosure, provided herein are a digital radiography system comprising different configurations and a method for selecting among the configurations. Particularly, in some embodiments, one or more of modules of the system form a vertical configuration, a horizontal configuration and a free-style configuration; the vertical configuration comprises a vertical stand and a vertical X-ray acquisition module, the vertical X-ray acquisition module coupled to the vertical stand; the horizontal configuration comprises a bed component and a horizontal X-ray acquisition module, the horizontal X-ray acquisition module coupled to the bed component; the control module further comprises a detection unit configured to detect existence of an imaging target in one of the vertical and horizontal configurations; and the control module is configured to select the vertical or horizontal configuration based on the detected existence.
In some embodiments, the control module further comprises a timing unit configured to time the detected existence, and the control module is configured to select the vertical or horizontal configuration if the detected existence persists for a predetermined period of time.
In some embodiments, the vertical and horizontal X-ray acquisition modules each comprises an X-ray detector, an ionization chamber and a filter grid.
In some embodiments, the control module is further configured to activate the ionization chamber and the filter grid of the selected vertical or horizontal configuration.
In some embodiments, the control module is further configured to determine if the X-ray detector of the selected vertical or horizontal configuration is ready for image acquisition.
In some embodiments, the control module is further configured to select the free-style configuration if the existence of the imaging target is not detected.
In some embodiments, the detection unit is an infrared detector.
According to one aspect of the present disclosure, provided herein is a device for moving components of the digital radiography system. Particularly, In some embodiments, the system comprises a support beam having a length; the support beam comprises a first column, the first column having a first side along the length of the support beam; the support beam comprise a second column, the second column having a second side along the length of the support beam and a pair of opposing sides along the length of the support beam; the first side attaches to the second side and at least part of the first side is uncovered by the second side; the pair of opposing sides each comprises a prolonged guiding ridge along the length of the support beam; and the support beam further comprises a slider capable of engaging with the guiding ridges and moving along the length of the support beam.
In some embodiments, the support beam further comprises a housing between the second column and the slider, and wherein the housing encloses the second column.
In some embodiments, the slider is configured to connect a moving component of the system.
In some embodiments, the support beam further comprises a driving mechanism for moving the slider.
According to one aspect of the present disclosure, provided herein is an exposure controller for controlling generation and emission X-ray by the system. Particularly, In some embodiments, the exposure controller has a elongated handle, a double gear button and a switch, the elongated handle having a first end, a second end and a side; the double gear button is located on the first end of the handle, and the switch is located on the side of the handle.
In some embodiments, the exposure controller further comprises a protective groove and a movable baffle; the protective groove extends inwardly on the side of the handle; the switch is located within the groove; the movable baffle is configured to move between at least a first position and a second position; when the movable baffle is in the first position, the switch is accessible; and when the movable baffle is in the second position, the switch is inaccessible.
In some embodiments, the double gear button comprises a first gear and a second gear; the exposure controller is configured to send an exposure preparation signal to the X-ray generation module when the first gear is pressed; and the exposure controller is configured to send a first exposure permitting signal to the X-ray generation module when the second gear is pressed.
In some embodiments, the switch is configured to send a second exposure permitting signal to the X-ray generation module.
In some embodiments, the X-ray generation module is configured to generate X-ray when both the first and second exposure permitting signals are received.
In some embodiments, the exposure controller further comprises at least one audio device. In some embodiments, the audio device is a microphone. In some embodiments, the switch is a micro switch, a stir switch or a touch sense switch.
According to one aspect of the present disclosure, provided herein is a power supply system. Particularly, in some embodiments, power supply system comprises a power connector, a charge up circuit, a battery, a capacitor and a high-voltage generator; the power connector is configured to connect the charge up circuit to a power network; the charge up circuit is configured to supply power to the battery; the battery is configured to supply power to the capacitor; and the capacitor is configured to supply power to the high-voltage generator.
In some embodiments, the power supply system further comprises a current limiting charge up unit configured to supply power to the capacitor with a current limit.
In some embodiments, the power supply system comprises a power connector, a charge up circuit, a battery, a current limiting charge up circuit, a voltage limiting charge up circuit, a capacitor, and a high-voltage generator. Particularly, the power supply system is capable of selecting between at least a first circuit and a second circuit; in the first circuit, the power connector is configured to connect the voltage limiting charge up circuit to a power network; the voltage limiting charge up circuit is configured to supply power to the capacitor with a voltage limit; and the capacitor is configured to supply power to the high-voltage generator; and in the second circuit, the power connector is configured to connect the charge up circuit to the power network; the charge up circuit is configured to supply power to the battery; the battery is configured to supply power to the current limiting charge up circuit; the current limiting charge up circuit is configured to supply power to the capacitor with a current limit; and the capacitor is configured to supply power to the high-voltage generator.
In some embodiments, the power supply system is capable of selecting among at least the first circuit, the second circuit and a third circuit. Particularly, in the third circuit, the power connector is configured to simultaneously connect both the high-voltage generator and the charge up circuit to the power network; the charge up circuit is configured to supply power to the battery; the battery is configured to supply power to the current limiting charge up circuit; the current limiting charge up circuit is configured to supply power to the capacitor with a current limit.
In some embodiments, the power supply system further comprises a converter configured to convert one or more characteristics of the supplied power. In some embodiments, the converter is an AC/DC converter or a voltage transformer.
In some embodiments, the power supply system further comprises a battery level indicator configured to monitor a power level of the battery; and the battery level indicator is configured to stop power supply from the battery to the capacitor, when the power level of the battery decreases to a pre-determined battery level threshold.
In some embodiments, the power supply system further comprises a capacitor level indicator configured to monitor a power level of the capacitor; and the capacitor level indicator is configured to stop power supply from the capacitor to the high-voltage generator, when the power level of the capacitor decreases to a pre-determined capacitor power level threshold.
In some embodiments, the capacitor level indicator further comprises a calculation sub-unit configured to calculate a number of times the high-voltage generator can work until power in the capacitor runs out. In some embodiments, the capacitor level indicator further comprises a display sub-unit configured to display the calculated number.
In some embodiments, the power supply system is configured to automatically select the first circuit when power level of the battery is low. In some embodiments, the power supply is configured to manually select the second circuit.
