EA042559B1 - SYSTEM AND METHOD FOR VISUALIZATION OF RADIATION ENERGY - Google Patents

Description

Cross-reference to related applications

This application claims the benefit of U.S. Provisional Application No.

62/709213, filed January 11, 2018, which is incorporated herein by reference in its entirety.

Field of invention

The present disclosure relates generally to radiative energy imaging. More specifically, the present disclosure is directed to imaging systems that use electromagnetic radiation to detect hidden security threats.

Background of the invention

Criminals and terrorists often hide security threats such as weapons, explosives, smuggling, illicit drugs under their clothing and in body cavities when entering security controls. These security threats must be detected on people entering high security areas such as prisons, airports, government buildings, nuclear power plants, military bases, and the like. However, manual body searches of people are time consuming, often inefficient, and unpleasant for both the person being checked and the security officer performing the check.

The essence of the invention

According to one or more embodiments, various features and functionality may be provided to enable or otherwise facilitate the imaging process for detecting objects hidden on or in the human body, or in or under clothing.

According to one embodiment, the imaging system comprises an x-ray source configured to emit an x-ray beam and an x-ray detector configured to detect an x-ray beam emitted by the x-ray source. The x-ray detector and the x-ray source may be connected by a connector such that the x-ray detector and the x-ray source remain in geometric alignment so that the x-ray detector receives the x-ray beam during the imaging process. The imaging system may further comprise a translation mechanism configured to vertically translate the x-ray source and the x-ray detector during the imaging process such that the x-ray source is translationally within the first vertical path having the first height range and the x-ray detector is translationally moves within a second vertical path having a second height range, the second height range exceeding the first height range.

In some embodiments, the x-ray source comprises a collimating device. This collimating device may be configured to shape the X-ray beam into an X-ray fan strip by passing at least a portion of the X-rays in the X-ray beam emitted by the X-ray source through openings in the collimating device.

In some embodiments, the x-ray detector comprises a first side element and a second side element, with the first side element and the second side element attached to either side of the rear element at an obtuse angle.

In some embodiments, the x-ray detector comprises an active zone defined by at least one photodiode array configured to absorb radiation energy associated with an x-ray beam emitted by the x-ray source. In some embodiments, geometric alignment between the x-ray detector and the x-ray source is established by iteratively translating the x-ray detector vertically and obtaining some amount of radiation energy absorbed by the active zone of the x-ray detector, this amount of radiation energy corresponding to a threshold amount of radiation energy. In some embodiments, the imaging process comprises receiving image data corresponding to electrical signals derived from optical signals generated by said at least one x-ray detector photodiode array in response to the x-ray detector receiving an x-ray beam emitted by an x-ray source.

In some embodiments, the translation mechanism comprises a first cable and a second cable, the first cable is attached to the x-ray detector at the first end and the first balancer at the second end, the second cable is attached to the x-ray source at the first end and the second balancer at the second end. end. In some embodiments, the first cable is passed through the first sheave and the second cable is passed through the second sheave.

In some embodiments, the translation mechanism comprises a first linear actuator and a second linear actuator, the first linear actuator is configured to perform vertical translation of the x-ray source via the first cable, the second linear actuator is configured to perform vertical translation moving the x-ray detector through the second cable. In some embodiments, the x-ray source is translated at a first speed and the x-ray detector is translated at a second speed.

In some embodiments, the translation mechanism is further configured to pivot the x-ray source toward the x-ray detector at a downward angle, wherein the vertical location of the x-ray detector within the second vertical path is below the vertical location of the x-ray source within the first vertical path.

In some embodiments, the translation mechanism is further configured to pivot the x-ray source towards the x-ray detector at an upward angle, wherein the vertical location of the x-ray detector within the second vertical path is higher than the vertical location of the x-ray source within the first vertical path.

In some embodiments, the rendering system may further comprise a controller configured to receive user input to initiate the rendering process.

According to another embodiment, the method may comprise receiving user input by a controller configured to initiate a rendering process. The method may further comprise geometric alignment between an x-ray source configured to emit an x-ray beam and an x-ray detector configured to detect an x-ray beam emitted by the x-ray source. The x-ray detector and the x-ray source may be connected by a connector such that the x-ray detector and the x-ray source remain in optical alignment so that the x-ray detector receives the x-ray beam during the imaging process. Additionally, the method may comprise independently and vertically translating the x-ray source and the x-ray detector such that the x-ray source is translated within a first vertical path having a first height range and the x-ray detector is translated within a second vertical path having a second height range. height, wherein the second height range is greater than the first height range.

In some embodiments, establishing geometric alignment between the x-ray detector and the x-ray source comprises iterative vertical translation of the x-ray detector.

In some embodiments, establishing geometric alignment further comprises obtaining some amount of radiation energy absorbed by the active zone of the x-ray detector. The active zone of the x-ray detector may comprise at least one photodiode array configured to respond to radiation energy associated with the x-ray beam emitted by the x-ray source during the imaging process.

In some embodiments, establishing the geometric alignment further comprises determining if the amount of radiation energy absorbed by the active zone of the x-ray detector corresponds to a threshold amount of radiation energy.

In some embodiments, independent and vertical translation of the x-ray source comprises vertical translation of the x-ray source by a first linear actuator configured to vertically translate by a first cable, the first cable attached to the x-ray source at a first end and to to the first balancing device at the second end.

In some embodiments, independent and vertical translation of the x-ray detector comprises vertical translation of the x-ray detector by a second linear actuator configured to vertically translate by a second cable, the second cable being attached to the x-ray detector at a first end and to the second balancing device at the second end.

In some embodiments, independent and vertical translation of the x-ray source and x-ray detector comprises vertical translation of the x-ray beam at a first speed and vertical translation of the x-ray detector at a second speed.

In some embodiments, the independent and vertical translation of the x-ray source and x-ray detector comprises rotating the x-ray source towards the x-ray detector at a downward angle, wherein the vertical location of the x-ray detector is within a second vertical path below the vertical location of the x-ray source. x-rays within the first vertical path.

In some embodiments, the independent and vertical translation of the x-ray source and the x-ray detector comprises rotating the x-ray source towards the x-ray detector at an upward angle, wherein the vertical location of the x-ray detector within the second vertical path is above the vertical location of the x-ray source within first vertical path.

In some embodiments, the method may further comprise generating optical signals by the x-ray detector in response to the x-ray detector receiving an x-ray beam emitted by the x-ray source during the imaging process. In some embodiments, the method may further comprise obtaining image data corresponding to electrical signals derived from optical signals generated during the imaging process.

Other features and aspects of the disclosed technology will become apparent from the following detailed description, taken in conjunction with the accompanying drawings, which illustrate, by way of example, features according to embodiments of the disclosed technology. This overview is not intended to limit the scope of any of the inventions described herein, which are defined solely by the appended claims.

Brief description of the figures

Fig. 1 shows an imaging system according to one implementation of the present disclosure.

Fig. 2A shows the X-ray module of the imaging system of FIG. 1 according to one implementation of the present disclosure.

Fig. 2B shows the connecting element of the imaging system of FIG. 1 according to one implementation of the present disclosure.

Fig. 3A-3B show a side cross-sectional view and a top-down cross-sectional view, respectively, of the imaging system of FIG. 1 according to one implementation of the present disclosure.

Fig. 4A-4B show a side cross-sectional view and a perspective view, respectively, of the lifting mechanism of the imaging system of FIG. 1 according to one implementation of the present disclosure.

Fig. 5A-5B show a cross-sectional side view of the X-ray source and X-ray detector of the imaging system of FIG. 1 during the rendering process according to one implementation of the present disclosure.

Fig. 65A-6B show a cross-sectional side view of the X-ray source and X-ray detector of the imaging system of FIG. 1 during the rendering process according to one implementation of the present disclosure.

Fig. 7 shows a process for performing an imaging scan according to one implementation of the present disclosure.

Fig. 8 shows an exemplary computing system that may be used in implementing various features of embodiments of the disclosed technology.

These and other features and characteristics of the present technology, as well as the modes of operation and functions of related structural elements and the combination of parts and savings in manufacturing, will become more apparent upon consideration of the following description and the appended claims with reference to the accompanying drawings, which are all part of this description. of the invention, with like reference numerals designating like parts in different figures. However, it should be clearly understood that the drawings are for illustration only and are not intended to define the limitations of the present invention.

Detailed description

Described herein are imaging systems for detecting objects that may be hidden under clothing, swallowed, inserted, or otherwise hidden on or in the human body. Details of some illustrative embodiments of the systems and methods of the present disclosure are set forth in the description below. Other features, objects, and advantages of the present disclosure will become apparent to those skilled in the art upon consideration of the following description, drawings, examples, and claims. All such additional systems, methods, features, and advantages are intended to be included in this specification, are within the scope of the present disclosure, and are protected by the appended claims.

As noted above, there are situations in which objects hidden on or in a person's body, in or under clothing, etc. must be identified. In addition, there are situations in which the form factor of the imaging system is a matter of consideration, for example, when the imaging system must be moved to the room in which it is to be used, when the imaging system must be moved from one zone (or room) to another through one or more doorways, etc. Accordingly, various embodiments of the present disclosure are directed to improvements in the form factor of an imaging system that improve the transmission of radiation energy transmitted by an x-ray source moving along a stationary object to the x-ray detector.

In particular, some embodiments may comprise an imaging system having a form factor that is smaller than conventional imaging systems and that can be easily moved to and from different areas. For example, an imaging system made in accordance with various embodiments may include portions of appropriately sized components that provide a general imaging system form factor that allows the imaging system to be pushed/pulled through standard sized doorway openings having limited height and width. Such appropriately sized component parts may include a connector (described in more detail below) that maintains the x-ray source and x-ray detector spaced apart and allows the x-ray source and x-ray detector to be aligned. In addition, various embodiments implement a specific range of movement of the connector (and x-ray source and x-ray detector) that allows a subject to be scanned vertically within the form factor of the imaging system.

In some embodiments, during the imaging process, the lifting mechanism may vertically translate the x-ray source and the x-ray detector, connected by a connector, along the entire object being rendered. For example, the lifting mechanism may include linear actuators connected to cables passed through sheaves and balanced by balancing devices to effect vertical translation of the x-ray source and x-ray detector. In some embodiments, the lifting mechanism may raise and lower the x-ray source and x-ray detector at different speeds, allowing the x-ray source to be angled or tilted relative to the x-ray detector, and vice versa.

It should be understood that the systems and methods disclosed herein can be applied to existing imaging systems and methods. In other embodiments, the imaging system and method may be configured to (in all respects) function in the manner disclosed. An imaging system comprising an x-ray source and an x-ray detector according to various embodiments may be controlled by an imaging circuit implemented in or as part of an imaging system control unit. The imaging circuit may receive data from one or more sensors or extract data based on data from the sensors regarding the movement and alignment of the x-ray source and x-ray detector to decide whether or not the x-ray source and x-ray detector are exposed, and/ or whether they move in sync.

