Method and system for power supply

Abstract

Various methods and systems for a power supply system are provided. In one example, a method and system includes a power distribution unit (PDU) configured to receive power from a primary power source and an uninterruptible power supply (UPS), where the UPS is configured to directly power an output alternating current (AC) load after the primary power source is unavailable, and where the UPS is configured to supply power to the AC load after the primary power source is unavailable. And the UPS is further configured to power an output high voltage direct current (HVDC) load via passing current through an autotransformer for boosting the voltage and an AC / DC converter.

Description

Technical Field

[0001] Embodiments of the subject matter disclosed herein relate to providing power to a medical imaging system in response to the absence of a primary power source due to a utility power interruption. Background Art

[0002] The computed tomography (CT) imaging system may receive AC power from a main power source, such as a utility power source. The utility power source may be connected to a utility grid. During some conditions, the main power source may not be provided in response to a power outage, a component failure, or because the main power source is accidentally disconnected.

[0003] Before shutting off the main power supply from the CT imaging system, certain components within the CT imaging system, such as an X-ray source or an X-ray tube, may require cooling during the shutdown period. Unexpected power interruptions may damage certain components in the CT imaging system, such as the X-ray source or the X-ray tube. In order to protect these components and extend their life, it may be desirable to provide backup power during an unexpected power interruption of the main power supply so as to maintain the cooling routine of the components even when the main power supply is unavailable. Summary of the invention

[0004] This summary introduces concepts that are described in more detail in the detailed description. It should not be used to identify essential features of the claimed subject matter, nor should it be used to limit the scope of the claimed subject matter.

[0005] In one aspect, a method and system include a power distribution unit (PDU) configured to receive power from a main power source and an uninterruptible power supply (UPS), wherein the UPS is configured to directly power an output alternating current (AC) load after the main power source is unavailable, and the UPS is further configured to power an output high voltage direct current (HVDC) load by passing current through an autotransformer and an AC / DC converter for boosting voltage.

[0006] In another aspect, a computed tomography (CT) imaging system includes: a rack coupled to an output HVDC load; a power cabinet coupled to an output AC load; and a power distribution unit (PDU). The PDU is configured to receive power from one of a main power source and an uninterruptible power supply (UPS), wherein when the main power source is unavailable, the UPS provides power to the HVDC load via an autotransformer. A plurality of contactors and a timer are coupled to the PDU and the UPS. A controller has computer-readable instructions stored on its memory, and the controller controls the plurality of contactors based on the availability of the main power source and input from the timer.

[0007] In yet another aspect, a method for a computed tomography (CT) imaging system, the method executed via instructions stored on a memory of a controller, the method including, in response to a main power source being unavailable, directly powering an output AC load via an uninterruptible power supply (UPS), waiting for a time delay, and powering an output HVDC load via power coupled from the UPS via an autotransformer for stepping up a voltage output from the UPS. In response to the main power source becoming available, the system executes the instructions, including waiting for a tube of the CT imaging system to cool, and powering the output HVDC load via the main power source.

[0008] The above brief description is provided to introduce selected concepts that are further described in the detailed description in a simplified form. It is not meant to identify key or essential features of the claimed subject matter, the scope of which is uniquely defined by the claims that follow the detailed description. Furthermore, the claimed subject matter is not limited to implementations that solve any disadvantages noted above or in any part of this disclosure. BRIEF DESCRIPTION OF THE DRAWINGS

[0009] The present disclosure will be better understood by reading the following description of non-limiting embodiments with reference to the accompanying drawings, in which:

[0010] Figure 1 A pictorial view of a computed tomography (CT) imaging system is shown according to one embodiment.

[0011] Figure 2 A block diagram of an exemplary CT imaging system is shown, according to one embodiment.

[0012] Figures 3 to 8 A schematic diagram showing a series of operations of the power supply circuit under normal operating conditions.

[0013] Figures 9 to 23 A schematic diagram showing a series of operations of the power supply circuit and the control circuit under power loss operating conditions.

[0014] Figures 24 to 28 A schematic diagram showing a series of operations of the power supply circuit and the control circuit power return condition.

[0015] Fig.29 A method for switching to power supply to a CT imaging system in response to the availability of power from a main power supply and controlling the return of the CT imaging system to the main power supply is shown. DETAILED DESCRIPTION

[0016] The following description relates to an embodiment of a backup power system for an imaging system, such as Figure 1 and Figure 2The backup power system for the imaging system may be configured as an uninterruptible power supply (UPS) coupled to a power distribution unit (PDU) of the imaging system. Figures 3 to 18 Depicted is a diagram of circuitry coupled to a power distribution unit (PDU) between a main power source or source providing alternating current (AC) power and an uninterruptible power supply (UPS) in normal operating conditions from when a CT imaging system is powered on until the system is ready to perform an imaging scan. Figures 9 to 23 Depicted is a diagram of the circuitry and control circuitry during a power loss condition during which the power source does not provide power to the imaging system and the UPS provides backup power. Figures 24 to 28 A diagram depicting circuitry and control circuitry during a power return condition in which the system changes from being powered by a UPS to using the mains after power has been restored. Fig.29 A method for operating a UPS based on the availability of power from a main power source is shown in FIG.