The present disclosure is further illustrated as exemplary embodiments. These exemplary embodiments are described in details with reference to the accompanying drawings. The drawings, which are incorporated in and constitute a part of this specification, illustrate several aspects described below. What illustrated in the drawings are non-limiting exemplary embodiments, in which like reference numerals represent similar structures throughout the several views of the drawings, and wherein:
In the following detailed description, numerous specific details are set forth by way of examples in order to provide a thorough understanding of the relevant disclosure. However, it should be apparent to those skilled in the art that the present disclosure may be practiced without such details. In other instances, well known methods, procedures, systems, components, and/or circuitry have been described at a relatively high-level, without detail, in order to avoid unnecessarily obscuring aspects of the present disclosure.
These and other features, and characteristics of the present disclosure, as well as the methods of operation and functions of the related elements of structure and the combination of parts and economies of manufacture, may become more apparent upon consideration of the following description with reference to the accompanying drawing(s), all of which form a part of this specification. It is to be expressly understood, however, that the drawing(s) are for the purpose of illustration and description only and are not intended to limit the scope of the present disclosure. As used in the specification and in the claims, the singular forms of “a”, “an”, and “the” include plural referents unless the context clearly dictates otherwise.
After reading this description, it will become apparent to one skilled in the art how to implement the disclosure in various alternative embodiments and alternative applications. However, not all embodiments of the present disclosure are specifically described herein. It will be understood that the embodiments are presented by way of example only, and not limitation. As such, this detailed description of various alternative embodiments should not be construed to limit the scope or breadth of the present invention as set forth below.
According to one aspect of the present disclosure, provided herein are digital radiography systems.
Particularly, the support module 102 may include any mechanical part that fixes, supports, and/or moves a component of the system. For example, in one embodiment, the support module 102 may include a vertical stand that fixes, supports and/or moves an X-ray acquisition device of the X-ray acquisition module 106 (A specific illustration of this embodiment is provided in
The control module 103 may be configured for controlling the functions and operations of the system. The controlled function and operation may include moving and positioning a system component, such as moving an X-ray generation module 104 into close proximity of an imaging target, or adjusting an X-ray acquisition module 106 into an optimal angle with respect to the target, etc. Particularly, the control module 103 may calculate various preferred parameters, including but not limited to the route and speed of the movement, and execute the movement accordingly. More particularly, in some embodiments, the control module 103 may calculate the movement based on proximity sensing. Additionally or alternatively, the control module 103 may calculate the movement using an artificial potential field method. Further detailed disclosure regarding the artificial potential field method is provided in
Further, the controlled function and operation may also include the system's data acquisition, such as generating X-ray images of an imaging target. For example, the control module 103 may control the ON/OFF status of the X-ray generation module 104, control the ON/OFF status of power supply to the X-ray generation module 104, and calculate preferred parameters for X-ray generation and acquisition, etc. Particularly, in some embodiments, the control module 103 may control X-ray exposure conditions for image acquisition, execute or stop acquisition under a specific condition, and calculate preferred exposure parameters, etc. The control module 103 may include one or more control units (not shown in
The structures and functions described above in relation to the control module 103 are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims. For example, in some embodiments, the control module 103 may be integrated into the processing module 105 that executes the control functions directly. Alternatively, in other embodiments, the control module 103 may execute the control functions based on one or more instructions sent by the processing module 105. Yet alternatively, in some embodiments, the control module 103, some or all of the control units (not shown in
The X-ray generation module 104 may be configured for generating and/or emitting X-rays. The X-ray generation module 104 may connect to or otherwise communicate with the control module 103 and the processor 105. The X-ray generation module 104 may include one or more X-ray generation units (not shown in
The processing module 105 may be configured to perform a plurality of operations during a running process of the system. The operations may include analysis, calculation, identification, or the like, or a combination thereof. The processor 105 may connect to or otherwise communicate with the X-ray generation module 104, the X-ray acquisition module 106 and the control module 103. The connection or the communication may be wired or may be wireless. The processing module 105 may include a digital signal processor (DSP), or a SoC (system on the chip), or a microprocessor, or the like, or the combination thereof. The processing module 105 may be integrated into another module within the operation module 110, or may be an independent component of the operation module 110. Additionally, each module in the operation module 110 may have its own independent processor. The processing module 105 may further include a cache memory (such as SRAM), which may be part of a memory hierarchy to store instructions and data. The processing module 105 may also include one or more logic modules (not shown in
The X-ray acquisition module 106 may be configured for acquiring an X-ray signal relating to one or more imaging targets. The X-ray acquisition module 106 may be arranged on the support module 102 (such as a vertical stand). In some embodiments, the X-ray acquisition module 106 may be in either a vertical or horizontal arrangement with respect to the space where image acquisition takes place (such as an X-ray imaging room), or the imaging target (such as a patient). Alternatively, in other embodiments, the X-ray acquisition module 106 may assume any angle with respect to the imaging space or target. The X-ray acquisition module 106 may include one or more units (not shown in
The structures and functions described above in relation to the operation module 110 are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims. For example, in some embodiments, the control module 103 is not needed, and, the X-ray generation module 104, the X-ray acquisition module 106 and the support module 102 may include one or more integrated control units (not shown in
The power supply module 101 may be configured to supply power for one or more modules or components of the system. In some embodiments, the power supply module 101 may include a battery, such as but not limited to lithium battery, lead acid storage battery, nickel-cadmium battery, nickel metal hydride battery, or the like, or a combination thereof. In some embodiments, the power supply module 101 may include an external power source, such as but not limited to a power network with a household power outlet socket or industrial power outlet socket, or the like, or a combination thereof. The power supply module 101 may provide direct current (DC) power, or alternating current (AC) power. The power supply module 101 may include one or more internal components, including but not limited to a switch, a converter, a charge/discharge interface, or the like, or a combination thereof. Further detailed disclosure regarding the power supply module 101 is provided in
The input/output module 107 may be configured for inputting information related to the system, and/or outputting results generated by the system. The transmission of the input or output may be via a wired connection, or via a wireless connection. The input or output may be transmitted in real time, or may be transmitted with a time delay. The input or output may be in the format of, for example, a graph, a code, a voice message, text, video, an audio alert, a haptic effect, or the like, or a combination thereof. The input/output module 107 may be an input equipment, such as a keyboard, a mouse, a trackball, or cursor direction keys to convey information about direction and/or command selections to, for example, a processer. The input/output module 107 may be an output equipment, such as a display screen. Merely by way of example, the output may be displayed on a local terminal, or transmitted to a remote terminal, or both. A terminal may include, for example, a personal computer (PC), a desktop computer, a laptop computer, a smart phone, or a combination thereof.