Fig. 1 shows an exemplary imaging system 100 implemented according to one embodiment. The imaging system 100 or components/features thereof may be implemented in combination with or instead of other systems/features/components described herein, such as the systems/features/components described with reference to other embodiments and figures. The imaging system 100 may further be used in any of the ways in which such systems/components/features are used as described herein. The imaging system 100 may also be used in various applications and/or permutations, which may or may not be noted in the exemplary embodiments described herein. For example, the rendering system 100 may include more or fewer features/components than the rendering system 100 shown in FIG. 1 in some embodiments. In addition, the rendering system 100 is not limited to the size, shape, number of components, etc. specifically shown in FIG. 1, although one or more aspects of the imaging system 100 may have particular size/shape limitations as those one or more aspects may affect the overall form factor of the imaging system 100.

A number of commercially available imaging systems use electromagnetic radiation to detect hidden objects and facilitate body searches. Conventional imaging systems can be configured to use low energy radiation during the imaging process. For example, low energy imaging systems may use radiative energies such as millimeter wave non-ionizing electromagnetic radiation and/or other low energy radiation such as backscattered x-rays. During the imaging process, low energy radiation can pass through the outermost layers containing the object, such as clothing, but is easily reflected off or scattered by any dense parts of the object. Accordingly, since low energy imaging systems emit radiation that cannot easily pass through the volume of an object, they can only detect latent threats hidden under the outermost layers. For example, low energy imaging systems can detect security threats hidden under a person's clothing, but cannot detect security threats hidden in body cavities.

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Other conventional imaging systems may be configured to use higher energy radiation. For example, imaging systems with higher energy radiation may use radiation energies, such as x-rays. While the radiation levels used by higher energy systems may be less than those used in, for example, medical x-ray scanners, the higher energy radiation is nevertheless transmitted through the object and captured behind the object by the detector. For example, a continuous beam of x-rays may be transmitted through the object under test during the imaging process. The detector can capture x-rays and generate optical signals that are converted into electrical signals by an array of photodiodes inside the detector. The electrical signals are then transmitted to a computing system which displays an image containing the transmitted electrical signals and/or is recorded by the image recording equipment. By detecting the radiation energy that is transmitted through the object, and not only by measuring the radiation that is reflected from the object, which can be the case in the case of low energy imaging systems, imaging systems using higher energy radiation (for example, transmitted x-rays) can detect threats security threats hidden in a person's body cavity, not just security threats hidden under a person's clothing.

Conventional imaging systems using higher energy radiation can be implemented in several ways. One such example of a conventional imaging system is an imaging system that includes an x-ray source configured to emit a vertical beam of x-rays towards a vertically oriented x-ray detector. During the imaging process, both the x-ray source and the x-ray detector are configured to remain stationary while the subject moves horizontally through the imaging system (eg, by placing it on a conveyor belt). However, moving the subject through the imaging system not only requires a large imaging system, but also leads to a number of operational problems (eg, subject movement safety problem).

Another example of a conventional imaging system is an imaging system that includes an x-ray source located at a mid-level relative to a stationary subject and an x-ray detector located behind the stationary subject. During the imaging process, the x-ray source is rotatable about a horizontal axis while the x-ray detector is movable vertically. Since the X-ray source does not move forward with the X-ray detector, but rotates, the X-ray beam emitted by the X-ray source enters the subject at an angle and thus travels an excessively long path, especially when scanning the lowest and highest areas. stationary entity. An excessively long path length traveled by an angled x-ray beam may interfere with imaging of certain important body cavities (eg, the abdomen) and may result in poor threat detection. Additionally, the long path leads to a number of motion synchronization problems between the x-ray source and the x-ray detector, which also affect the quality of the images generated during the imaging process.

Yet another example of a conventional imaging system is an imaging system that includes an x-ray source that is vertically translated along with an x-ray detector in synchronism around a stationary object. Translational movement of the x-ray source together with the x-ray detector causes horizontal entry (rather than entry at an angle) of the x-ray beam into the subject, resulting in improved threat detection, with reference to the above, and improved image quality due to reduced geometric distortion. However, conventional imaging systems that vertically translate an x-ray source along with an x-ray detector are known to be heavy, bulky, and difficult to transport without extensive disassembly or mechanical lifting equipment.

An exemplary imaging system having a form factor that is smaller than conventional imaging systems may be implemented as shown in FIG. 1. As shown in FIG. 1, the imaging system 100 includes a frame housed in a housing mounted on a base module 112 that defines the width and length of the imaging system 100. The housing may contain one or more imaging components configured to render transmitted x-rays, one or more movement components configured to move one or more imaging components, and/or other components. In some embodiments, the frame may include metal supports configured to provide structural support and/or framing for the imaging components and movement components of the imaging system 100, as described in more detail below.

- 5 042559

In some embodiments, the base module 112 may include opposing first and second sides 103, 105. In some embodiments, the housing may include an X-ray source compartment 120 and an X-ray detector compartment 118 mounted on the first and second sides 103, 105 of module 112 grounds, respectively. For example, the X-ray source compartment 120 may accommodate an X-ray source, and the X-ray detector compartment 118 may accommodate an X-ray detector.

In some embodiments, the implementation of the housing may contain a connecting compartment 122, installed between the first and second sides 103, 105 module 112 of the base. For example, the connecting compartment 122 may be located between the X-ray source compartment 120 and the X-ray detector compartment 118. In some embodiments, the connecting compartment 122 may accommodate a connecting element configured to connect an x-ray source placed in the x-ray source compartment 120 and an x-ray detector placed in the x-ray detector compartment 118, as described in more detail below. In some embodiments, the connector may provide support, stabilization, and alignment of the x-ray source and x-ray detector during the imaging process.

In some embodiments, each of the X-ray source compartment 120, the X-ray detector compartment 118, and the body connection compartment 122 and the base module 112 of the imaging system 100 may comprise an outer and an inner surface. The outer and inner surfaces may be formed using the same or different materials. For example, materials used to form the outer surfaces of the X-ray source compartment 120, X-ray detector compartment 118, connection compartment 122, and base module 112 may include leaded steel, aluminum honeycomb, plastic, and/or other such material configured to absorb x-rays. Through the use of the materials described, the imaging system 100 can provide physical protection against scattered x-rays emitted from an object during an imaging process (commonly known as scattered radiation) to protect other people in close proximity to the provided scattered radiation. In some embodiments, the materials used to form the interior surfaces of the x-ray source compartment 120, x-ray detector compartment 118, connection compartment 122, and base module 112 may include structurally strong materials such as carbon fiber composite that are transparent to x-rays.

In some embodiments, the body of the imaging system 100 may be defined by at least three sides. The two sides may be formed by the X-ray source section 120 and the X-ray detector section 118 mounted on the first and second sides 103, 105 of the base module 112, respectively, and the third side may be defined by the connecting section 122 installed between the first and second sides 103, 105 base module. The fourth side may include an opening opposite the connection compartment 122. The boundaries of the opening may be defined by an x-ray source compartment 120 and an x-ray detector compartment 118 that extend towards the opening.

In some embodiments, the imaging system 100 may include an internal space 119 formed over the base module 112 and surrounded by three housing ends, with reference to the above. The interior space 119 may be completely covered by the three sides mentioned and only partially covered by the fourth side to allow entry/exit from the imaging system 100. For example, interior space 119 may be completely enclosed on three sides by X-ray source compartment 120, X-ray detector compartment 118, and connection compartment 122. A fourth side partially covering interior space 119 may include a side compartment (not shown) located opposite the connection compartment. 122. In some embodiments, the side compartment may include a door (not shown) configured to enclose interior space 119. For example, the door may be a sliding door or standard hinged door that opens and closes to provide access to interior space 119 imaging systems 100. In some embodiments, the door may be operatively attached to the X-ray source compartment 120 and/or the X-ray detector compartment 118. In some embodiments, the door may be slidable between the X-ray source compartment 120 and the X-ray detector compartment 118.

In some embodiments, interior space 119 may be completely and/or partially covered by a top cover (not shown) configured to cover interior space 119 from above. In some embodiments, the implementation of the top cover may be configured to be fully and/or partially removable. For example, the top cover may be removed to allow rendering of an object that may be larger than the height 132 of the rendering system 100, as will be described in more detail below.

- 6 042559

In some embodiments, interior space 119 may include a hollow cavity configured to receive a subject during an imaging process, as will be described in more detail below. Used here in some embodiments, the implementation of the term subject may refer to the object that is scanned by the imaging system 100, such as an inanimate object. As described in more detail below, the object may also contain a person, such as a prisoner, an alleged criminal, a terrorist, or a person entering a high security area (eg, an airport).

In some embodiments, the base module 112 and the housing of the imaging system 100 mounted on top of the base module 112 may be reduced in size compared to conventional imaging systems. For example, the width, height, and length of one or more components may be sized to allow imaging system 100 to pass through a standard sized doorway (eg, to accommodate a large person during an imaging process, or to facilitate placement of an object on base module 112).

The dimensions of the imaging system 100 in this example include a width 130, a length 134, and a height 132. In some embodiments, the width 130 of the imaging system 100 may be approximately 84 cm, the length 134 may be approximately 182 cm, and the height 132 may be approximately 211 cm. In some embodiments, base module 112 may include height 173, which may be part of height 132 of imaging system 100. For example, base module 112 may be approximately 10 cm in height.

In some embodiments, the imaging system 100 may be transportable. For example, as shown in the embodiment of FIG. 1, the imaging system 100 may include at least four wheels or rollers 114 mounted on the outer surface of the base module 112. As the imaging system 100 moves, each of the rollers 114 can be rolled to facilitate movement of the imaging system 100. It should be understood that various embodiments involve the use of other mechanisms to move the imaging system 100, such as sliders, pads, and the like. For example, the imaging system 100 may be rolled through a doorway by the engagement of rollers 114.

In some embodiments, with reference to the above specific dimensions of the imaging system 100, such as width and height 130, 132, may allow imaging system 100 to be transported through standard doorways (or custom doorways having smaller dimensions). By making the width and height 130, 132 of the imaging system 100 smaller than the length and width of a standard size doorway, respectively, the imaging system 100 can fit through a standard size doorway of most commercial buildings. For example, a standard size doorway in a commercial building may be approximately 86 cm wide and approximately 213 cm high. Accordingly, since the width 130 and height 132 of the imaging system 100 are approximately less than 84 cm and less than 211 cm, respectively, the particular dimensions of the imaging system 100 allow the imaging system 100 to be transported through a standard size commercial doorway.

Additionally, while the imaging system 100 can be transportable through the standard size doorways of most commercial buildings, the particular dimensions of the imaging system 100 can also allow a larger than average person to be accommodated during the imaging process. For example, a large person may have a width and height of approximately 80 cm and 200 cm, respectively. Accordingly, the dimensions of the imaging system 100 of the embodiment shown in FIG. 1 are larger than a large person to be placed in the imaging process. For example, the dimensions of the imaging system 100 may exceed the dimensions of a large person by 10%. Notably, while the imaging system 100 is large enough to render a large person, it still has a smaller form factor than conventional imaging systems. For example, conventional imaging systems often have dimensions that greatly exceed the width and height of the person being scanned. Accordingly, due to the significant oversize of the person being scanned, it may be necessary for the conventional imaging system to be transported in modules and reassembled upon arrival.