[0017] In one example of the present disclosure, an imaging system may include a gantry. The gantry may include an X-ray tube bearing (such as a liquid bearing) that may be cooled after operation. In order to perform a cooling routine of the X-ray tube bearing in the gantry, power such as electrical energy may be consumed. In a case where power is not supplied to the imaging system, a shutoff of the gantry power may occur without cooling the bearing, which may result in degradation and / or a reduced useful life.

[0018] In many applications, the imaging system may be located near a UPS system that is configured to provide backup power to the computer and console of the imaging system. However, the UPS system is not wired to provide power to the rack to achieve desired cooling prior to shutdown in the event that the main power is interrupted (e.g., absent). Additionally, the rack may not be sized to power the computer, console, and rack for an extended period of time.

[0019] The inventors have recognized these shortcomings and have proposed a way to adjust one or more circuits between the UPS and the PDU to supply power from the UPS to the rack when the main power source is unavailable. By doing so, no additional power source other than the pre-existing UPS is required, which can reduce manufacturing and installation costs while also reducing the package size of the system. For example, by adding multiple contactors (e.g., switches), the power supply source can be reliably controlled so that two power supplies (e.g., the UPS and the main power source) do not provide power at the same time.

[0020] Figures 1 to 28An exemplary configuration in which various components are relatively positioned is shown. In at least one example, if shown as being in direct contact or directly connected to each other, such elements may be referred to as being in direct contact or directly connected, respectively. Similarly, in at least one example, elements that are adjacent or adjacent to each other may be adjacent or adjacent to each other, respectively. For example, components that are arranged to be in coplanar contact with each other may be referred to as being in coplanar contact. For another example, in at least one example, elements that are positioned to be spaced apart from each other and have only space therebetween without other components may be described and referenced as such. For another example, elements that are shown to be located above / below each other, located on opposite sides of each other, or located between the left / right sides of each other may be described and referenced as such relative to each other. In addition, as shown in the figure, in at least one example, the topmost element or point of an element may be referred to as the "top" of a component, and the bottommost element or point of an element may be referred to as the "bottom" of a component. As used herein, top / bottom, upper / lower, upper / lower may be relative to the vertical axis of the figure, and may be used to describe the positioning of elements relative to each other in the figure. Thus, in one example, an element that is shown to be located above other elements is vertically positioned above other elements. As another example, the shapes of elements shown in the figures may be referred to as having those shapes (e.g., such as being rounded, straight, planar, curved, rounded, chamfered, angled, etc.). In addition, in at least one example, elements shown as intersecting each other may be referred to as intersecting elements or intersecting each other. In addition, in one example, an element shown as being within another element or shown as being outside another element may be described and referred to as such.

[0021] Although a CT system is described by way of example, it should be understood that the methods and systems of the present invention may also be useful when applied to other imaging systems, such as X-ray imaging systems, magnetic resonance imaging (MRI) systems, positron emission tomography (PET) imaging systems, single photon emission computed tomography (SPECT) imaging systems, ultrasound imaging systems, and combinations thereof (e.g., multimodal imaging systems such as PET / CT, PET / MR, or SPECT / CT imaging systems). The present discussion of a CT imaging system is provided merely as an example of a suitable imaging system.

[0022] Figure 1 An exemplary CT imaging system 100 configured for CT imaging is shown. Specifically, the CT imaging system 100 is configured to image a subject (such as a patient, an inanimate object, one or more manufactured parts) and / or a foreign object (such as a dental implant, a stent, and / or a contrast agent present in the body). In one embodiment, the CT imaging system 100 includes a gantry 108, which in turn may also include at least one X-ray source 104, which is configured to project an X-ray radiation beam 106 (see Figure 2). Specifically, the X-ray source 104 is configured to project an X-ray radiation beam 106 toward an X-ray detector array 108 positioned on an opposite side of the gantry 108. Figure 1 Only a single X-ray source 104 is depicted, but in certain embodiments, multiple X-ray sources and detectors may be employed to project multiple X-ray radiation beams 106 for acquiring projection data at different energy levels corresponding to the patient. In some embodiments, the X-ray source 104 may implement dual-energy gem spectral imaging (GSI) by fast peak kilovolt (kVp) switching. In some embodiments, the X-ray detector employed is a photon counting detector capable of distinguishing X-ray photons of different energies. In other embodiments, two sets of X-ray sources and detectors are used to generate dual-energy projections, wherein one set of X-ray sources and detectors is set to low kVp and the other set to high kVp. It should therefore be understood that the methods described herein may be implemented with single energy acquisition techniques as well as dual energy acquisition techniques.