Particularly, the vertical configuration components 2290 may include a vertical X-ray acquisition device 2202 installed on a vertical stand 2201. In various embodiments, the vertical X-ray acquisition device 2202 may include an X-ray detector, an ionization chamber, or a filter grid, or a combination thereof. The vertical X-ray acquisition device 2202 may move up and down the vertical stand 2201, thereby reaching an optimum location for X-ray image acquisition. For example, in some embodiments, a patient may stand in front of the vertical stand 2201. Thus, positions of the vertical X-ray acquisition device 2202 and the X-ray generation module 2206 may be adjusted according to the patient's position relative to the vertical stand 2201 as well as the body part to the imaged.
The horizontal configuration components 2280 may include a horizontal X-ray acquisition device 2204 installed on a bed component 2203. Similarly, the horizontal X-ray acquisition device 2204 may include an X-ray detector, an ionization chamber, or a filter grid, or a combination thereof. The horizontal X-ray acquisition device 2204 may move horizontally in the bed plane, thereby reaching an optimum location for X-ray image acquisition. For example, in some embodiment, a patient may lay flat on the bed component 2203. Thus, positions of the horizontal X-ray acquisition device 2204 and the X-ray generation module 2206 may be adjusted according to the patient's position relative to the bed as well as the body part to be imaged.
In some embodiment, the digital radiography system may detect the position of a patient or other imaging target, thereby detecting which of the vertical and horizontal configurations should be selected in the operation. Particularly, in some embodiment, the vertical configuration components 2290 further include a detection unit 2203, and the horizontal configuration components 2280 further include a detection unit 2205. In various embodiments, the detection units (2203, 2205) may be of the same type or different, such as an infrared sensor, or any sensor or sensing device that may be used for detecting an existence of an imaging target.
The structures and functions described above are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims. For example, the first detection unit 2203 and the second detection unit 2205 may be a detachable device which may be placed on any other particular component while needed. In another example, the first detection unit 2203 and the second detection unit 2205 may be controlled by a wireless remote tele-control device (such as an infrared remote controller).
In some embodiments, the digital radiography system may also include a free-style configuration, where the imaging components may assume any angle with respect to the imaging space or imaging target.
Particularly, as shown in
In some embodiments, the vertical stand 220 may be installed on the ground plane parallel to the XY-plane in the three-dimensional coordinate system shown in
The X-ray tube 260 may be mounted on the tube stand 250, which in turn connects with the ceiling suspension unit 240. The beam limiting device 270 may be mounted proximal to the X-ray tube 260. The tube stand 250 may include a first stand unit 201 and a second stand unit 202. The first stand unit 201 may be at an angle with the second stand unit 202. For example, the first stand unit 201 may be perpendicular to the second stand unit 202. In some embodiments, the X-ray tube 260 and the beam limiting device 270 may rotate for a certain angle in the XY-plane and/or the XZ-plane in the three-dimensional space. In some embodiments, the tube 260 and the beam limiting device 270 may move in the Z-axis direction through the extension or retraction of the ceiling suspension unit 240. In some embodiments, the tube 260 and the beam limiting device 270 may move in the X-axis direction along the moving guide 280.
As will be further appreciated from
For the convenience of illustration only,
Also for the convenience of illustration only,
The aforementioned motion control signal may be generated based on the sensing result and the threshold. For example, if the sensing result exceeds the threshold, a stop signal may be generated. If the sensing result is within a permissible range close to the threshold, a slow-down signal or a tilt signal may be generated.
In other embodiments, additional proximity sensors (not shown in
The structures and functions described above in relation to the proximity sensor are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims. For example, the multiple independent proximity sensors in the system may be replaced by a proximity sensor array. The proximity sensor array may include a series of sensors, arranged according to a specific rule.
Particularly, as shown in
For example, as shown in
The control module 103 controls and coordinates the movement of system components. As mentioned above, one or more proximity sensors may be used. For example, in some embodiments, the proximity sensor generates sensing results, which may include but are not limited to the speed or route information of the move, location and movement of other nearby objects, and remaining distance between the nearby objects and the moving system component, etc. The sensing results may be transmitted to an analysis unit (not shown in
As used herein, the preset threshold refers to a value corresponding to one or more parameter of an operation, and when the operational parameter approaches or reaches the threshold, the system will be triggered to act in response. Particularly, the threshold may be a single value or a value range. The system's reaction when a threshold is approached or reached may include but are not limited to stopping the operation, reversing the operation, adjusting one or more parameters of the operation, etc. The threshold may be set by the system default, or by a system operator, such as medical practitioners (e.g., a doctor) or other end users.
Take the operation of moving a system component as an example. A proximity sensor sends sensing results to the control module 103, which may include but are not limited to speed or route information of the move, location and movement of nearby objects, and remaining distance between the nearby objects and the moving system component. When, for example, the remaining distance approaches a preset distance value or falls within a preset distance range, the control module 103 may react by reducing the moving speed and/or tilting the moving angle of the moving system component and/or other moving object that controlled by the system. For example, when the remaining distance reaches a present distance value, the control module 103 may react by stopping or reverse the movement of the system component.
More particularly, referring to
In some embodiments, the control module 103 may include one or more control units (not shown in
The structures and functions described above in relation to the movement control are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims. For example, in some embodiments, separate control units may not be needed, as the control module 103 may be configured for performing the control function independently. In some embodiments, the control module 103 may be replaced by the processing module 105. In other embodiments, the control module 103 and the processing module 105 may be integrated into one independent module or an independent device that performs the control functions for the system.
According to one aspect of the present disclosure, provided herein is a system for moving system components to specific positions according to particular needs in practice.