With reference to the above, various embodiments of the imaging system 100 may have a form factor that allows the imaging system 100 to be transported within certain institutions (eg, government buildings) having doorways that are reduced in size compared to other standard sized commercial doorways. For example, prison doorways may be approximately 200 cm high. In some embodiments, the imaging system 100 may be sized to be transportable through doorways that are approximately 200 cm high. For example, the height 132 of the imaging system 100 may be less than 200 cm. As described in more detail below, the imaging system may include a lift mechanism that may temporarily increase the height 132 of the imaging system 100 during the imaging process to accommodate a person whose height

- 7 042559 exceeds 200 cm.

In some embodiments, one or more external surfaces of the imaging system 100 may include one or more markings and/or decorative features 150. radiation) associated with the imaging system 100. In some embodiments, one or more external surfaces of the imaging system 100 may contain an identifier (eg, name) of the room in which the imaging system 100 is used. In some embodiments, one or more exterior surfaces of the casing of the imaging system 100 may include one or more decorative features, such as a decorative feature 150 used to enhance the appearance of the imaging system 100. In some embodiments, one or more exterior surfaces of the housing of imaging system 100 may include any or all of the aforementioned markings, decorative features, or other relevant features, as will be appreciated by those skilled in the art upon reading this application.

Visualization process

In some embodiments, the object being imaged by the imaging system 100 may be placed between the X-ray source compartment 120 and the X-ray detector compartment 118. For example, as shown in the embodiment of FIG. 1, the object to be checked is a person 110 who enters the interior 119 of the imaging system 100 by stepping on the floor 116 attached to the inside surface of the base module 112. Alternatively, a person using a walker, crutches, or wheelchair may also be placed on the floor 116 through the use of a ladder or other such components configured to facilitate such placement.

With reference to the above, in some embodiments, a person 110 can access the interior 119 of the imaging system 100 by entering through an opening in the housing formed by the X-ray detector compartment 118 and the X-ray source compartment 120. With reference to the above, in some embodiments, a person 110 can access the interior space 119 of the imaging system 100 by opening and/or sliding a door configured to completely and/or partially cover the interior space 119. After entering the interior space 119, the person may be positioned so that it faces the X-ray detector compartment 118. In some embodiments, the implementation of the person may be positioned so that he was facing the office 120 of the x-ray source. After the person 110 is correctly positioned, the door can be closed and the imaging process can be initiated. In some embodiments, during operation of the imaging system 100, the person 110 may be instructed to stand still.

In some embodiments, with reference to the aforementioned small form factor of the imaging system 100 may prevent and/or mitigate the difficulties associated with accessing the interior space 119. Namely, specific dimensions of the base module 112, such as the height 173, may minimize the distance from the floor. , on which the imaging system 100 can be placed. For example, the person 110 may be required to walk onto or off the floor 116 of the base module 112 during the rendering process. Due to the reduced height 173 of the base module 112 compared to conventional imaging systems, a person may need to cover a relatively short distance.

In some embodiments, the duration of the rendering process may vary from about 0.5 to 5 seconds. Conventional imaging systems typically complete the imaging process in about 8 to 10 seconds. After the rendering process is complete, and as described in more detail below, the image can be generated and submitted for inspection for hidden threats. In some embodiments, the door may be opened and the person may exit the imaging system 100 by stepping off the floor 116 of the base module 112, which completes the imaging process.

In some embodiments, the imaging system 100 may be controlled by an operator by entering one or more user commands through a control interface. For example, the operator may initiate the rendering process by entering an appropriate command through the control interface of the control panel 124 or other appropriate control interface.

In some embodiments, the imaging system 100 may be configured to be controlled from a remote location. For example, an operator may initiate an imaging process by entering an appropriate command through a control interface within a computing platform (not shown) communicatively coupled to an imaging system 100 located at a physical location other than the physical location of the computing platform. The operator can both initiate the visualization process and see

- 8 042559 one or more images generated by the imaging system 100 from a computing platform.

In some embodiments, the imaging system 100 may be controlled automatically. For example, upon detecting that an object has been placed on the floor 116 of the base module 112, the rendering process may be initiated. The images generated during the automatic rendering process can be transferred to a computing platform.

X-ray module

Fig. 2A shows an exemplary x-ray module 200 of the imaging system 100. The X-ray module 200 includes an X-ray source 202, an X-ray detector 204, and a connector 206. With reference to the above and as shown in FIG. 1, the x-ray source 202 may be placed inside the x-ray source compartment 120. The x-ray detector 204 may be placed inside the x-ray detector compartment 118, and the connector 206 can be placed inside the connector compartment 122.

X-ray source

As noted above, the x-ray source 202 may be configured to emit a continuous high-energy x-ray beam captured by the x-ray detector 204 to enable detection of hidden objects (eg, in body cavities). For example, as shown in FIG. 2A, x-ray source 202 may include an x-ray generator (e.g., a Monoblock® generator) configured to generate an x-ray beam with a maximum energy of at least 120-180 keV and a maximum tube current of at least 0.1-10 milliamps. In some embodiments, the x-ray source 202 may have a height of 248. For example, and as shown in FIG. 2A, the height 248 of the x-ray source 202 may be approximately 40 cm.

During the rendering process, the x-ray source 202 is translated vertically along the entire rendered object. Since the emitted X-rays must be captured by the X-ray detector 204, the X-ray source 202 and the X-ray detector 204 must be aligned during translation. Maintaining the alignment may require stabilization of the x-ray source 202 and x-ray detector 204 to maintain substantially the same relative position of the two components during the imaging process.

In some embodiments, the x-ray source 202 may be mounted on the connector 206 to help maintain substantially the same position of the x-ray source 202 relative to the x-ray detector 204 and align the x-ray source 202 with the x-ray detector 204 during the imaging process. For example, as shown in FIG. 2B, the x-ray source 202 may be mounted on the first holder 251 of the connector 206. The first holder 251 of the connector 206 may be located at a distance from the second holder 261 of the connector 206.

In some embodiments, a filter wheel containing one or more filters may be placed in close proximity (within a few centimeters) to the exit of the x-ray source 202 to intercept and filter the x-ray beam generated by the x-ray source 202. For example, said one or more filters may be formed from aluminum and copper with varying thicknesses (eg Al 1-10 mm, Cu 0.1-1 mm).

collimator

In some embodiments, imaging system 100 may include at least one collimator (eg, collimator 213 shown in FIG. 3A) to control the spatial extent of the x-ray photon stream emitted from the x-ray source focal spot. By limiting the spatial extent of the x-ray beam (for example, by limiting the x-ray beam to a specific area), the image quality can be improved and the radiation dose can be reduced. A single slit collimator, which shapes the X-ray beam into a thin stripe or fan beam, is one such example of a collimator. Another example is a multi-slit collimator having a series of holes or through holes formed in close proximity to each other, each of which directs and transmits x-rays. Typically, the collimator is made using a high density metal and/or a refractory metal designed to absorb rather than transmit radiation, such as tungsten or lead. For example, the collimator may be configured to have a slit of approximately 0.25 mm through which X-rays pass.

In some embodiments, the implementation of the collimator may be configured to remain in a fixed position relative to the source 202 x-rays. In some embodiments, the collimator may be movable relative to the x-ray source 202. In other embodiments, multiple collimators may be used. For example, the first collimator may be a fixed slit collimator while the second collimator may be a rotary collimator.

In some embodiments, a collimator may be placed adjacent to the x-ray source 202 to intercept and collimate the x-ray beam into a fan-shaped x-ray beam 208 corresponding to the dimensions of the x-ray detector 204. By collimating the X-ray beam, the X-ray beam can be limited to an area having a specific width and height. For example, the collimated fan beam of x-rays 208 may be limited to a zone having a width of approximately 30 cm and a height of approximately 2 mm on the side of the x-ray detector 204, while it is approximately 0.25 mm high when emitted from the x-ray source 202 rays. Accordingly, although the X-ray beam expands in both the vertical and horizontal directions, when it propagates by using a collimator, with reference to the above, the X-ray radiation is limited to the active area 210 of the X-ray detector 204, described in detail below. Accordingly, the collimator makes it possible to limit the x-rays to be intercepted by the x-ray detector 204 having a narrow active area, which in turn reduces the size of the x-ray detector 204 and contributes to the form factor of the imaging system 100 described below.

X-ray detector

With reference to the above, the X-ray detector 204 may be configured to capture the X-ray beam emitted from the X-ray source 202 and generate optical signals that are converted into electrical signals by the photodiode array included in the X-ray detector 204. During the imaging process, the x-ray detector 204 is translated vertically while providing alignment with the x-ray source 202.

In some embodiments, specific dimensions of the x-ray detector 204 may contribute not only to maintaining alignment between the x-ray detector 204 and the x-ray source 202 and/or stabilizing the x-ray detector 204 during the imaging process, but also to the overall form factor of the imaging system 100.

The reduced size and weight of the x-ray detector 204 compared to x-ray detectors used in conventional imaging systems is one example that can result in greater stability during vertical translation, with reference to the above. This is because the connector 206 on which the x-ray detector 204 is mounted may be susceptible to vibrational and/or other mechanical forces during vertical translational movement. These mechanical forces acting on the connector 206 can lead to inconsistency between the X-ray detector 204 and the X-ray source 202 and can cause poor image quality. Conventional imaging systems that do not consider the form factor focus on stabilizing the x-ray detector (ie, reducing the mechanical forces on the connector that supports the x-ray detector) by increasing the size of the connector. However, this can lead to an increase in the weight and size of the imaging system itself. For example, conventional imaging systems typically weigh approximately 900 kg and measure approximately 2.4 meters wide, 2.4 meters long, and 2.4 meters high. A particular problem is that such large imaging systems cannot be transported without extensive disassembly and/or the use of mechanical lifting equipment.

In some embodiments, the x-ray detector 204 may have a height 216 and a width 218. For example, as shown in FIG. 2A, the height and width 216, 218 of the x-ray detector 204 may be approximately 10 cm and 80 cm, respectively. In some embodiments, the width 218 of the x-ray detector 204 may approximately correspond to the width 130 of the imaging system 100 shown in FIG. 1.

In some embodiments, the x-ray detector 204 may comprise at least one detector array, an example of which would be a photodiode array. In some embodiments, the detector array may comprise one or more photodiode arrays. In some embodiments, the photodiode array may be a linear array. For example, as shown in FIG. 2A, X-ray detector 204 may include a detector array including at least one photodiode array. In some embodiments, said at least one photodiode array of x-ray detector 204 may comprise a plurality of individual photodiodes. For example, said at least one photodiode array of x-ray detector 204 may contain 640 photodiodes.

In some embodiments, each of the photodiodes in the photodiode array may have a scintillating material (eg, cadmium tungstate or cesium iodide) attached and may be of specific dimensions. For example, individual photodiodes in the photodiode array of x-ray detector 204 may be approximately 1.6 mm high and approximately 1.6 mm wide. IN

- 10 042559 In some embodiments, the x-ray detector 204 may comprise approximately 40 photodiode arrays, each containing 16 photodiodes, for a total of 640 photodiodes. In some embodiments, each of the photodiode arrays of the x-ray detector 204 may be approximately 71 cm in length.