[0023] In certain embodiments, the CT imaging system 100 further includes an image processor 110 that is configured to reconstruct an image of a target volume of a subject using an iterative or analytical image reconstruction method. For example, the image processor 110 may use an analytical image reconstruction method such as filtered back projection (FBP) to reconstruct an image of a target volume of a patient. As another example, the image processor 110 may use an iterative image reconstruction method such as advanced statistical iterative reconstruction (ASIR), conjugate gradient (CG), maximum likelihood expectation maximization (MLEM), model-based iterative reconstruction (MBIR), etc. to reconstruct an image of a target volume of a subject. As further described herein, in some examples, in addition to iterative image reconstruction methods, the image processor 110 may also use an analytical image reconstruction method (such as FBP).

[0024] In some CT imaging system configurations, an X-ray source projects a cone-shaped X-ray radiation beam that is collimated to lie in the XYZ plane of a Cartesian coordinate system and is often referred to as the "imaging plane". The X-ray radiation beam passes through an object being imaged, such as a patient or subject. The X-ray radiation beam strikes an array of detector elements after being attenuated by the object. The intensity of the attenuated X-ray radiation beam received at the detector array depends on the attenuation of the X-ray radiation beam by the object. Each detector element of the array generates a separate electrical signal that is a measurement of the X-ray beam attenuation at the detector location. The attenuation measurements from all detector elements are collected individually to produce a transmission profile.

[0025] In some CT imaging systems, a gantry is used to rotate the X-ray source and detector array around the object to be imaged in an imaging plane so that the angle at which the X-ray radiation beam intersects the object is constantly changing. A set of X-ray radiation attenuation measurements (e.g., projection data) from the detector array at one gantry angle is called a "view." A "scan" of an object includes a set of views made at different gantry angles or viewing angles during one rotation of the X-ray source and detector.

[0026] The projection data is processed to reconstruct an image corresponding to a two-dimensional slice acquired through the object, or in some examples where the projection data includes multiple views or scans, an image corresponding to a three-dimensional rendering of the object. A method for reconstructing an image from a set of projection data is known in the art as a filtered back projection technique. Transmission and emission tomography reconstruction techniques also include statistical iterative methods such as maximum likelihood expectation maximization (MLEM) and ordered subset expectation reconstruction techniques and iterative reconstruction techniques. The method converts the attenuation measurements from the scan into an integer called a "CT number" or "Hou's unit", which is used to control the brightness of the corresponding pixel on the display device.

[0027] To reduce the total scan time, a "helical" scan can be performed. To perform a "helical" scan, the patient is moved while data for a specified number of slices is acquired. Such systems produce a single spiral from a cone beam helical scan. The spiral mapped out by the cone beam produces projection data from which an image in each specified slice can be reconstructed.

[0028] As used herein, the phrase "reconstructing an image" is not intended to exclude embodiments of the invention in which data representing an image is generated rather than a visible image. Thus, as used herein, the term "image" broadly refers to both a visible image and data representing a visible image. However, many embodiments generate (or are configured to generate) at least one visible image.

[0029] The CT imaging system 100 may receive power from a main power source 122 or from an uninterruptible power supply (UPS) 124 via a power distribution unit (PDU) 120. Additionally or alternatively, the CT imaging system may receive power from a generator, wherein the power from the generator may be provided via a coupling similar to the main power source 122. In one example, the PDU 120 may include one or more sensors configured to sense the availability of power from the main power source 122. The PDU controller 130 may be configured to receive feedback from a plurality of sensors and adjust the position of one or more actuators in response to the availability of power from the main power source 122 and a command signal from a gantry control board (GCB) in the CT imaging system 102. The one or more actuators may be adjusted after a timer measures a specified time delay. In one example, the one or more actuators are contactors and / or switches configured to alternate between the main power source 122 and the UPS 124 based on the availability of power from the main power source 122. In one example, if power from the main power supply is unavailable, the PDU controller 130 may signal to actuate a first switch to disconnect a circuit in which the main power supply 122 is disposed and actuate a second switch to complete a circuit in which the UPS 124 is disposed, such that power is supplied from the UPS 124 to the CT imaging system, as will be described in more detail below.

[0030] The PDU controller 130 may include instructions stored on its memory that, when executed, cause the PDU controller 130 to adjust switches or contactors that control power received from the main power source 122 when power from the main power source is unavailable. Power from the main power source 122 may be detected via a current sensor. Feedback from the current sensor may prompt the PDU controller 130 to actuate a switch from the main power source 122 and simultaneously actuate a UPS switch from the UPS (after a time delay) to output the load of the PDU 120, thereby powering the CT imaging system 100.

[0031] Figure 2 Shows something like Figure 1 1. An exemplary imaging system 200 of the CT imaging system 100 of FIG. According to aspects of the present disclosure, the imaging system 200 is configured to image a subject 204. In one embodiment, the imaging system 200 includes a detector array 108 (see FIG. Figure 1 ). The detector array 108 also includes a plurality of detector elements 202 that together sense the X-ray radiation beam 106 that passes through a subject 204 (such as a patient) (see Figure 2) to collect corresponding projection data. Therefore, in one embodiment, the detector array 108 is manufactured in a multi-slice configuration including multiple rows of units or detector elements 202. In such a configuration, another row or rows of detector elements 202 are arranged in a parallel configuration for collecting projection data.