As shown in
In some embodiments, the slider 601 may include sets of sliding wheels (not shown in
Additionally, to stabilize the sliding, such as preventing swaying of the slider 601 as it moves along the guiding ridges 504, additional sets of sliding wheels may be used. Particularly, in different embodiments, the slider 601 may include one or more additional sets of sliding wheels that run against surfaces of the first and second columns (501 and 502) to stabilize the sliding. Merely by way of example and not indented to be limiting, the one or more additional sets of sliding wheels may run against surface 505 of the first column 501, and/or surface 506, 507 and/or 508 of the second column 502.
In the above embodiments, each set of sliding wheels may include one or more rows of sliding wheels according to specific needs in practice. Yet, in other embodiments, sliding wheels may not be needed for the sliding. Alternatively, in those embodiments, the slider 601 may include sliding surfaces which substitute the function of sliding wheels to engage the guiding ridges 504 and/or stabilize against the column surfaces (e.g., 505, 506, 507, 508, etc.) for the sliding.
As shown in
In some embodiments, the support beam may further include a driving mechanism for moving the slider. For example, in some embodiments, the support beam 500 may include a motor. Particularly, in those embodiments where the support beam 500 is used to move system components vertically, the support beam 500 may further include a matching weight unit such that the motor only needs to exert a relatively small force for elevating or lowering the system component.
In some embodiments the support 801 may not be needed, as the system component 802 may connect to the slider 601 directly. In other embodiments, the slider 601 may connect to an object external to the system, such as an imaging target. As such, the support beam 500 may be used to move and position a system component 802 or other objects to a particular location for image acquisition. More detailed descriptions of the support beam 500 and the slider 601 may be found in
Further, it should be noted that although
The structures and functions described above in relation to the support beam 500 are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims. For example, in some embodiments, the second column 502 may be a bulge forming on the surface 505 of the first column 501. The method for connecting the first column 501 and the second column 502 includes but is not limited to riveting, soldering, fixing screws, integral forming, or the like, or a combination thereof. The method for connecting the guiding ridges 504 and the second column 502 includes but is not limited to riveting, soldering, fixing screws, integral forming, or the like, or a combination thereof. The method for connecting the system component 802 and the support component 801 includes but is not limited to riveting, soldering, fixing screws, integral forming, or the like, or a combination thereof. The support beam 500 may be made of metal materials (such as aluminum, steel, etc.), non-metallic materials, metamaterials or the like, or a combination thereof. The material of the first column 501 and the second column 502 may be the same or different. The shapes of the first column 501 and the second column 502 may be the same or different, which include but are not limited to rectangular, round, polygon, irregular shape, or the like, or a combination thereof. The slider 601 may be made by soldering materials which include but are not limited to aluminum, steel, metal plate, or the like, or a combination thereof. The housing 701 may be made by bending materials which include but are not limited to aluminum, steel, metal plate, or the like, or a combination thereof.
According to one aspect of the present disclosure, the digital radiography system may further include an exposure controller for an end user to control and operate the system more easily and conveniently. The exposure controller provides a hardware controlling mechanism that may either supplement or replace a software controlling mechanism of the system, thereby increasing safety.
Referring to
In some embodiments, the communication unit 901 may enable communication 1) between the exposure controller 910 and other modules or components of the system (such as those control generation and emission of X-ray in the system); or 2) between the exposure controller 910 and an end user; or 3) between different end users. As used herein, an end user of the digital radiography system generally refers to any human subject that operates (such as a medical practitioner) or being examined by the system (such as a patient). Communications via the communication unit 901 may be in a wired and/or wireless fashion, and may include, for example, audio communications, video communications, mechanical contact, and other suitable types. For example, an end user may send commands to the system via the exposure controller 910, such as by providing a body gesture (such as pressing a button or stomping a foot paddle, etc.) or a voice command, etc. Further, an end user may communicate with another end user via the exposure controller 910.
The support unit 903 generally refers to any mechanical component of the exposure controller 910, such as but not limited to a handle, a paddle, a button, a switch, a protecting case, etc.
In some embodiments, the protection unit 904 functions to prevent accidentally sending undesired commands to the system by error triggering. For example, in the field of digital radiography, a situation that the protection unit 904 aims to prevent would be accidentally or erroneously triggering the system to emit X-ray when a patient, a medial practitioner and/or another system component is not yet ready for X-ray image acquisition. In some embodiments, the exposure control unit 905 functions to monitor and control radiation emission by the digital radiography system. For instance, the exposure control unit 905 may control the ON/OFF status of X-ray emission, as well as the intensity and duration of X-ray emission.
As can be appreciated from further detailed descriptions of specific embodiments of the exposure controller 910, function-wise, the aforementioned functional units (901, 903, 904, 905) work in concert to enable safe and convenient operation of the system by an end user. Yet, structure-wise, these functional units may each has its own independent hardware components or share one or more common hardware components.
Referring to
The movable baffle 1003 may move relatively to the protective groove 1007, and has at least two positions. Left panel 1010 illustrates the first position of the movable baffle 1003 relative to the protective groove 1007; in the first position, at least part of the protective groove 1007 is exposed and an end user may access the switch 1001. Right Panel 1020 illustrates the second position of the movable baffle 1003; in the second position, the groove 1007 is enclosed by the movable baffle 1003, and an user cannot access the switch 1001. In some embodiments, the protective groove 1007 has indentations (not shown in
When in use, this embodiment of the exposure controller 910 provides several safety features to prevent accidentally or erroneously triggering X-ray exposure. Particularly, in some embodiments, an end user need to both turn on the switch 1001 and press down the double gears (1004 and 1005), in order to trigger X-ray exposure. Specifically, for a user to access the switch 1001, the movable baffle 1003 needs to be at the first position. In some embodiments, the movable baffle 1003 is configured to 1) stay in the second position until a user moves it, and 2) return to the second position after the user release it. Thus, in these embodiments, the user always needs to go through the step of moving the baffle 1003 before activating X-ray exposure.