In some embodiments, collimated x-ray fan beam 208 may pass through an aperture that limits the size and movement of x-ray beams 208 toward x-ray detector 204. In some embodiments, the implementation of the collimated fan beam of x-rays 208 may be limited to a specific area within the detector 204 x-rays. For example, the collimated fan beam of x-rays 208 may be limited to the active area 210 of the x-ray detector 204. The active zone 210 of the x-ray detector 204 may be defined by an array of photodiodes. For example, x-ray source 202 may generate a single collimated x-ray beam that may require only a narrow core 210. Narrow core 210 may in turn result in an x-ray detector 204 having reduced size and/or weight. With reference to the above, reducing the size and/or weight of the x-ray detector 204 results in the same form factor of the imaging system 100.

Photodiode array

In some embodiments, said at least one photodiode array of x-ray detector 204 may be irradiated by fan-shaped x-ray beam 208 generated by x-ray source 202. In some embodiments, the photodiodes and accompanying scintillators in the photodiode array can absorb radiation energy generated by the x-ray source 202. After absorbing some level of radiation energy, photodiodes can generate an electrical signal. In some embodiments, the implementation of the electrical signal generated by the photodiodes may lead to the transmission of output data through analog and/or digital electronic circuits. The output may comprise image data supplied to the computing platform for displaying the image.

In some embodiments, a line scan geometry may be used to read all of the photodiodes in each of the one or more photodiode arrays of the x-ray detector 204. In some embodiments, the image data may be processed by a software tool or imaging processing program configured to generate a digital image of the object being scanned.

In some embodiments, the read rate (ie, the rate at which individual photodiodes in the photodiode array are processed) of the photodiode arrays may be determined by the microprocessor controller. For example, all 640 photodiodes in 40 photodiode arrays in x-ray detector 204 can be read in approximately 3 ms. The read rate may determine the time of the imaging process. For example, with reference to the above, the photodiode arrays in the x-ray detector 204 can be read in approximately 3 ms. Since the imaging system 100 is configured to read 1333 scan lines during the imaging process, it follows that the total scan time will be approximately 4 seconds. The individual scan lines may correspond to the resolution of the resulting image generated during the rendering process.

Accordingly, the x-ray detector 204 must complete reading of all 640 photodiodes before reading the next scan line. Namely, reading at a rate of 3 milliseconds for all photodiodes in the x-ray detector 204 can be completed before the next vertical shift. This can be achieved by ensuring that the height of the scan line is approximately the same as the height of the photodiode array. For example, assuming an average human height is approximately 200 cm, each scan line is approximately 1.6 mm in height, which corresponds to the height of the photodiode array (i.e., approximately 1.6 mm).

In some embodiments, the x-ray detector 204 may comprise an x-ray detector module including a rear element 228, a first element 226, and a second element 224, with the first and second elements 226, 224 connected to each side of the rear element 228. Alternatively, the first and the second members 224, 226 and the rear member 228 may be/formed as a single unit. The x-ray detector module may have a height of 216 and a width of 218. For example, and as shown in FIG. 2A, the height and width 216, 218 of the x-ray detector module may be approximately 10 cm and 80 cm, respectively.

In some embodiments, the implementation of the first and second elements 226, 224 of the x-ray detector module can be attached on either side of the rear element 228 at a right angle. Accordingly, the x-ray detector 204, comprising the x-ray detector module defined by the rear member 228 and the first and second members 226, 224, may be U-shaped. In some embodiments, the implementation of the first and second elements 226, 224 may be attached on either side of the rear element 228 at an obtuse angle. By using the module

- 11 042559 x-ray detector, containing the first and second elements 226, 224 attached on both sides of the rear element 228, the x-ray detector can be configured to accommodate at least one photodiode array having a length the same as and/or greater than the width 218 of the x-ray detector module.

For example, and as shown in FIG. 2A, the photodiode array may be as long as the average width of a person (eg, approximately 76 cm) and yet still fit within a width dimension 218 that may be less than the average width of a person. Namely, said at least one photodiode array placed in the first and second elements 226, 224 of the X-ray detector module can detect X-rays emitted by the X-ray source 202 by wrapping it around at least one area of the subject's body. By arranging said at least one photodiode array in the U-shaped X-ray detector 204, with reference to the above, the X-ray detector module can only be approximately 10% smaller than the imaging system 100. Namely, due to the U-shape of the x-ray detector 204, all or the necessary portion of the x-ray fan beam 208 required to fully image the subject is captured, despite the vertical and horizontal expansion of the x-ray beam. This, together with the use of the aforementioned collimator (which confines the x-rays to the active zone 210 of the x-ray detector 204), results in improved x-ray detection within the small form factor of the imaging system 100.

For example, during the imaging process, person 110 may be facing x-ray source 202 while person 110's back may be facing x-ray detector 204, or vice versa (for example, person 110 may be facing x-ray detector 204). Accordingly, half of the frontal plane of the subject may be covered or surrounded by the X-ray detector 204 (e.g., the first and second elements 226, 224 and the rear element 228) by means of the U-shaped X-ray detector 204 with reference to the above. Namely, said at least one photodiode array placed in the U-shaped X-ray detector 204 can capture the emitted radiation by covering or surrounding almost the entire subject, despite the fact that the rear element 228 is shorter than the width of the imaged subject. Additionally, by placing the photodiode array 210 within the first and second elements 226, 224 instead of placing the photodiode array 210 only within the rear element 228, a small form factor of the imaging system 100 shown in FIG. 1.

In some embodiments, the x-ray detector 204 may not be linear, but may be angled to match the shape of the base module 112 of the imaging system 100. The use of an x-ray detector 204 shaped to match the shape of the base module 112 instead of the linear x-ray detector 204 results in a reduction in the size of the base module, which contributes to the small form factor of the imaging system 100. In particular, and with reference again to FIG. 2A, it can be understood that the elements 226, 224 of the x-ray detector module are designed so that they are substantially perpendicular to the rear element 228. However, in other embodiments, the side elements 226, 224 may be angled to the rear element 228. For example, and with reference now to FIG. 3B, the side members 224, 226 may be angled in accordance with half-angle cutouts in which the side members 224, 226 may be at rest before and after the rendering process.

Security control system

In some embodiments, imaging system 100 may include one or more radiation shielding components. The radiation shielding components may be formed from a radiation-absorbing material such as lead, tungsten, and/or other such material configured to absorb radiation energy emitted by the x-ray source during the imaging process. For example, and as shown in FIG. 2A, the x-ray detector 204 may include one or more radiation protection components on each of the first and second elements of the x-ray detector 204. During the imaging process, the X-ray source 202 is directed towards the X-ray detector 204 and one or more radiation protection components at each end of the X-ray detector 204. Because the collimator limits the horizontal width of the X-ray fan 208 emitted by the X-ray source 202 to be slightly less than the width of the X-ray detector 204, the appearance of non-irradiated photodiodes at each end of the X-ray detector 204 may indicate that the X-ray fan beams 208 is correctly aligned with the x-ray detector 204 in the horizontal direction. Namely, it provides a method for ensuring that the sides (or necessary portions) of the x-ray fan beam 208 are intercepted and thus blocked by one or more radiation protection components at each end of the x-ray detector 204

- 12 042559

connecting element

As noted above, the alignment between the x-ray source and the x-ray detector is maintained during the imaging process to obtain an accurate image. Conventional imaging systems often maintain alignment between the x-ray source and the x-ray detector by means of one or more components supporting the x-ray source and the x-ray detector. However, these components are often heavy and large, resulting in bulky imaging systems that are difficult to transport.

With reference to the above, in some embodiments, the implementation of the connecting element 206 may rigidly connect the source 202 of the x-rays and the detector 204 of the x-rays. In some embodiments, the connector 226 may be formed from a substantially rigid material, such as steel or any other such material, configured to retain a rigid shape.

As shown in FIG. 2B, connector 226 may be C-shaped. For example, and with reference to the above, the x-ray source 202 may be mounted on the first holder 251 of the connector 206, while the x-ray detector 204 may be mounted on the second holder 261 opposite the first holder 251 of the connector 226. Conventionally, the connector , similar to connector 206 shown in FIG. 2B may be appropriately sized to maintain substantially the same position of the X-ray detector and X-ray source during the imaging process and to provide alignment between the X-ray source and X-ray detector. With reference to the above, since the collimated fan beam of X-rays 208 emitted by the X-ray source 202 is focused into a particular area of the X-ray detector 204 (e.g., the core 210), it is only required that the X-ray detector 204 be as narrow as the width and the length of the x-ray fan beam 208 (ie, much smaller than the x-ray detector used in conventional imaging systems). By reducing the size of the x-ray detector 204, as contemplated by various embodiments, the connector can be configured to be lighter and have a form factor that is smaller than the conventional connector, which contributes to the form factor of the imaging system 100. For example, connector 206 may comprise a width 238 that may be between about 1.9 and 10 cm. In some embodiments, width 238 of connector 206 may comprise the same width as second element 224 of the x-ray detector module shown in FIG. . 2A and described above. Namely, the width 238 of the connector 206 may be such that it cannot increase the width 130 of the imaging system 100 shown in FIG. 1.

In some embodiments, during the imaging process, the connector 226 is configured to maintain alignment between the x-ray source 202 and the x-ray detector 204. For example, when the x-ray source 202 and the x-ray detector 204 are raised and lowered, the alignment between the x-ray source 202 and the x-ray detector is maintained by a rigid connection provided by the connector 226. In some embodiments, the use of the connector 226 to maintain the alignment between the x-ray source 202 x-rays and the x-ray detector 204 during the imaging process, instead of using feedback sensors, for example, results in an exposure with a lower margin of error (eg margin of error down to 0.13 mm) compared to conventional imaging systems. In some embodiments, maintaining a tight alignment between x-ray source 202 and x-ray detector 204 reduces the risk of discontinuities (eg, distortion in the resulting image) during the imaging process.

Attachment points

With reference to the above, during the imaging process, the X-ray unit 200 of the imaging system 100 is translated vertically. Often, conventional imaging systems raise or lower the x-ray module within the frame of the imaging system by using a lifting mechanism that is attached to the x-ray module via a single attachment point (and thus uses a single actuator). However, a single attachment point often causes unintentional torsion of the X-ray module, causing mismatch between the X-ray source and the X-ray detector, resulting in unwanted image distortion. With reference to the above in order to compensate for these unintended movements, conventional imaging systems focus on increasing the size of the connector, resulting in unwieldy and large imaging systems to provide the required amount of stability in the x-ray module. For example, conventional imaging systems typically use connectors that are larger, heavier, and harder to

- 13 042559 move and actuate.

In contrast, in some embodiments, the x-ray module 200 is raised and lowered by a lifting mechanism that is attached to the x-ray module via at least two separate attachment points. For example, and as shown in FIG. 2A, the first attachment point 214 may be mounted on the x-ray detector 204, and the second attachment point 212 may be mounted on the x-ray source 202. The first and second attachment points 212, 214 may be connected to the first and second linear actuators, respectively, as described below.

The first and second attachment points 214, 212 may be located at opposite ends of the x-ray module 200, i.e., at or near the center of mass of each of the x-ray detector 204 and x-ray source 202, respectively. This configuration can reduce any potential mechanical forces (eg, pressure forces) that the connector 206 must overcome during vertical translation. Accordingly, reducing any potential pressure forces that the connector 206 must overcome during vertical translation allows the connector 206 to have a narrow width 238 and still provide stability and alignment during the imaging process as described above. Additionally, reducing the size of the connector 206 allows the form factor of the imaging system 100 shown in FIG. 1.