[0032] In certain embodiments, the imaging system 200 is configured to traverse different angular positions around the subject 204 to acquire desired projection data. Thus, the gantry 108 and components mounted thereon can be configured to rotate about the rotation center 206 for acquiring, for example, projection data at different energy levels. Alternatively, in embodiments where the projection angle relative to the subject 204 changes over time, the mounted components can be configured to move along a generally curved line rather than along a segment of a circle.

[0033] Thus, as the X-ray source 104 and the detector array 108 rotate, the detector array 108 collects data of the attenuated X-ray beam. The data collected by the detector array 108 then undergoes pre-processing and calibration to condition the data to represent the line integral of the attenuation coefficient of the scanned subject 204. The processed data is often referred to as a projection.

[0034] In some examples, individual detectors or detector elements 202 in detector array 108 may include photon counting detectors that register interactions of individual photons into one or more energy bins. It should be appreciated that the methods described herein may also be implemented using energy integrating detectors.

[0035] The acquired projection data sets may be used for base material decomposition (BMD). During BMD, the measured projections are converted into a set of material density projections. The material density projections may be reconstructed to form a pair or set of material density maps or images for each corresponding base material (such as bone, soft tissue, and / or contrast agent maps). The density maps or images may then be correlated to form a volume rendering of the base material (e.g., bone, soft tissue, and / or contrast agent) in the imaging volume.

[0036] Once reconstructed, the base material image produced by the imaging system 200 shows the internal features of the subject 204 represented by the density of the two base materials. The density image can be displayed to show these features. In traditional methods of diagnosing medical conditions (such as disease states), and more generally diagnosing medical events, a radiologist or physician will consider a hard copy or display of a density image to discern characteristic features of interest. Such features can include lesions, size and shape of specific anatomical structures or organs, as well as other features that should be discernible in the image based on the skill and knowledge of the individual practitioner.

[0037] In one embodiment, the imaging system 200 includes a control mechanism 208 to control movement of components, such as rotation of the gantry 108 and operation of the X-ray source 104. In some embodiments, the control mechanism includes a timer 209. In certain embodiments, the control mechanism 208 also includes an X-ray controller 210 configured to provide power and timing signals to the X-ray source 104. Additionally, the control mechanism 208 includes a gantry motor controller 212 configured to control the rotational speed and / or position of the gantry 108 based on imaging requirements.

[0038] In certain embodiments, the control mechanism 208 also includes a data acquisition system (DAS) 214 that is configured to sample analog data received from the detector elements 202 and convert the analog data into digital signals for subsequent processing. The DAS 214 may also be configured to selectively aggregate analog data from a subset of the detector elements 202 into a so-called macro detector, as further described herein. The data sampled and digitized by the DAS 214 is transmitted to a computer or computing device 216. In one example, the computing device 216 stores the data in a storage device or mass storage device 218. For example, the storage device 218 may include a hard drive, a floppy disk drive, a compact disk-read / write (CD-R / W) drive, a digital versatile disk (DVD) drive, a flash drive, and / or a solid-state storage drive.

[0039] In addition, the computing device 216 provides commands and parameters to one or more of the DAS 214, the X-ray controller 210, and the gantry motor controller 212 for system operation, such as data acquisition and / or processing. In certain embodiments, the computing device 216 controls system operation based on operator input. The computing device 216 receives operator input, which includes, for example, commands and / or scan parameters, via an operator console 220 operatively coupled to the computing device 216. The operator console 220 may include a keyboard (not shown) or a touch screen to allow an operator to specify commands and / or scan parameters.

[0040] Although Figure 2 Only one operator console 220 is shown, but more than one operator console may be coupled to the imaging system 200, e.g., for inputting or outputting system parameters, requesting exams, plotting data, and / or viewing images. In addition, in certain embodiments, the imaging system 200 may be coupled to multiple displays, printers, workstations, and / or the like located locally or remotely, e.g., within an institution or hospital or at an entirely different location, via one or more configurable wired and / or wireless networks (such as the Internet and / or a virtual private network, a wireless telephone network, a wireless local area network, a wired local area network, a wireless wide area network, a wired wide area network, etc.).

[0041] In one embodiment, for example, the imaging system 200 includes or is coupled to a picture archiving and communication system (PACS) 224. In one exemplary implementation, the PACS 224 is further coupled to a remote system (such as a radiology department information system, a hospital information system) and / or to an internal or external network (not shown) to allow operators at different locations to supply commands and parameters and / or gain access to image data.

[0042] The computing device 216 uses operator-provided and / or system-defined commands and parameters to operate a table motor controller 226, which in turn can control the table 114, which can be a motorized table. Specifically, the table motor controller 226 can move the table 114 to properly position the subject 204 in the gantry 108 to acquire projection data corresponding to a target volume of the subject 204.