Additionally, in some embodiment, the switch 1001 may be an auto-lock switch. In these embodiments, a user needs to press the switch 1001 once to turn it ON, and press again to turn it OFF. In other embodiments, the switch may be a self-reset switch. Particularly, in these embodiments, the user needs to press and hold the switch 1001 to turn it ON, and the switch 1001 automatically turns off when released. Thus, in these embodiments, the user always need to go through the step of turning on the switch 1001 before activating X-ray exposure. Particularly, in those embodiments where the switch 1001 is a self-reset switch, the user further needs to press and hold it to complete X-ray exposure.
Further, in some embodiments, a user need to press down both gears (1004, 1005) to activate X-ray exposure. Particularly, in some embodiments, when the user presses down the first gear 1004, the exposure controller 910 sends a preparation signal to the X-ray generation module 104; when the user presses further down to the second gear 1005, the exposure controller 910 sends the exposure signal to the X-ray generation module 104. Thus, in these embodiments, the user always needs to go through the step of pressing down double gears (1004, 1005) before activating X-ray exposure. Particularly, in those embodiments, where the switch 1001 is a self-reset switch, the user may need to use two fingers, one pressing and holding the switch 1001 and the other pressing down the double gears (1004, 1005) to activate X-ray exposure.
In some embodiments, the exposure controller 910 functions as a supplement to software exposure controlling mechanism. In other embodiments, the exposure controller 910 functions independently without a software mechanism,
In various embodiments, the exposure controller 910 may send signals to the X-ray generation module 104 in a wired or wireless fashion. Particularly, for wired signal transmission, signal lines 1008 may be used to connect the exposure controller 910 and X-ray generation module 104. Particularly, shielded wires can be used to shield signal transmission from interferences. Alternatively, for wireless signal transmission, both the exposure controller 910 and the X-ray generation module 104 may include corresponding wireless transmission devices. Accordingly, in these embodiments, the exposure controller 910 may not include the signal line 1008.
In various embodiments described above, the X-ray generation module 104 may include a high-voltage generator (not shown in
The switch 1001 may be various types, such as a micro-switch, stir switch, touch sense switch and other mechanical switch or soft switch. The protective groove 1007 and movable baffle 1003 may have various shapes, such as square, rectangular, round, oval, polygonal, or cambered, etc., according to particular needs in practice. The handle 1006 may have additional surface structures and/or textures according to particular need in practice, including but not limited to grooves, embossments, gripping, and/or other suitable structures or profiles, which may provide convenience and comfort for a user to hold the exposure controller 910 for a prolonged period.
The structures and functions described above in relation to the exposure controller 910 are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims.
In practice, communication between end users of the system may be performed before activating X-ray exposure. For instance, a doctor may require a patient to make and maintain in a particular body posture before image acquisition. Accordingly, in some embodiments, the exposure controller 910 further includes an audio device that enables communication between the end users. In addition to communication between end users, in some embodiments, the audio device 1101 may be configured to transit voice commands of an end user to the control module 103 of the system.
Particularly, integrating an audio device into the exposure controller 910 can have several advantageous. First, it can make the operation of the system more easy and convenient for an end user (such as a doctor). For example, when operating the exposure controller with both hands, a doctor can simply talk to the nearby audio device on the exposure controller 910, instead of approaching a faraway audio device, such as one on the console. Further, incorporating an audio device onto the exposure controller 910 may improve communication quality and safety of the system, as well as reduce cost of the system to some extent.
In various embodiments, the exposure controller 910 may send voice communication in a wired or wireless fashion. Particularly, for wired communication, signal lines 1008 may be used to connect the exposure controller 910 to the control module 103 and/or a loudspeaker (not shown) in the imaging room. Particularly, shielded wires can be used to shield communication from interferences. Alternatively, for wireless signal transmission, the exposure controller 910, the control module 103 and/or the loudspeaker may include corresponding wireless transmission devices. Accordingly, in these embodiments, the exposure controller 910 may not include the signal line 1008.
According to one aspect of the present disclosure, provided herein is a power supply system. The power supply system is configured to supply power through a high-voltage generator 1203, and thus can supply power to medical imaging devices including but not limited to the present digital radiography system.
The power storage unit 1202 may be any kind of equipment that can store and supply power. In one embodiment, the power storage unit 120 may include a battery (such as a fuel cell, electrochemical cell, etc.), an energy-storage element (such as a capacitor, inductor, etc.), or the like, or a combination thereof. For example, the power storage unit 1202 may be the battery 1303 or capacitor 1304 as shown in
The high-voltage generator 1203 may be any kind of equipment that may generate a high electric voltage. For example, the high-voltage generator 1203 may be a direct current (DC) high-voltage generator, alternating current (AC) high-voltage generator, or the like, or a combination thereof. In one embodiment, the high-voltage generator 1203 may share one power storage unit 120 with other devices. For example, the high-voltage generator 1203, X-ray detector 415, motor driver 401-407, and motor 408-414 as shown in
The charging unit 1204 may be configured to charge a power storage unit 120 using a power supply. For example, the power supply may be from a power network, a battery or an energy-storage element, or the like, or a combination thereof. The charging method of the charging unit 1204 may be wire or wireless. For example, the charging unit 1204 may charge a power storage unit 120 using an electromagnetic field. In some embodiment, the charging unit 1204 may include some control circuits (not shown in
The monitor unit 1206 may be configured to monitor the power of the power storage unit 1202. For example, the monitor unit 1206 may be a battery level indicator 1501 or a capacitor level indicator 1503 as shown in
The converter unit 1207 may be configured to convert the electrical characteristics (such as voltage, current, frequency, power-phase, etc.) of the power storage unit 1202. In some embodiments, the converter unit 1207 may be a rectifier circuit (such as converting direct current to alternating current, converting one direct current to another direct current, etc.), a power inverter (such as converting direct current to alternating current), an AC frequency converter, a DC transformer, or the like, or a combination thereof. The converter unit 1207 may connect to the power storage unit 1202 and a power consumption equipment (e.g., high-voltage generator 1203.).
The structures and functions described above in relation to the power supply system 1200 are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims. For example, the power storage unit 1202 may be replaced by a power network.
The power connector 1301 may be configured for connecting the charge up circuit 1302 with a power supply. In some embodiments, the power connector 1301 may be a one-pin plug, two-pin plug, three-pin plug, four-pin plug, or the like, or a combination thereof. For example, the power connector 1301 may be a UL-NEMA 5-15 USA 3 pin plug to connect an outlet socket of a power network. In another example, the power connector may be a 2-pin plug without the earth pin.