In other embodiments, the use of at least two attachment points results in the x-ray detector 204 being independently actuated or being actuated at a different speed than the x-ray source 202, as further described below.

lifting mechanism

An exemplary imaging system having a form factor that is smaller than conventional imaging systems, in which the X-ray module is translated vertically, may be implemented as shown in FIG. 3A-3B. Fig. 3A provides a cross-sectional side view of the imaging system 100. Fig. 3A provides a top-down, cross-sectional view of the imaging system 100.

In some embodiments, the imaging system 100 comprises a lifting mechanism comprising one or more motors, one or more linear actuators, one or more pulleys, one or more cables, one or more balancing devices, and/or other components configured to lower and lift the x-ray module 200 inside the frame of the imaging system 100.

For example, the hoist includes electric motors 256, 268 shown in FIG. 3B as a source of driving force. Motors 256, 268 may be connected to an external power source (eg, wall outlet or energy storage device) and an inverter. The energy storage device may include, for example, one or more batteries, capacitive storage units, or other storage tanks suitable for storing electrical energy that can be used to power one or more motors. When the energy storage device is implemented using one or more batteries, the batteries may include, for example, nickel metal hydride batteries, lithium ion batteries, lead acid batteries, nickel cadmium batteries, lithium ion polymer batteries, and other types of batteries.

In some embodiments, motors 256, 268 may be controlled by a microprocessor controller. The microprocessor controller may receive data from one or more encoders mounted on the x-ray source 202 and x-ray detector 204, respectively. Said one or more encoders may communicate to the microprocessor controller data relating to the position and velocity of the x-ray source 202 and x-ray detector 204, respectively. In some embodiments, the microprocessor controller may be configured to align the x-ray detector 204 with the x-ray source 202 prior to the imaging process, as described below.

In some embodiments, the driving force generated by motors 256, 268 in connection with one or more linear actuators may be transmitted to cables 252, 262 through sheaves 254, 264, 266, respectively, to move the X-ray module 200. For example, cables 252, 262 may include straps and/or flexible slings. In some embodiments, the cables 252, 262 may comprise a cross section that is approximately 1.27 by 0.32 cm. one or more respective pulleys (eg, pulleys 254, 264, 266).

In some embodiments, the pulleys 254, 266, and 266 may include a toothed pulley, an idler pulley, and/or any such pulley configured to match the translational movement of the cables 252, 262. In some embodiments, the pulleys 254, 264, 266 may include a pulley element , and the rotation of the pulley element is provided around almost

- 14 042559 horizontal axis in at least one position of use.

In some embodiments, linear actuators communicatively coupled to motors 256, 268 may include a lift cylinder and piston. One example of a lift cylinder is a hydraulic device capable of applying a required force. In some embodiments, the linear actuators comprise at least one of a hydraulic cylinder, a servo motor, a gear train, and a rack and pinion system. In some embodiments, the lift cylinder of the linear actuators may be in communication with a piston, which may have a movable actuator arm. The motors 256, 268 can generate and transmit force to the lift cylinders which drive the actuator arm in linear motion.

In some embodiments, the lifting mechanism is configured to lower and raise the x-ray module 200 within frame 270. Frame 270 may include one or more vertical rails and/or channels. Said one or more vertical guides or channels may be configured to provide a vertical path along which the x-ray module 200 moves when it is raised and lowered. For example, the x-ray source 202 and the x-ray detector 204 can move within the vertical paths of the frame 270 as the x-ray module 200 is raised and lowered. In some embodiments, the vertical paths of the frame 270 along which the x-ray source 202 and x-ray detector 204 travel may be of different sizes. For example, the x-ray source 202 may move within a vertical path having a first height range, while the x-ray detector 204 may move with the x-ray source 202 but within a vertical path having a second height range that exceeds the first height range. height, as described in more detail below.

With reference to the above, cables 252, 262 supporting the x-ray module 200 during the imaging process can be attached to separate attachment points 214, 212 mounted on the x-ray detector 204 and the x-ray source, respectively. For example, cable 252 has a first end at attachment point 214 mounted on x-ray detector 204, while cable 262 has a first end at attachment point 212 mounted on x-ray source 202. Cables 252, 260 may be secured at attachment points 214, 212 by any number of known attachment devices. For example, one or more cables 252, 262 may be secured with standard suspension elements such as a loop connector provided in a steel cable and sometimes referred to as a complex or dutch loop. Such an element may be wrapped around a protrusion on the device to be lifted (eg, x-ray detector 204 and x-ray source 202) to provide a force-transmitting connection between the two components.

In some embodiments, the lifting mechanism includes one or more balancing devices to facilitate movement of the x-ray module 200 by providing a balancing mechanism that allows the x-ray module 200 to move efficiently and easily within frame 270. For example, cable 252 may be passed through pulley 254 and may extend downward to connect to balancer 250. Similarly, cable 262 may be routed through pulleys 266, 264, respectively, and may extend downwards to connect to balancer 260.

In some embodiments, balancing devices 250, 260 may be constructed from a plate of iron or other heavy metal. For example, the balancing device 250 may be approximately 30 cm long, 30 cm wide and 1.9 cm deep, and may have a weight approximately equal to that of the x-ray source 202 (eg, 22 kg). Similarly, the balancing device 260 may be approximately 10 cm long, 30 cm wide and 0.75 cm deep, and may have a weight approximately equal to that of the x-ray detector 204 (eg, 7.2 kg).

In some embodiments, with reference to the aforementioned lifting mechanism, it is configured to raise and lower the x-ray module 200 by activating motors 256, 268 that actuate linear actuators that drive and translate cables 252, 262 passed through pulleys 254 and 264, 266, respectively, for vertical translation of the x-ray detector 204 and x-ray source 202. The weight of each of the elevating x-ray detector 204 and x-ray source 202 can apply a force to respective pulleys 254 and 264, 266 via respective cables 252, 262, respectively. The force applied through cables 252, 262 can be balanced by balancing devices 250, 260 connected to cables 252, 262, respectively.

In some embodiments, one or more balancing devices may be configured to balance and/or maintain upward pressure on the x-ray module 200 when the x-ray detector 204 and x-ray source 202 are translated

- 15 042559 are moved during the rendering process. An exemplary imaging system having a form factor that is smaller than conventional imaging systems, in which the lifting mechanism includes one or more balancing devices to facilitate movement of the x-ray module, may be implemented as shown in FIG. 4A-4B. Fig. 4A provides a side cross-sectional view of the lifting mechanism of the imaging system 100. Fig. 4B provides a perspective view of the lifting mechanism of the imaging system 100.

In some embodiments, as shown in FIG. 4A, the lifting mechanism may include one or more cables supporting the x-ray module 200 and connected to one or more balancing devices. For example, cable 252 attached to x-ray detector 204 may be passed through pulley 514 and may extend downward to connect to balancer 524. Similarly, cable 262 attached to x-ray source 202 may be connected to balancer 522.

Said one or more balancing devices may comprise a tension adjusting mechanism configured to control the necessary force to tension the cables connected to the balancing devices. For example, the force required to raise or lower the x-ray source 202 and the x-ray detector 204 can be controlled by the tension adjustment mechanism. In this example, each of the balancing devices 524, 522 may have a tension adjustment mechanism used to control the necessary force to tension the cables 252, 262, respectively. As an alternative embodiment, the tension adjustment mechanism may be configured to only hold the x-ray module 200 suspended. In some embodiments, said one or more balancing devices may comprise a manual adjustment mechanism, such as a screw adjustment mechanism, configured to manually adjust the required force settings.

In some embodiments, said one or more balancing devices may be mounted at the bottom of the frame of the imaging system 100. With reference to the above, one or more cables may support the x-ray source 202 and the x-ray detector 204 by passing from the top of one or more pulleys and continuing down to connect with one or more balancing devices. For example, one or more cables may be attached to the x-ray detector 204, may run over one or more pulleys, and may be connected to two balancing devices mounted on the x-ray detector 204 side of the imaging system 100. Similarly, the x-ray source 202 may be supported by one or more cables running over one or more pulleys and connected to two balancing devices on the x-ray source 202 side of the imaging system 100. In this example, the four balancing devices may be configured to support the weight of the x-ray module 200 during the translation required for the imaging process.

In some embodiments, each of said one or more balancing devices may be designed or made similar to an instrumental balancer. For example, instrument balancers may include devices manufactured by Nasco Industries such as the Model TBJ-1522. In some embodiments, these balancing devices may use rotational springs in conjunction with a tapered cable drum to provide a nearly constant force on the cable regardless of stretch.

For example, and as shown in FIG. 4B, four balancing devices 524 may be configured to support the weight of the x-ray module 200 (shown in FIG. 2A) during the translation required for the imaging process. With reference to the above, four balancing devices 524 may be installed at the bottom of the frame of the imaging system 100. For example, four balancing devices 524 may be installed near the base frame 602.

As noted above, the imaging system may include a frame surrounded by a housing. In some embodiments, the frame may further comprise a number of separate support frames. For example, the imaging system 100 may include a base frame 602, a side vertical frame 604 of the x-ray detector 204, and a side vertical frame 606 of the x-ray source 202. In some embodiments, the base frame 602, the X-ray detector 204 side vertical frame 604, and the X-ray source 202 side vertical frame 606 may be formed using a welded aluminum structure.

As noted above, the one or more cables may support the X-ray source 202 and the X-ray detector 204 by passing from the top of one or more pulleys and continuing down to connect to one or more balancing devices. For example, four balancing devices 524 may be configured to support cables 512 passing over four pulleys 514. In some embodiments, cables 512 may be attached to the x-ray detector 204, may pass over pulleys 514

- 16 042559 and can be connected to two balancing devices 254 installed on the side of the X-ray detector 204 of the imaging system 100. Similarly, the x-ray source 202 may be supported by cables 512, which may be attached to the connector 206 near the x-ray source 202 and thus support some of the weight of the x-ray module.

In some embodiments, cables 512 extending downward from pulleys 514 may be attached to a vertical member 450. The vertical member 450 may be configured to support a pulley 452. In some embodiments, a cable 454 may extend from a rigid support 456 near the base frame 602. For example, the cable 454 may extend from the top of the pulley 452 and then down and may be attached to the connector 206 near the x-ray detector 204. In some embodiments, the vertical member 450 may be attached to the movable slide 305 of the two vertically mounted linear actuators 303. In some embodiments, the connector 206 may be attached to the movable slide 306 of the two vertically mounted linear actuators 304.

In some embodiments, the balancers 524 may be configured to support the x-ray imaging module on the side of the x-ray detector 204 by directly supporting the pulley 452 and cable 454. By directly supporting the pulley 452 and cable 454, the balancers 524 in turn support x-ray module. By using four balancers 524 to support the weight of the x-ray module, the imaging system 100 can use four linear actuators (eg, 303, 304) to provide vertical movement of the x-ray imaging module.