[0043] As previously described, the DAS 214 samples and digitizes the projection data acquired by the detector elements 202. Subsequently, the image reconstructor 230 uses the sampled and digitized X-ray data to perform high-speed reconstruction. Figure 2 The image reconstructor 230 is shown as a separate entity, but in certain embodiments, the image reconstructor 230 may form part of the computing device 216. Alternatively, the image reconstructor 230 may not be present in the imaging system 200, and instead the computing device 216 may perform one or more functions of the image reconstructor 230. In addition, the image reconstructor 230 may be located locally or remotely, and may be operably connected to the imaging system 200 using a wired or wireless network. In particular, one exemplary embodiment may use computing resources in a "cloud" network cluster for the image reconstructor 230.

[0044] In one embodiment, the image reconstructor 230 stores the reconstructed image in the storage device 218. Alternatively, the image reconstructor 230 may transmit the reconstructed image to the computing device 216 to generate usable patient information for diagnosis and evaluation. In certain embodiments, the computing device 216 may transmit the reconstructed image and / or the patient information to a display or display device 232 that is communicatively coupled to the computing device 216 and / or the image reconstructor 230. In some embodiments, the reconstructed image may be transmitted from the computing device 216 or the image reconstructor 230 to the storage device 218 for short-term or long-term storage.

[0045] In one embodiment, the display 232 allows the operator to assess the imaged anatomy. The display 232 may also allow the operator to select a volume of interest (VOI) and / or request patient information, such as via a graphical user interface (GUI), for subsequent scanning or processing.

[0046] In one example, Figure 1 The UPS 124 of the embodiment may be a pre-existing UPS for the computing device 216 and its auxiliary components (e.g., the display 232, the operator console 220, etc.). As will be described herein, the inventors have discovered that it is possible to modify the UPS 124 to provide a UPS for the computing device 216 and its auxiliary components (e.g., the display 232, the operator console 220, etc.). Figure 1 The PDU 120 and one or more circuits of the UPS 124 are configured in such a way that the UPS 124, which was previously configured to power the computing device 216 only when power from the main power source 122 is unavailable, also powers the rack 108. When the main power source is available, the UPS can be charged via the main power source. In this way, the desired cooling of the rack 108 can be performed in response to an event in which power from the main power source 122 is unavailable.

[0047] Now go to Figures 3 to 28 , depicting an embodiment of the power interface of a UPS device 124 and a main power supply 122 with a PDU 120. Therefore, previously introduced components may be numbered similarly in these figures. The power distribution unit 120 may include a main power supply 122, a circuit with a circuit breaker 302, a three-phase input 304 for power, and a transformer 305. The transformer 305 may have a primary winding integrated with the three-phase input, a first secondary winding 310, and a second secondary winding 330. The power distribution unit 120 may include a plurality of wires 308 extending through corresponding switches in the three-phase input 304 to the primary winding of the transformer 305. The circuit breaker 302 may be configured to trip in response to a current of 150A (amperes) or more flowing through any of the plurality of power lines 308.

[0048] The primary winding of transformer 305 includes an electrical winding configured to draw power from a plurality of wires or conductors. The winding may be electrically coupled to windings of first secondary winding 310 and second secondary winding 330. The three-phase input 304 may be adjusted in response to the absence of power from the main power source 122 via a signal, which is transmitted via a PDU controller (e.g., Figure 1 The PDU controller 130 of the present invention is sent to the actuator of the three-phase input. The three-phase input 304 can be actuated to an open or closed position, wherein the closed position completes the circuit and allows current to flow from the main power supply 122 to the primary winding.

[0049] The first secondary winding 310 may direct power to a rectifier 316 via a plurality of wires, which may include a higher voltage than the second secondary winding 330. In some examples, the plurality of wires or conductors 312 may each include a fuse configured to interrupt the circuit in response to a current through the plurality of wires or conductors exceeding the rating of the fuse. A plurality of contacts (e.g., KXG contacts 314, KSS contacts 315) may be positioned between the first secondary winding 310 and the rectifier 316. The rectifier 316 may be a passive or active rectifier configured to convert alternating current (AC) to direct current (DC). The DC lines or conductors are coupled to an output HVDC load 320, which may be used to supply power to a rack (e.g., Figure 1 In one example, the power supplied to the output HVDC load 320 is a relatively high voltage (eg, greater than 600V DC).

[0050] The second secondary winding 330 can direct power to the output AC load 340 via a plurality of wires or conductors. Each of the plurality of wires or conductors can include a fuse rated to interrupt the circuit in response to a current exceeding the fuse rating. In one example, the fuse is rated for 50A. However, based on the size and ampere rating of the plurality of wires, the fuse can be rated for other amperes. The output AC load 340 can send power to lower power demand devices such as consoles, power cabinets, computers, etc.