The charge up circuit 1302 may be configured to charge a battery 1303 with a power supply through the power connector 1301. In some embodiments, the charge up circuit 1302 may correspond to or be part of the charging unit 1204 as in
The battery 1303 and capacitor 1304 may be configured to store and supply power. In some embodiments, the battery 1303 and the capacitor 1304 may correspond to or be part of the power storage unit 1202 in
Referring to
The capacitor 1304 may connect to the battery 1303 and the high-voltage generator 1203. Referring to
The structures and functions described above in relation to the power supply system are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims. For example, there may be a converter circuit between the capacitor 1304 and the high-voltage generator 1203.
The converter 1401 may be configured to convert the electrical characteristics (e.g., voltage, current, frequency, power-phase, etc.) of the capacitor 1304. In some embodiments, the converter 1401 may correspond to or be part of the converter unit 1207 in
The structures and functions described above in relation to the power supply system are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims.
The battery level indicator 1501 may be configured to monitor the power level of the battery 1303. In some embodiments, the battery level indicator 1501 may correspond to or be part of the monitor unit 1206 in
The current limiting charge up circuit 1502 may be configured to charge the capacitor 1304 with a current limit. The use of the current limiting charge up circuit 1502 may avoid undesired large-current discharge of the battery 1303. In some embodiments, the current limiting charge up circuit 1502 may correspond to or be part of the charging unit 1204 in
The capacitor level indicator 1503 may be configured to monitor the power level of the capacitor 1304. In some embodiments, the capacitor level indicator 1503 may correspond to or be part of the monitor unit 1206 in
The structures and functions described above in relation to the power supply system are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims. For example, the battery level indicator 1501 and the capacitor level indicator 1503 may share a same display sub-unit.
The selection sub-unit 1601 is configured to form at least two different circuits for the power supply based on selection. Particularly, as shown in
When the first circuit is selected, the voltage limiting charge up circuit 1602 may charge the capacitor 1304 with a voltage limit. With using the voltage limiting charge up circuit 1602, the capacitor 1304 may receive power supply from a power network. In some embodiments, the voltage limiting charge up circuit 1602 may correspond to or be part of the charging unit 1204 in
The structures and functions described above in relation to the power supply system are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims.
The first selection sub-unit 1701 may include an input node 1701a, a first output node 1701b, a second output node 1701c, and a third output node 1701d. The first selection sub-unit 1701 may be configured to select an output node among the three output nodes (1701b, 1701c, 1701d) form a power supply circuit. The position of the first selection sub-unit 1701 in the circuit may be between the battery 1303 and the power connector 1301. For example, as shown in
The second selection sub-unit 1702 may include an output node 1702a, a first input node 1702b, and a second input node 1702c. The second selection sub-unit 1702 may be configured to select an input node between the first input node 1702b and the second input node 1702c to form a power supply circuit. Position of the second selection sub-unit 1702 in the circuit may be between the capacitor 1304 and the high-voltage generator 1203. For example, as shown in
In some embodiments, the first selection sub-unit 1701 and the second selection sub-unit 1702 may be a selection circuit, a multi-way switch, a multiplexer, or the like, or a combination thereof.
As shown in
A fourth circuit is formed when input node 1701a connects to output node 1701b, and input node 1702b connects to output node 1702a. In this power supply circuit, the power network may charge the capacitor 1304 through the voltage limiting charge up circuit 1602. The capacitor 1304 may charge the high-voltage generator 1203. This power supply circuit may be selected when there is a need to fast charge the capacitor 1304.
A fifth circuit is formed when input node 1701a connects to output node 1701d, and input node 1702c connects to the output node 1702a. In this power supply circuit, the power network may supply power to the high-voltage generator 1203, while at the same time the power network may charge the battery 1303, and the battery 1303 may charge the capacitor 1304. In some embodiments, the battery 1303 may simultaneously receive power from the power network and supply power to the capacitor 1304 and/or the operation module 110 of the digital radiography system (see e.g.,
If the power supply is normal through step 1810, or if the quantity of the power supply reaches the pre-set threshold value, a system component's position may be adjusted in step 1830. The component may be any component of the system, including but not limited to the X-ray detector 230, the ceiling suspension unit 240, the tube stand 250, the X-ray tube 260, the beam limiting device 270, or the like. The adjusting may be performed by the control module 103, or may be performed by the control unit (not shown) integrated in the control module 103. The adjusting may include adjusting the motion speed, adjusting the motion route, tilting an angle, or the like, or a combination thereof. More detailed descriptions regarding the controlling or adjusting of the motion of the system components may be found in
After the positions of system components are adjusted and determined, an X-ray acquisition module 106 of a specific configuration may be selected in step 1840. The selection of the X-ray acquisition module 106 of the specific configuration may be performed by the control module 103, or may be performed by a selection unit (not shown) integrated in the control module 103, or may be performed by a selection unit (not shown) integrated in the X-ray acquisition module 106. The specific configuration may be a vertical configuration, a horizontal configuration, a free-style configuration, or the like.
After the X-ray acquisition module 106 is selected, step 1860 for preparing exposure may be performed. The preparation may include setting one or more exposure parameters, including but not limited to exposure duration (ED), exposure frequency (EF), adherence factor (AF), body weight (BW), event frequency (EV), intake rate (IR), surface area of exposed skin (SA), age dependent adjustment factor (ADAF), or the like, or a combination thereof. The exposure parameters may be prepared based on a feature of the imaging target, or may be set by the system default. After the exposure parameters are set, an exposure for obtaining an X-ray image may be performed in step 1850.
The structures and functions described above in relation to the system process are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims. For example, in order to guarantee a normal operation of the system, a power detection step (such as step 1810) may be performed between any two steps. In another example, after selecting an X-ray acquisition module of a specific configuration in step 1840, a step for adjusting positions of system components (such as step 1803 may be performed).