In some embodiments, the imaging system 100 may include one or more components for stabilizing the imaging system 100 and ensuring that the imaging system 100 is level with the floor on which it is placed. For example, the imaging system may include four leveling feet 608 configured to support the base frame 602. In some embodiments, the leveling legs 608 may be configured to adjust the level of the imaging system 100.

With reference to the above, the imaging system 100 may include a floor 116 attached to the inner surface of the base module 112 shown in FIG. 1. With reference now to FIG. 4B, the imaging system 100 may include one or more components configured to support the floor on which the subject stands during the imaging process. For example, one or more support elements 610 may be attached to the base frame 602 and may provide support for the floor.

Synchronized movement

In some embodiments, the lifting mechanism described above is configured to lift the x-ray module 200 in a synchronized manner. Namely, during the imaging process, the movement of the x-ray source 202 is synchronized with the movement of the x-ray detector 204. By synchronizing the movement of the x-ray source 202 and the x-ray detector 204, the x-ray fan beam 208 is at the same vertical height as the active area 210 of the x-ray detector 204 during the imaging process. With reference to the above, the connector 206 that connects the X-ray source 202 and the X-ray detector 204 is configured to provide additional stability and alignment between the X-ray source 202 and the X-ray detector 204 during this synchronized movement.

Independent movement

In some embodiments, the lifting mechanism is configured to raise and lower the x-ray source 202 independently of the x-ray detector 204. For example, the hoist raises and lowers the x-ray detector 204 by activating a motor 256 that drives a linear actuator that drives and translates a cable 252 that runs over a pulley 254 to translate the x-ray detector 204. Similarly, the hoist raises and lowers the x-ray source 202 by activating a motor 268 which drives a linear actuator that drives and translates a cable 262 that runs over pulleys 264, 266 to translate the x-ray source 202 x-rays.

Further, with reference to the above, due to the use of a single attachment point and a single linear actuator, conventional imaging systems thus cannot tilt individual imaging components (eg, x-ray source and x-ray detector). Because the X-ray source and X-ray detector must be exposed during the imaging process,

- 17 042559 the X-ray source must be moved to the topmost part of the frame. Because of the need to move the x-ray source to that very top, conventional imaging systems are required to be sized to match the height range traveled by both the x-ray source and the x-ray detector, which contributes to the height of the imaging system. Accordingly, the overall height of a conventional imaging system is greater than the overall height of a standard doorway, making it impossible to transport the imaging system through a standard doorway without extensive disassembly and mechanical lifting equipment. Additionally, the use of a single linear actuator to raise and lower the X-ray module requires a significantly larger connector, with reference to the above, which contributes to the form factor of the imaging system.

In contrast, with reference to the above, the x-ray source 202 may move within a vertical path having a first height range, while the x-ray detector 204 may move with the x-ray source 202 within a vertical path having a second height range that exceeds first height range. By independently driving the x-ray source 202 and the x-ray detector 204, the x-ray source 202 can be angled or tilted towards the x-ray detector 204 during the imaging process. Accordingly, instead of moving the x-ray source 202 to the lowest or highest part of the imaging system 100 shown in FIG. 1, the x-ray source may be angled so that the emitted x-ray beam is directed towards the x-ray detector 204 even when the x-ray source 202 is below or above the x-ray detector 204. This allows the imaging system 100 to maintain its reduced size, which contributes to the overall small form factor of the imaging system 100.

An exemplary imaging system, having a form factor that is smaller than conventional imaging systems, in which the x-ray source moves vertically and independently of the x-ray detector, may be implemented as shown in FIG. 5A-5B. Fig. 5A shows a cross-sectional side view of the imaging system 100 with the x-ray source and x-ray detector in the raised position. Fig. 5B provides a side cross-sectional view of the imaging system 100 with the x-ray source and x-ray detector in the lowered position.

In some embodiments, by independently driving the x-ray source 202 and the x-ray detector 204, the x-ray source 202 may be angled or tilted towards the x-ray detector 204 during the imaging process. For example, when the x-ray source 202 is in the raised position 350 shown in FIG. 5A, the x-ray source 202 is tilted upwards and towards the x-ray detector 204. Similarly, when the x-ray source 202 is in the lowered position 351 shown in FIG. 5B, the x-ray source 202 is tilted downward and towards the x-ray detector 204.

In some embodiments, x-ray source 202 may include a focal spot 241 from which a fan beam of x-rays 208 is emitted. Focal spot 241 may be substantially equidistant from the edges of x-ray source 202. For example, the focal spot 241 may be located centrally within the x-ray source 202 and may include a distance 243 from any edge of the x-ray source 202.

An upward angle or inclination of the X-ray source 202 allows the X-ray source 202 to direct a fan beam of X-rays 208 into the X-ray detector 204 to scan the topmost portion of an object without having to raise the X-ray source 202 to the level of the X-ray detector 204 (e.g., X-ray source 202 x-rays located below the x-ray detector 204). As shown in FIG. 5A, by tilting or tilting the X-ray source 202 during the imaging process, the X-ray beam 208 emitted from the focal spot 241 is directed to the X-ray detector 204 without moving the X-ray source 202 to the uppermost portion of the imaging system 100. Namely, distance 243 may not be covered by x-ray source 202.

Similarly, angling or tilting the x-ray source 202 downwards allows the x-ray source 202 to direct the fan beam of x-rays 208 into the x-ray detector 204 to scan the lowest portion of the object without having to lower the x-ray source 202 to the level of the x-ray detector 204 (e.g. , the x-ray source 202 is positioned above the x-ray detector 204). As shown in FIG. 5B, by angling or tilting the x-ray source 202 during the imaging process, the x-ray beam 208 emitted from the focal spot 241,

- 18 042559 is sent to the x-ray detector 204 without moving the x-ray source 202 to the lowest portion of the imaging system 100. Namely, distance 243 may not be covered by x-ray source 202.

In some embodiments, the angle of the x-ray source 202 (eg, approximately 5° to 20°) may increase the path of the x-ray beam through the subject's body by only a few percent. Since the angle of inclination only slightly increases the X-ray path length, the increase in radiation due to the increased X-ray path length is negligible. In contrast, in some conventional systems, X-rays enter the subject's body at an angle of 45°, which results in the subject being exposed to increased levels of radiation.

Let us turn again to Fig. 2A to illustrate how tilting the x-ray source 202 either up or down allows the imaging system 100 to maintain a smaller form factor than conventional imaging systems. For example, the height 216 of the x-ray detector 204 is approximately 10 cm, while the height 248 of the x-ray source 202 is approximately 40 cm. or down to the height 132 of the imaging system 100 shown in FIG. 1, only the height 216 of the x-ray detector 204 is affected. Accordingly, the imaging system 100 can maintain a lower height 132, whereby the imaging system 100 can be transported through a standard doorway.

With reference again to FIG. 5A-5B, in some embodiments, the motors 256, 268 used to raise and lower the x-ray module 200 during the imaging process from the lowest position 351 to the highest position 350 may be configured to operate at different speeds.

In some embodiments, the imaging system 100 may include a motion control unit (not shown) configured to adjust the individual speeds at which the motors 256, 268 operate. For example, the individual speeds at which the motors 256, 268 operate may be configured with one or more microprocessor controllers. By controlling the speeds at which the motors 256, 268 operate, the imaging system 100 can raise and lower the x-ray module 200 without rotation, with co-rotation in one direction, with co-rotation in the other (e.g., opposite) direction, or with any combined co-rotation. rotation.

In some embodiments, motor 254 driving x-ray detector 204 may operate at about 12% to 13% faster than motor 266 driving x-ray source 202. During the rendering process and as shown in FIG. 5A-5B, the difference in speeds at which the motors 254, 266 operate causes the X-ray detector 204 to travel a distance that is approximately twelve to thirteen percent greater than the distance traveled by the X-ray source 202 over the same period. time. This is because the distance that the x-ray detector must travel during the imaging process is approximately 15 percent greater than the distance that the x-ray source 202 must travel.

Mechanism of extension

With reference to the above, maintaining a small form factor can be a factor for the portability of an imaging system. Of particular importance is the ability of the imaging system to pass through standard sized doorways without extensive disassembly. However, with reference to the above, some doorways (eg, prison doorways) may have one or more dimensions that are smaller than the dimensions of a standard size doorway (eg, less than 200 cm). Another factor is the ability to visualize a person who may be taller than a standard sized doorway. Namely, the imaging system according to one embodiment has one height during transport and a different height when imaging a person whose height is smaller than the doorway through which the imaging system is transported. One way of providing both is to use a lifting mechanism that can perform a range of movement that exceeds the height of the imaging system to temporarily raise the x-ray source and x-ray detector. For example, the lifting mechanism may be configured to raise the x-ray source and the x-ray detector during the imaging process to image a person whose height exceeds the height of the imaging system through the use of one or more mechanisms (e.g., extend, cut, etc.) .

Fig. 6A-6B show an exemplary imaging system 600 (which may be an embodiment of the imaging system 100) having a form factor that is smaller than conventional imaging systems, in which an X-ray source and an X-ray detector connected by a coupling component move vertically within the frame of the system 600. visualization along individual vertical paths with variable height ranges, which can be implemented as shown in FIG. 6A-6B. Fig. 6A provides a side cross-sectional view of the system.

600 imaging with the X-ray source and X-ray detector in the lowered position. Fig. 6B provides a side cross-sectional view of the imaging system 600 with the x-ray source and x-ray detector in an elevated position.

In some embodiments, the lifting mechanism described above is configured to raise the x-ray source 202 within a vertical path having a first height range and raise the x-ray detector 204 within a vertical path having a second height range that is greater than the first height range. In some embodiments, the vertical path within which the x-ray detector 204 is raised may exceed the height of the imaging system 600. Through the vertical path of the X-ray detector 204 exceeding the height of the imaging system 600, it is possible for the system 600 to render a subject that would otherwise be impossible due to height limitations of the imaging system 600 (e.g., the height of the person 101 exceeds the height 132 of the imaging system 100 shown in FIG. . 1).

For example, at the start of the imaging process, the x-ray module 200 (eg, x-ray source 202 and x-ray detector 204) shown in FIG. 2A is in the lowest position 352 shown in FIG. 6A. Similarly, at the end of the imaging process, the x-ray module 200 is in the highest position 350 shown in FIG. 6B. Accordingly, the imaging system 600 may be configured to render a person 110 whose height exceeds the height 492 of the imaging system 600.

In some embodiments, the lifting mechanism may be configured to raise the X-ray detector 204 beyond the height of the frame of the imaging system 600 (eg, to the topmost position 350) only during the imaging process. Namely, after the imaging process is completed, the X-ray detector 204 is lowered and returned to the lowest position 352. Raising the X-ray detector 204 above the height of the imaging system 600 during the imaging process only allows the imaging system 600 to be transported through standard sized doorways, since the height 492 imaging system 600 is not affected by this extent.

In some embodiments, the lifting mechanism may include one or more movable skids, one or more motors, one or more linear actuators, one or more pulleys, one or more cables, one or more balancing devices, a rigid support, and/or other components. , configured to lower and raise the x-ray module 200 within the frame of the imaging system 600.