[0051] Figures 3 to 8 A schematic diagram showing a series of operations of the power supply circuit under normal operating conditions. Figure 3 1 is a diagram depicting a first operating phase during normal operating conditions (e.g., receiving power from a power source). During normal conditions, KJC contact 342a and R1 contact 344 are closed during an initial startup phase. Power is provided from power source 122 to PDU TS4 346, and KJC contact 342a is closed, while KJC auxiliary contact 342b is open, as shown in FIG. Figure 4 As shown. KJC is a contact that is operable to detect whether the main power source is available. When the main power source 122 is available, the KJC contact or switch 342 is in a first position (e.g., KJC contact 342a is open and KJC auxiliary contact 342b is closed), which achieves a normal operating condition. When the main power source 122 is not available, such as before the system is turned on or during a power outage, the KJC contact or switch 342 is in a second position (e.g., KJC contact 342a is closed and KJC auxiliary contact 342b is open). Power flows back to PDU TS4 346 through UPS 124 and flows to the AC power output or load 340, PDU TS5 through Ktg contact 348. In addition, power flows from UPS 124 to KBK contact 350. As shown Figure 5As shown, the rack control board (GCB) sends a signal (e.g., XG continuous signal 352) to the PDU 120. When the contacts are normally open, the XG continuous signal 352 provides signal power to the contacts to maintain the contacts (e.g., Kss contact 315, Kxg contact 314, etc.) in a closed position. Figure 6 As shown, R1 contact 344 is switched, R2 contact 354 is opened, and Kss contact is opened. After a short delay (e.g., 1.2 seconds), Kxg contact 315 is opened, as shown. Figure 7 Then, the HVDC power is supplied to TS2 or DC load 320 via rectifier 316, and normal operation of the CT imaging system is restored, as shown in FIG. Figure 8 The system is now ready to perform a scan.

[0052] Upon detecting a power loss, the system begins a power loss mode or operation. Figures 9 to 23 is a schematic diagram depicting a series of operations of the power supply circuit and the control circuit during the power loss mode. Fig. 9 The process begins by detecting a loss of power from the main power source 122 . Fig.10 The control circuitry during this initial phase of the power loss mode is depicted. In this initial phase, the CB1 Aux 1002, R1 344, R2 354, and KJC 342 contacts are closed. Shortly after the power loss, when no power is supplied to the UPS 1214, the KJC Aux 342b contact is opened, thereby interrupting the XG continuous signal 352 to the Kss and Kxg contacts 315, 314, and closing the KJC contact 342a, as shown in FIG. Fig.11 In addition, the R1 contact 344 is switched. Fig.12 As shown, in the control circuit, the KJC and R1 contacts 342a, 344 are closed. Fig.13 The Kss and Kxg contacts 315, 314 are depicted as being closed due to the interruption of the XG continuous signal 352, which also prevents power transmission to the HVDC load 320. The XG signal 352 is no longer transmitted from the GCB, as shown in FIG. Fig.13 and Fig.14 In addition, open the R2 354 contact in the control circuit, as shown Fig.14 shown.

[0053] exist Fig.15 In the embodiment, the UPS battery power is presented to the PDU TS5 or AC load 340 through the Ktg contact 348, thereby supplying power to the rack and related control circuits, such as Fig.16 shown. Fig.171702 is a control circuit that is enabled to determine whether the power loss detected by the KJC contact switch 344 is a momentary power loss (e.g., a power flash or surge) or a significant power loss (e.g., a power loss that lasts for more than a threshold amount of time). The DR contact 1702 enables a delay of a threshold amount of time or a threshold period of time (which in some examples is 10 seconds). After the delay, the state of the DR switch 1702 changes, as shown in FIG. Fig.18 and Fig.19 After a time delay (e.g., 12.5 seconds after the main power is lost), the XG continuous signal 352 from the GCB is restored, and therefore, the R2 contact 354 is closed, and the KBK contact 350 is closed, so that the autotransformer 2002 can step up the voltage and then perform rectification so that power can be provided from the UPS 124 to the DC load 320, as shown. Figure 20 to Figure 22 As shown. In the example shown, the UPS 124 is sufficient to provide HVDC power to the DC load 320 for a period of time sufficient to cool the tubes. In other applications, the UPS 124 may be adjusted to provide different amounts of power. In addition, the Kss and Kxg contacts 315, 314 are closed. After a delay of 1 second, the TR 2202 state changes, thereby closing the KDC contact 2204 and enabling power transfer from the UPS 124 to the rectifier and DC load 320 to provide backup HVDC power to the CT imaging system ( Fig.23 ). In some examples, UPS 124 can provide backup HVDC power until power is restored from power source 122. Alternatively, UPS 124 provides power for a specified period of time (e.g., 45 minutes) to enable the CT imaging system to properly cool and shut down safely.