The step for adjusting positions of system components (such as step 1803) according several embodiments is disclosed in further details in relation to
In step 1906, a comparison between the calculated distance and the preset threshold may be performed. If the distance reaches or exceeds the threshold, the motion of the component may be stopped in step 1907. If the distance is within the threshold range, the motion of the component may be adjusted in step 1908. For example, the motion speed of the component may be reduced. In another example, the component may be tilted for a specific angle to avoid collision. In a further example, the component may be turned around to another direction. After the motion of the component is adjusted, a motion control may be performed in step 1909. The motion control may be performed by the control module 103, or may be performed by a peripheral equipment (not shown) related to the system, or may be performed by any processing device disclosed anywhere in the present disclosure. The motion control may be continuous in real time, or may be performed at certain time intervals.
If no obstacle is detected in step 1903, the process may proceed to step 1910 to determine whether the current position and the target position are the same. If the answer is “Yes,” no motion is needed. If the answer is “No”, axial speeds may be calculated based on potential field method in step 1911 (such as artificial potential field (APF)). The calculation process of the potential field method will be described in further details below in relations to
As described above in the present disclosure, the motion path of system components may be calculated using the artificial potential field (APF) method. Particularly, APF is a mathematical approach for path planning as an object moves towards a target position, which assumes that the target position generates attractive forces towards the object, while nearby obstacles generates repulsive forces against the object. By calculating net forces of the repulsive and attractive forces, the object's motion path may be calculated. Regarding the structure of the present digital radiography system, any moving system component may be considered as the object in APF. It should be noted that when calculating the motion path of one system component, that system component may be regarded as the object to be moved to a target position, while another system component may be considered as an obstacle in APF. Similarly, objects external to the system, such as an imaging target or furniture in the imaging room, may be considered as obstacles in APF. For example, when calculating the motion path of the X-ray tube, the repulsive force generated by the X-ray detector may be calculated. Below provided are exemplary calculations based on two components of the present system, namely the X-ray tube and the X-ray detector.
Particularly,
VRHA=KRp(ΔPRt+1/TRiΣΔPRtΔt+TRd(ΔPRt−ΔPRt-1)/Δt)
VTilt=KTp(ΔPTt+1/TTiΣΔPTtΔt+TTd(ΔPTt−ΔPTt-1)/Δt) (Equation 1)
Where, KTp, TTi, TTd, KRp, TRi, TRd are PID constants that can be obtained by testing. ΔPTt is the difference of the target angle in Tilt axis and the angle at t moment, while ΔPRt is the difference of the target angle in TRHA axis and the angle at t moment, Δt is sampling period.
Axial speeds VFDZ, VTubeX and VTubeZ may determine the position of the collision area. To avoid collisions, axial speeds VFDZ, VTubeX and VTubeZ may be influenced by the collision area. In some embodiments of the present disclosure, APF may be utilized to calculate the axial speeds of the tube and the detector, and the axial speeds may be updated constantly to accomplish obstacle avoidance and path planning.
Particularly, when calculating the motion path of the tube, in step 2101, the repulsive force generated by the detector may be calculated.
If DFT≤Dmax, the repulsive force may be calculated by:FTX=KF
FTX/DFT2
FTZ=KF
FTZ/DFT2 (equation 2)
Where DFT denotes the distance between the tube and the detector. Referring to FTX and
FTZ are X component and Z component of DFT respectively. Dmax is a threshold distance where an obstacle starts to exert repulsive forces.
FTX and
FTZ are X component and Z component of the repulsive force generated by the detector, respectively. KF is a proportionality coefficient.
It should be noted that both repulsive forces and attractive forces in APF are artificially abstracted forces. For persons of ordinary skills in the art, it should be understood that the X component and the Z component of the repulsive force may be generated by the detector, while the X component and the Z component of the attractive force may be generated by the target position.
If DFT≥Dmax, both FTX and
FTZ may be set to 0. It may be inferred from equation 2 that the repulsive force generated by the detector increases as DFT decreases, when DFT approaches 0, the repulsive force generated by the detector may tend to be infinite, which may avoid the collision of the tube and the detector.
In step 2102, the attractive force generated by the target position may be calculated.
When Dg≥Dmin, the attractive force generated by the target position may be calculated by:
Where goalX and
goalZ are X component and Z component of the attractive force generated by the target position, respectively. Kg is a proportionality coefficient. Dmin is a threshold distance between the target position and the current position of the moving component. Dgoal is a distance between the target position and the current position of the moving component. Drun is a minimum threshold for the attractive force;
goalX and
goalZ are X component and Z component of Dgoal respectively.
When Dgoal<Dmin, it may be determined that the tube has arrived the target position, thus goalX and
goalZ may be set to 0, and the calculation of the attractive force generated by the target position may be terminated. It should be noted that Dmin may be determined by accuracy requirement. Drun may be set for an avoidance of slow movement of the object when the attractive force is not large enough.
In step 2103, the net force of the repulsive force and the attractive force may be calculated. Taking the movement of the tube as an example, the net force may be calculated by:
Where x is the net force in X axis and
z is the net force in Z axis.
In step 2104, axial speeds of the tube may be calculated based on the net force calculated in step 2103. Taking the movement of the tube as an example, the axial velocities may be calculate by:
Where x and
z are X axial speed and Z axial speed, respectively, Kv is transformation proportionality coefficient of forces and velocities,
maxX and
maxX are the maximum velocity in X axis and Z axis respectively.
It should be understood by persons of ordinary skill in the art that the axial speeds of the X-ray detector may be calculated based on the method described above. Particularly, to calculate the axial speeds of the detector, the X-ray tube may be regarded as an obstacle.
It should be noted that the flowchart described above is merely provided for the purposes of illustration, and not intended to limit the scope of the present disclosure. For persons of ordinary skills in the art, various variations and modifications may be conceptualized and reduced to practice. Those variations and modifications are intended to be within the scope of the present disclosure.