In some embodiments, the x-ray source 202 may be coupled to a movable sled 306. For example, a hoist raises and lowers the x-ray source 202 by activating a motor that drives a linear actuator 304 that drives a movable sled 306 connected to the linear actuator 304. Namely, the lift raises the x-ray source 202 from the first position 368 (shown in FIG. 6A) at the start of the imaging process to the second position 366 (shown in FIG. 6B) at the end of the imaging process by activating a motor that drives a linear actuator 304 which drives and moves a movable slide 306 connected to the linear actuator 304.

In some embodiments, x-ray detector 204 may be connected to cable 454. For example, cable 454 may include a first end at an attachment point mounted to x-ray detector 204. In some embodiments, a cable 454 may be passed through a pulley 452 and may extend downward to connect to a rigid support 456.

In some embodiments, a rigid support 456 may be installed within a linear actuator 303 containing a fixed frame. In other embodiments, the implementation of the rigid support 456 can be installed in any stationary location within the frame of the system 600 imaging.

In some embodiments, the implementation of the pulley 452 may be mounted on a vertical element 450, located inside the frame of the system 600 imaging. For example, a pulley 452 may be mounted on the upper end of the vertical member 450 while the lower end of the vertical member 450 may be rigidly attached to the movable slide 305 of the linear actuator 303. In some embodiments, the vertical member 450 may be approximately 38 cm in length. .

In some embodiments, the lifting mechanism raises the x-ray detector 204 from the first position 480 (shown in FIG. 6A) at the start of the imaging process to the second position 482 (shown in FIG. 6B) by activating a motor that drives the linear actuator 303, which drives and translates the movable slide 305 connected to the linear actuator 303.

In some embodiments, at the beginning of the imaging process, the slide 305 is located at the first position 470, the pulley 452 is located at the first position 471, and the x-ray detector 204 is located at the first position 480. With reference to the above, during the imaging process, the lifting mechanism raises the detector 204 x-rays by translational movement of the movable sled 305 from the first position 470 to the second position 472. When the movable sled 305 is translated, the pulley 452 (mounted on the vertical member 450, which is rigidly attached to the movable sled 305, as explained above) moves from the first position 471 to the second position 473.

By actuating the linear actuator 303, which vertically translates the movable sled 305 from the first position 470 to the second position 472, the pulley 452 is movable from the first position 471 to the second position 473. The translational movement of the movable sled 305, in turn, raises the X-ray detector 204 from the first position 480 to the second position 482. By means of the lifting mechanism, the distance that the movable sled 305 travels is approximately 107 cm, while the distance that the X-ray detector 204 travels is approximately 214 cm. Accordingly, the distance traveled by the x-ray detector 204 is twice the distance traveled by the moving sled 305.

Automated billing

In some embodiments, prior to initiating the imaging process, the imaging system 100 of FIG. 1 may be configured to align the x-ray detector 204 with the x-ray source 202. For example, the X-ray detector 204 may be located at the lowest position 351 shown in FIG. 4B. The lifting mechanism described above drives the X-ray detector 204 independently of the X-ray source 202 until the X-ray beam emitted by the X-ray source 202 is intercepted and absorbed by one or more X-ray detector photodiode arrays. For example, the lifting mechanism may include one or more linear actuators mounted at each end of the x-ray detector 204 configured to move the x-ray detector 204 relative to the connector 206. The translational movement of the x-ray detector 204 may be small and may include translational moving at least one end of the x-ray detector 204. In some embodiments, the lifting mechanism is configured to rotate the x-ray detector 204 about a horizontal axis.

In some embodiments, imaging system 100 is configured to detect a signal comprising a signal level corresponding to one or more photodiodes in one or more photodiode arrays of x-ray detector 204 absorbing a specific amount of radiation energy emitted by x-ray source 202. Namely, the stronger the signal, the greater the amount of radiation energy absorbed. A stronger signal indicates that an alignment between the X-ray detector 204 and the X-ray source 202 may have been achieved. The x-ray detector 204 may be progressively moved (eg, raised or lowered) until a threshold level signal level is detected. In some embodiments, this process may iteratively repeat until the x-ray detector 204 and x-ray source 202 are aligned.

In some embodiments, after the desired signal level is reached, the imaging system 100 is configured to notice the alignment between the X-ray detector 204 and the X-ray source 202 that is a consequence of the desired signal level. Namely, the imaging system 100 is configured to use the resulting exposure between the X-ray detector 204 and the X-ray source 202 during the imaging process.

Identity Verification

With reference to the above, the visualization system 100 can be used to detect latent security threats on people entering high security areas (eg, airports, prisons, etc.). As described above, imaging system 100 may generate images that show hidden threats in or on the human body. Because these images may later be used as physical evidence in various government actions taken against the subject, the management of acquired information (eg, image data), including access issues and chain of custody, must be considered. Of particular importance is the ability to confirm and/or verify the identity of a subject using only image data. For example, the subject may subsequently dispute that an image showing a hidden threat is indeed theirs.

- 21 042559 or her image.

In some embodiments, with reference to the aforementioned imaging system 100 of FIG. 1 may include one or more features configured to facilitate verification of a personal identity. For example, the imaging system 100 may be configured to capture information related to a subject. The information may include visual information (eg, image, video, audio), biometric information (eg, fingerprint, face recognition, retinal scan, etc.), and/or other similar information.

In some embodiments, one or more input devices configured to capture information related to a subject may be associated with the imaging system 100. For example, said one or more input devices may include a biometric input device and an image input device. In some embodiments, the biometric input device may comprise a digital device, such as a fingerprint scanner or a retinal scanner, configured to acquire a scanned image of the subject's retina. The visual input device may include a device such as an image camera and/or other device capable of capturing information including, but not limited to, visual information, video information, and audio information.

In some embodiments, said one or more input devices may be associated with or combined with a control panel 124 and/or other interface within the imaging system 100. For example, prior to entering interior space 119 of imaging system 100, person 110 may be positioned in front of a control panel 124 associated with an imaging camera such that an image associated with person 110 can be captured. In some embodiments, said one or more input devices may be built into one or more housing components of the imaging system 100 (eg, X-ray source compartment 120). For example, the imaging input device may capture a video of the subject at the same time as acquiring image data during the rendering process.

In some embodiments, information generated by imaging system 100, including image data and information captured by one or more input devices, may be tagged, time-stamped, annotated, and/or otherwise processed such that all information generated rendering system 100 may be synchronized, grouped, annotated, and/or otherwise associated with it. For example, video information captured by an image sensor may be synchronized with image data generated by an x-ray detector. Subject-related information generated by one or more input devices (and/or information based thereon) may be stored and/or transmitted in electronic files. Capturing information related to a subject and associating it with image data, with reference to the above, may allow the subject's identity to be verified. For example, while image data alone may not be sufficient to definitively establish a subject's identity, using an image of the subject with image data may provide the necessary confirmation.

Fig. 7 is a flowchart showing exemplary operations that may be performed to operate the hoist to perform an imaging process. In some implementations, the operations may be implemented in one or more processing devices (e.g., a digital processor, an analog processor, a digital circuit capable of processing information, a CPU, a graphics processor, a microcontroller, an analog circuit capable of processing information, machine, and/or other mechanisms for electronic information processing). Said one or more processors may include one or more devices performing some or all of the operations in response to instructions electronically stored on one or more electronic storage media. Said one or more processing devices may include one or more devices implemented in hardware, firmware, and/or software configured to perform one or more operations.

At operation 701, a control signal or command is received to initiate the rendering process. For example, as described above, the rendering process may be initiated by a user-initiated command entered through the control panel 124 or other such interface. The user command provided via the control panel 124 is translated into initiating a rendering process in the rendering system 100 .

At operation 702, the step of ensuring that the x-ray source is in geometric alignment with the x-ray detector is performed. For example, as described above, the x-ray detector 204 is independently driven to vertically translate in either direction to intercept the x-ray fan beam 208,

- 22 042559 emitted by the X-ray source 202. When the X-ray detector 204 intercepts the X-ray fan beam, the X-ray detector 204 can detect a signal with a specific signal level. The X-ray detector 204 may iteratively advance until a signal with a threshold signal level is detected, which assumes that the X-ray source 202 and the X-ray detector 204 are in optical alignment.

At operation 703, the x-ray source and the x-ray detector are independently driven to move to a position of their mutual readiness to receive signals associated with the imaging of the lowermost region of the subject. For example, as described above, to obtain signals associated with imaging of the lowermost portion of the subject, the X-ray detector 204 is placed on the first level, while the X-ray source 202 is placed on the second level, the second level being higher than the first level. When in the second level, the x-ray source 202 is tilted downward to emit an x-ray beam towards the x-ray detector 204, ready to receive signals associated with the imaging of the lowermost portion of the subject.

In operation 704, the x-ray source and the x-ray detector are jointly moved such that the x-ray source is translated vertically at a first speed and the x-ray detector is translated vertically at a second speed relative to each other to obtain signals associated with the imaging of the subject, for except for the lowermost and uppermost portions of the subject. For example, as described above, the x-ray detector 204 is raised by activating a motor 256 that drives a linear actuator that drives and translates a cable 252 attached to the x-ray detector 204 that is passed through a pulley 254 to provide translational movement of the x-ray detector 204. Similarly, x-ray source 202 is raised by activating motor 268, which drives a linear actuator that drives and translates cable 262, which is passed through pulleys 264, 266, to translate x-ray source 202.

At operation 705, the x-ray source and x-ray detector are independently driven to complete translation 704 to a position suitable for receiving signals associated with imaging of the uppermost portion of the subject. For example, as described above, to obtain signals associated with imaging of the lowest region of the subject, the X-ray detector 204 is raised to the third level, while the X-ray source 202 is raised to the fourth level, the fourth level being lower than the third level. When in the fourth level, the x-ray source 202 is tilted upward to emit an x-ray beam towards the x-ray detector 204 to receive optical signals associated with imaging.

At operation 706, image data corresponding to the image of the subject being scanned during the rendering process is received. For example, as described above, during the imaging process, the optical signals generated by the photodiode array in the x-ray detector 204 are converted into electrical signals. The electrical signals provide image data transmitted via analog and/or digital electronic circuits.

Where the circuits are implemented in whole or in part using software, in one embodiment, those software elements may be configured to function with a computing or processing system configured to perform the functionality described therein. One such exemplary computing system is shown in FIG. 8. Various embodiments are described in terms of this exemplary computing system 800. After reading this description, those skilled in the art will appreciate how this technology can be implemented using other computing systems or architectures.

With reference now to FIG. 8, computing system 800 may provide, for example, computing or processing capabilities found in desktop computers, small computers, and laptop computers; hand-held computing devices (PDA, smartphones, cell phones, PDAs, etc.); mainframes, supercomputers, workstations or servers; or any other type of special purpose or general purpose computing device as may be necessary or may be suitable for a given application or environment, such as one or more of the various components shown in FIG. 16 and described here.

Computing system 800 includes a bus 802 or other communication mechanism for transmitting information, one or more hardware processors 804 coupled to bus 802 for processing the information. The hardware processor(s) 804 may be, for example, one or more general purpose microprocessors. Computing system computing system 800 also includes main memory 808, such as random access memory (RAM),

- 23 042559 cache memory and/or other dynamic storage devices connected to bus 802 to store information and instructions to be executed by processor 804. Main memory 808 can also be used to store temporary variables or other intermediate information during instruction execution. to be executed by the processor 804. Such instructions, stored on storage media accessible to the processor 804, transform the computing system 800 into a special purpose machine that is configured to perform the operations specified in the instructions.