[0054] Figure 24 to Figure 28 A schematic diagram showing a series of operations of the power supply circuit and the control circuit power return condition. Fig.24 The initial return of power from the power source is depicted. Upon return to the power source, LVAC power is supplied via the main power source 122 rather than via the UPS 124, as shown in FIG. Fig.25 As shown. In addition, the normal XG continuous signal 342 is supplied from the GCB. The KBK 350 and KDC 2204 contacts are opened, thereby preventing the power supply from the UPS 124 to the HVDC output 320, thereby changing the standby HVDC state. The contacts KJCAux 342b and R1 344 are closed, thereby allowing the XG continuous signal 352 to reach the Kss and Kxg contacts 315, 314, as shown. Fig. 27 The Kss contact 315 is closed, and after a 1.2 second delay, the Kxg contact 314 is then closed. Normal conditions of operation are restored, and the CT imaging system is ready for operation.

[0055] Fig.29 A method 2900 is depicted for adjusting an energy source based on the availability of electrical energy from the primary power source 122. Instructions for the method may be issued by a controller of the PDU (e.g., Figure 1 The controller may be configured to receive input from one or more sensors of the PDU 120 and adjust the operation of one or more switches to change the direction of current flow.

[0056] The method 2900 begins at 2902, which includes turning on the CT imaging system power. Turning on the system power may include, for example, operating a switch and / or a plug. After turning on the system power, the CT imaging system begins to initiate normal operating conditions to prepare for performing scans. In some examples, when the system power is turned on, AC power is immediately available to AC loads via the AC power output of the PDU, such as Figure 4 The method continues to step 2904, and the GCB sends an XG continuous signal to the PDU (see Figure 5 ), thereby initiating a startup process for normal operating conditions (block 2906). Initiating normal operating conditions may include closing R2, R1, and Kss contacts, such as Figure 6 In addition, after a delay, the Kxg connector is closed (see Figure 7 ), and provide HVDC power to the racks ( Figure 8 ). The system is now in normal operating conditions and is ready to perform a scan (block 2908). During normal operating conditions, the UPS may be charged.

[0057] In block 2910, the system (e.g., rack control board, PDU controller, etc.) operates to detect a power outage. If no power outage is detected, the system continues to operate under normal conditions. If a power outage is detected, the system initiates a power loss operating condition (block 2912). Initially, the KJC auxiliary contacts are opened, interrupting the XG continuous signal ( Fig.11 ). This causes the Kss and Kxg contacts to open, thereby disabling the HVDC output from the PDU ( Fig.13). At the same time, UPS power is provided as AC output from the PDU. The delay relay is enabled. In box 2914, the system determines (e.g., using a timed delay relay) whether the power interruption has lasted for a time period exceeding a threshold. If the power interruption has not exceeded the threshold amount of time, the system identifies the power interruption as a temporary surge or flicker and returns to normal operating conditions. If the duration of the power interruption has exceeded the threshold, the delay relay contacts close and the system continues in the power loss mode operating condition (box 2916). To continue the power loss mode, the system resends the XG continuous signal via the GCB, which now uses the UPS for power. The XG continuous signal closes the Kss contact, then closes the Kxg contact, and simultaneously closes the KBK contact and enables the timed relay. As a result of the closure of the KBK relay, the transformer is energized ( Fig. 20 ). The timing relay delays the closing of the KDC contact for 1 second and then closes the KDC contact, thereby enabling HVDC power to be supplied from the UPS to the DC output of the PDU.

[0058] The method continues at block 2918 to wait for the tube of the imaging system to cool. In some examples, the system waits a predetermined amount of time (e.g., 45 minutes) to allow the tube to completely cool. In other examples, a sensor may be used to determine when the tube is completely cooled. When the tube cools, the method continues at block 2920 to determine whether main power has been restored. If main power has been restored, the system initiates a return to normal operating conditions (block 2922). Fig.25 As shown, the return to normal operating conditions begins with the supply of LVAC power via the main power supply instead of via the UPS. In addition, the normal XG continuous signal is supplied from the GCB. The KBK and KDC contacts are opened, thereby preventing the supply of power from the UPS to the HVDC output, thereby changing the standby HVDC state. Contacts KJC Aux and R1 are closed, thereby allowing the XG continuous signal to reach the Kss and Kxg contacts, as shown in FIG. Fig. 27 As shown. Close the Kss contact and, after a 1.2 second delay, then close the Kxg contact. This enables normal supply of HVDC power via the main power supply, such as Fig. 27 The system is ready to scan again and the method is completed.

[0059] If at block 2920, main power has not been restored, tube cooling is completed (block 2924) and the system is shut down and the method is complete.

[0060] As used herein, the elements or steps listed in the singular and beginning with the word "one" or "a kind of" should be understood as not excluding multiple elements or steps, unless such exclusion is explicitly stated. In addition, the reference to "an embodiment" of the present invention does not exclude the existence of additional embodiments that also include the cited features. In addition, unless explicitly stated to the contrary, the embodiment of "including", "comprising" or "having" an element or multiple elements with a specific characteristic may include additional such elements without the characteristic. The terms "including" and "in..." are used as the concise language equivalents of the corresponding terms "including" and "wherein". In addition, the terms "first", "second" and "third" etc. are only used as marks, and are not intended to impose numerical requirements or specific positional order on their objects.