According to one aspect of the present disclosure, provided herein are methods for selecting an X-ray acquisition module of a suitable configuration. In practice, because X-ray images obtained from an imaging target in different positions may be desirable (for example, a doctor may need X-ray images of a patient when the patient stands up and lies down), a digital radiography system may include more than one X-ray acquisition modules. Particularly, the more than one X-ray acquisition modules may have a horizontal configuration (e.g., suitable for imaging a target in horizontal position) and a vertical configuration (e.g., suitable for imaging a target in vertical position). However, if the selection of a suitable X-ray acquisition module is performed manually by a medical practitioner (e.g., a doctor), error could happen when X-ray exposure occurs when an imaging target (e.g., a patient) is not in a suitable position relative to the selected X-ray acquisition module. Thus, provided herein is a method for automatically selecting an X-ray acquisition module of a suitable configuration, thereby increasing efficiency and safety of the digital radiography system.
In step 2230, the selected X-ray acquisition module 106 may be activated. As used herein, activating a selected X-ray acquisition module indicates that one or more units (not shown) of the selected X-ray acquisition module may be activated, such as but not limited to the ionization chamber (not shown), and/or the filter grid (not shown), etc. During the activation process, one or more acquisition parameters may be set or adjusted, such as duration, sensitivity, current, voltage, temperature, etc. Particularly, after the activation process, the process may proceed to step 2240 to determine whether an X-ray detector is ready, such as whether an X-ray detector is at a suitable location relative to the imaging target for X-ray image acquisition of the imaging target. In some embodiments, only one X-ray detector may be present in the system (see, e.g.,
If no X-ray detector is ready in step 2240, the process may be paused and an exposure may be prohibited in step 2250. If an X-ray detector is ready, the process may be continued. For example, one or more parameters for the exposure may be set in step 2260. The exposure parameters may include exposure current, exposure voltage, exposure duration, dosage or the like, or a combination thereof. Also, an exposure controller may be used (as described in
After the time duration of the detected signal is determined, a second threshold may be set in step 2350. The second threshold may be a single value of a duration time, or may be a value range. The second threshold may be set by the system default, or may be set by an end user (e.g., a doctor). In step 2360, a comparison between the determined time duration of the detected signal with the second threshold may be performed. If the time duration does not reach the second threshold, the process may return to step 2310 to start a new detection process. If the duration time reaches or exceeds the second threshold, the process may determine that an imaging target exists (step 2370). As used herein, existence of an imaging target indicates that an imaging target is in a suitable position relative to an X-ray acquisition module for imaging. In step 2380, an X-ray acquisition module may be selected based on the detected existence of the imaging target. The selection process will be described in further details in relation to
In some embodiments, the selection may be performed by the control module 103 based on the sensing result. In some embodiments, the selection may be performed automatically by the system while receiving the sensing result. In some embodiments, the selection may be performed by an end user (e.g., a doctor). Subsequently the selected X-ray acquisition module of the vertical configuration may be activated in step 2440. In some embodiments, in step 2505, whether an X-ray detector on the vertical stand is ready is determined. As described in relation to
If existence of an imaging target is not detected by the detection unit 2203 on the vertical stand 2201 in step 2420, the process may proceed to step 2450 to determine whether existence of an imaging target is detected by the second detection unit 2205 on the bed component 2203 (see,
If existence of an imaging target is also not detected nearby the bed component in step 2450, the process may proceed to step 2480 to select X-ray acquisition module of a free-style configuration. As described above, the free-style configuration acquisition module may assume any angle with respect to the imaging space or target. Additionally or alternatively, when a free-style configuration is selected, an end user (e.g., a doctor) may manual select a suitable X-ray acquisition module 106 and/or adjust position and angle of corresponding system components.
According to one aspect of the present disclosure, provided herein are methods for controlling X-ray exposure, which aims to improve safety and efficiency of the operation of the digital radiography system.
In step 2610, the process may set a status for permitting X-ray generation. The status for permitting X-ray generation may be set by software mechanism, or by a hardware mechanism, or both. In some embodiments, the status for permitting X-ray generation may be set by pressing the switch 1001 on the exposure control unit 905 (see, e.g.,
In step 2620, the process 2500 may send an exposure parameter preparation signal to a high-voltage generator 1203. The exposure parameter preparation signal may be a continuous signal, or may be a discrete signal. The exposure parameter preparation signal may be a pulse signal of a certain frequency. In some embodiments, the exposure parameter preparation signal may be sent by pressing down the first gear 1004 of the exposure controller 910 (see e.g.,
In step 2630, the process may send an exposure start signal to a high-voltage generator 1203. The exposure start signal may be a continuous signal, or may be a discrete signal. The exposure start signal may be a pulse signal of a certain frequency. The exposure start signal and the exposure preparation signal may be generated by a same component, unit, and/or module. In some embodiments, sending the exposure start signal is after sending the exposure parameter preparation signal in order to enhance security of the imaging target. In some embodiments, the exposure start signal may be generated by the pressing down the second gear 1005 of the exposure controller 910 (see e.g.,
The structures and functions described above are not exhaustive and are not limiting; numerous other changes, substitutions, variations, alterations, and modifications may be ascertained to one skilled in the art and it is intended that the present disclosure encompasses all such changes, substitutions, variations, alterations, and modifications as falling within the scope of the appended claims. For example, step 2620 may not be necessary in some embodiments. In another example, the exposure start signal may be sent simultaneously with the exposure parameter preparation signal.
| Number | Date | Country | Kind |
|---|---|---|---|
| 201420568992.3 | Sep 2014 | CN | national |
| 201420609950.X | Oct 2014 | CN | national |
| 201510490957.3 | Aug 2015 | CN | national |
This application is a continuation of U.S. application Ser. No. 15/322,424, filed on Dec. 27, 2016, which is a U.S. national stage under 35 U.S.C. § 371 of International Application No. PCT/CN2015/091076, filed on Sep. 29, 2015, which claims priority to Chinese Application No. 201420568992.3 field on Sep. 29, 2014, and Chinese Application No. 201420609950.X field on Oct. 21, 2014, and Chinese Application No. 201510490957.3 field on Aug. 11, 2015, each of which application is incorporated herein by reference in its entirety.
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| Examination Report in British Application No. 1902516.2 dated Jul. 5, 2019, 5 pages. |
| Combined Search and Examination Report under Sections 17 and 18(3) in British Application No. 1902519.6 dated May 1, 2019, 7 pages. |
| Number | Date | Country | |
|---|---|---|---|
| 20190357864 A1 | Nov 2019 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 15322424 | US | |
| Child | 16536437 | US |