Computing system 800 further includes read-only memory (ROM) 808 or other static storage device coupled to bus 802 for storing static information and instructions for processor 804. Storage device 810, such as a magnetic disk, optical disk, or USB a flash drive (flash memory), etc., is provided and connected to the bus 802 to store information and commands.

Computer system 800 may be connected via bus 802 to display 812, such as a cathode ray tube (CRT) or liquid crystal display (or touch screen) to display information to a computer user. An input device 814, including alphanumeric and other keys, is coupled to the bus 802 to communicate information and select commands to the processor 804. Another type of user input device is a cursor control 818 such as a mouse, trackball, or cursor direction keys. to communicate direction information and command selection to the processor 804 and to control cursor movement on the display 812. This input device typically has two degrees of freedom in two axes, a first axis (eg x) and a second axis (eg y), which allows the device to set positions in the plane. In some embodiments, the same direction information and command selections as from a cursor control may be implemented by receiving touches on a touch screen without a cursor.

Computing system 800 may include a user interface component for implementing a GUI that may be stored in mass storage as executable program codes that are executed by the computing device(s). This and other components may include, by way of example, components such as software components, object-oriented software components, class components and task components, processes, functions, attributes, procedures, routines, program code segments, drivers, hardware software, microcode, schemas, data, databases, data structures, tables, arrays, and variables.

Computing system 800 may implement the technologies described herein using custom hardwired logic, one or more ASICs or FPGAs, firmware and/or software logic that, in combination with the computing system, cause or program computing system 800 to become a special purpose machine. In one embodiment, the techniques described herein are performed by computing system 800 in response to processor(s) 804 executing one or more sequences of one or more instructions contained in main memory 808.

Such instructions may be written to main memory 808 from another storage medium, such as storage device 88. Execution of the instruction sequences contained in main memory 808 causes processor(s) 804 to perform the method steps described herein. In alternative embodiments, hardwired circuits may be used in place of or in combination with software instructions.

The term non-transitory media and similar terms as used herein refers to any media that stores data and/or instructions that cause a machine to operate in a particular mode. Such non-transitory media may include non-volatile media and/or volatile media. Non-volatile media includes, for example, optical or magnetic disks such as storage device 88. Non-volatile media includes dynamic memory, such as main memory 808. hard disk, solid state drive, magnetic tape, or any other magnetic storage device, CD-ROM, any other optical storage device, any physical media with hole patterns, RAM, PROM, and EPROM, FLASH-EPROM, NVRAM, any other memory chip or cartridge and their network versions.

Non-transitory media are distinct from, but can be used with, transmission media. Communication media are involved in the transfer of information between non-transient media. For example, communication media includes coaxial cables, copper wires, and optical fibers, including wires that contain an 802 bus. Communication media may also be in the form of acoustic or light waves, such as those generated during radio data and infrared transmissions. data transfers.

Various forms of media may be involved in the transmission of one or more consecutive

-

Claims (20)

a set of one or more instructions for processor 804 to execute. For example, the commands may first reside on the remote computer's magnetic disk or solid state drive. The remote computer can load commands into its dynamic memory and send commands over the telephone line using a modem. A modem local to computer system 800 may receive data over a telephone line and use an infrared transmitter to convert the data into an infrared signal. The infrared detector may receive data transmitted in the infrared signal, and appropriate circuitry may place this data on bus 802. Bus 802 transmits data to main memory 808, from which processor 804 retrieves and executes instructions. Instructions received by main memory 808 can be retrieved and executed. Instructions received by main memory 808 may, but need not, be stored in memory 88 either before or after they are executed by processor 804. Computing system 800 also includes a communications interface 818 coupled to bus 802. Communications interface 818 provides two-way communication on one or more network links that are connected to one or more local area networks. For example, communication interface 818 may be an integrated services digital network (ISDN) card, a cable modem, a satellite modem, or a modem for providing a data connection to an appropriate type of telephone line. As another example, network interface 818 may be a local area network (LAN) card for providing a data connection to a compatible LAN (or a WAN component for WAN communication). Wireless communication channels can also be implemented. In any such implementation, network interface 818 sends and receives electrical, electromagnetic, or optical signals that carry digital data streams representing various types of information. Network link 820 typically provides data transmission over one or more networks to other information devices. For example, the network link may provide a connection over a local area network with the host computer 824 or information equipment managed by the provider 828 Internet services (Internet Service Provider - ISP). The ISP 828, in turn, provides data services over the worldwide packet data network, now commonly referred to as the Internet 828. Local area network 822 and Internet 828 use electrical, electromagnetic, or optical signals that carry digital data streams. Signals passing through various networks and signals passing through the communication channel and through the communication interface 818 that carry digital data to and from the computing system 800 are exemplary forms of communication media. Computing system 800 can send messages and receive data, including program code, via the network(s), network link, and communication interface 818. In the Internet example, the server 830 may transmit the requested code for the application through the Internet 828, ISP 828, local area network 822, and communication interface 818. The received code may be executed by processor 804 upon receipt and/or stored in memory 810 or other non-volatile storage for later execution. Other implementations, uses, and advantages of the present invention will become apparent to those skilled in the art upon consideration of the description of the invention disclosed herein and the practice of the invention. The description of the invention is to be considered illustrative only and, accordingly, the scope of the present invention is intended to be limited only by the following claims. CLAIM 1. Radiation energy visualization system comprising an X-ray source capable of emitting an X-ray beam; an x-ray detector configured to detect an x-ray beam emitted by the x-ray source, wherein the x-ray detector and the x-ray source are connected by a connecting member so that the x-ray detector and the x-ray source remain in geometric alignment so that the x-ray detector receives the x-ray beam rays during the imaging process; and a translation mechanism configured to vertically translate the x-ray source and the x-ray detector during the imaging process, so that the x-ray source is translated within the first vertical path having the first height range, and the x-ray detector is translated within the second a vertical path having a second height range, the second height range being greater than the first height range, the translation mechanism comprising a first cable and a second cable, the first cable attached to the x-ray detector at the first end and the first balancing device at the second end, the second cable - 25 042559 attached to the x-ray source at the first end and to the second balancing device at the second end, and the first cable is passed through the first pulley and the second cable is passed through the second pulley. 2. The system according to claim 1, and the x-ray source contains a collimating device; wherein the collimating device is configured to shape the X-ray beam into an X-ray fan strip by passing at least a portion of the X-rays in the X-ray beam emitted by the X-ray source through an opening in the collimating device. 3. The system of claim 1, wherein the x-ray detector comprises a first side element and a second side element, the first side element and the second side element being obtusely attached to either side of the rear element. 4. The system of claim 1, wherein the x-ray detector comprises an active zone formed by at least one photodiode array configured to absorb radiation energy associated with an x-ray beam emitted by the x-ray source. 5. The system according to claim 4, wherein the geometric alignment between the X-ray detector and the X-ray source is established by iterative vertical translation of the X-ray detector and obtaining a certain amount of radiation energy absorbed by the active zone of the X-ray detector, and this amount of radiation energy corresponds to a threshold amount radiation energy. 6. The system of claim 5, wherein the imaging process comprises receiving image data corresponding to electrical signals derived from optical signals generated by said at least one X-ray detector photodiode array in response to the X-ray detector receiving an X-ray beam emitted by an X-ray source. rays. 7. The system of claim 1, wherein the translation mechanism comprises a first linear actuator and a second linear actuator, wherein the first linear actuator is configured to vertically translate the x-ray source via the first cable, the second linear actuator is configured to perform vertical translation of the x-ray detector through the second cable; wherein the x-ray source is translated at a first speed and the x-ray detector is translated at a second speed. 8. The system of claim 1, wherein the translation mechanism is further configured to pivot the x-ray source toward the x-ray detector at a downward angle, wherein the vertical location of the x-ray detector within the second vertical path is below the vertical location of the x-ray source within the first vertical path. 9. The system of claim 1, wherein the translation mechanism is further configured to rotate the x-ray source toward the x-ray detector at an upward angle, wherein the vertical location of the x-ray detector within the second vertical path is higher than the vertical location of the x-ray source within the first vertical path. 10. The system of claim 1, further comprising a controller configured to receive user input to initiate the rendering process. 11. The method of visualization of radiation energy using the system according to any one of claims 1 to 10, comprising receiving user input by a controller configured to initiate the imaging process; establishing a geometric alignment between the X-ray source configured to emit an X-ray beam and the X-ray detector configured to detect the X-ray beam emitted by the X-ray source, the X-ray detector and the X-ray source being connected by a connecting member so that the X-ray detector beams and the x-ray source remain in optical alignment so that the x-ray detector receives the x-ray beam during the imaging process; and vertical translation of the x-ray source using a first linear actuator configured to vertically translate via the first cable independently of a second linear actuator configured to vertically translate the x-ray detector via the second cable, the first cable attached to source of x-rays at the first end and to the first balancing device at the second end, and the vertical translation of the x-ray detector using auto - 26 042559 horn linear actuator, configured to perform vertical translation through the second cable, independently of the first linear actuator, configured to perform vertical translation of the x-ray source through the second cable, so that the x-ray source translationally moves within the first vertical a path having a first height range, and the x-ray detector is translationally moved within a second vertical path having a second height range, the second height range being greater than the first height range. 12. The method of claim 11, wherein establishing geometric alignment between the x-ray detector and the x-ray source comprises iterative vertical translation of the x-ray detector. 13. The method of claim 12, wherein establishing the geometric alignment further comprises obtaining a certain amount of radiation energy absorbed by the active zone of the x-ray detector, and the active zone of the x-ray detector contains at least one array of photodiodes configured to respond to radiation energy associated with the X-ray beam emitted by the X-ray source during the imaging process. 14. The method of claim 13, wherein establishing the geometric alignment further comprises determining whether the amount of radiation energy absorbed by the active zone of the x-ray detector corresponds to a threshold amount of radiation energy. 15. The method of claim 11, wherein the second cable is attached to the x-ray detector at the first end and to the second balancer at the second end. 16. The method of claim 11, wherein the independent and vertical translation of the x-ray source and the x-ray detector comprises vertical translation of the x-ray beam at a first speed and vertical translation of the x-ray detector at a second speed. 17. The method of claim 11, wherein the independent and vertical translation of the x-ray source and the x-ray detector comprises turning the x-ray source towards the x-ray detector at a downward angle, wherein the vertical location of the x-ray detector within the second vertical path is below the vertical location x-ray source within the first vertical path. 18. The method of claim 11, wherein the independent and vertical translation of the x-ray source and the x-ray detector comprises rotating the x-ray source towards the x-ray detector at an upward angle, wherein the vertical location of the x-ray detector within the second vertical path is above the vertical location x-ray source within the first vertical path. 19. The method of claim 11, further comprising generating optical signals by the x-ray detector in response to the x-ray detector receiving an x-ray beam emitted by the x-ray source during the imaging process. 20. The method of claim 19, further comprising obtaining image data corresponding to electrical signals derived from optical signals generated during the imaging process. -