[0061] The control methods and routines disclosed herein may be stored as executable instructions in a non-transitory memory and may be implemented by a control system (including a combination of a controller and various sensors, actuators, and other engine hardware). The specific routines described herein may represent one or more of any number of processing strategies (such as event-driven, interrupt-driven, multi-tasking, multi-threading, etc.). Therefore, the various actions, operations, and / or functions shown may be executed in the sequence shown, executed in parallel, or omitted in some cases. Similarly, the order of processing is not necessarily required to achieve the features and advantages of the exemplary embodiments described herein, but is provided for ease of illustration and description. One or more of the actions, operations, and / or functions shown may be repeatedly performed according to the specific strategy used. In addition, the actions, operations, and / or functions may be graphically represented as codes in a non-transitory memory of a computer-readable storage medium to be programmed into an engine control system, wherein the actions are implemented by executing instructions in a system including a combination of various engine hardware components and an electronic controller.

[0062] This written description uses examples to disclose the invention, including the best mode, and also to enable a person skilled in the relevant art to practice the invention, including making and using any devices or systems and performing any included methods. The patentable scope of the invention is defined by the claims, and may include other examples that occur to a person skilled in the art. Such other examples are intended to be within the scope of the claims if they have structural elements that do not differ from the literal language of the claims, or if they include equivalent structural elements with insignificant differences from the literal language of the claims.

Claims

1. A system, comprising: A power distribution unit (PDU) configured to receive power from a main power source and an uninterruptible power supply (UPS), wherein the UPS is configured to directly power an output alternating current (AC) load after the main power source is unavailable, and the UPS is further configured to power an output high voltage direct current (HVDC) load by passing current through an autotransformer and an AC / DC converter for boosting the voltage.

2. The system according to claim 1 further includes a first contact switch for detecting the availability of main power, wherein when the main power is available, the first contact switch is in a first position to enable a signal for achieving a normal operating condition, and wherein when the main power is not available, the first contact switch is in a second position to achieve a power loss mode operating condition.

3. The system of claim 2, further comprising a delay circuit, wherein the delay circuit is enabled to determine whether the power loss detected by the first contact switch is a momentary power loss or a significant power loss.

4. The system of claim 3, wherein the delay circuit includes a timer that closes a delay contact after a threshold time period.

5. The system of claim 4, further comprising a second contact, wherein the second contact closes after the delayed contact closes if the power loss exceeds a threshold time period, and wherein closing the second contact enables the UPS to provide power to the autotransformer.

6. The system of claim 1, wherein the output AC load supplies AC power to a plurality of systems of a computed tomography (CT) imaging system.

7. The system of claim 1, wherein the output HVDC load supplies HVDC power to a plurality of systems within a rack of a computed tomography (CT) imaging system.

8. The system of claim 1, wherein the UPS is configured to power the output AC load and the output HVDC load in response to power from the primary power source being unavailable.

9. A computer tomography (CT) imaging system comprising: a rack coupled to an output HVDC load; a power cabinet coupled to an output AC load; Power distribution unit (PDU); wherein the PDU is configured to receive power from one of a main power source and an uninterruptible power supply (UPS), wherein when the main power source is unavailable, the UPS provides power to the HVDC load via an autotransformer; a plurality of contactors and timers coupled to the PDU and the UPS; and A controller having computer readable instructions stored on a memory thereof for controlling the plurality of contactors based on availability of the primary power source and input from the timer.

10. The CT imaging system of claim 9, wherein the plurality of contactors comprises a first contact switch for detecting the availability of main power, wherein when the main power is available, the first contact switch is in a first position to enable a signal for implementing a normal operating condition, and wherein when the main power is unavailable, the first contact switch is in a second position to implement a power loss mode operating condition.

11. The CT imaging system of claim 10, further comprising a delay circuit, wherein the delay circuit is enabled to determine whether the power loss detected by the first contact switch is a momentary power loss or a significant power loss.

12. The CT imaging system of claim 11, wherein the delay circuit comprises a timer that closes a delay contact after a threshold time period.

13. The CT imaging system of claim 12, wherein the plurality of contactors further comprises a second contact, wherein the second contact closes after the delayed contact closes if the power loss exceeds a threshold time period, and wherein closing the second contact enables the UPS to provide power to the autotransformer.

14. The CT imaging system of claim 9, wherein the output AC load supplies AC power to a plurality of systems of a computed tomography (CT) imaging system.

15. The CT imaging system of claim 9, wherein the output HVDC load supplies HVDC power to a plurality of systems within a gantry of a computed tomography (CT) imaging system.

16. A method for a computed tomography (CT) imaging system, the method being executed via instructions stored on a memory of a controller, the method comprising: in response to main power being unavailable; Directly power output AC loads via an uninterruptible power supply (UPS); Waiting time delay; powering an output HVDC load via power coupled from the UPS via an autotransformer for stepping up a voltage output from the UPS; and In response to the primary power becoming available: Waiting for the tube of the CT imaging system to cool; and The output HVDC load is powered via the main power source.

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