CN109259779B - Medical image generation method and medical image processing system - Google Patents
Medical image generation method and medical image processing system Download PDFInfo
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Abstract
The invention provides a generation method of a medical image and a medical image processing system, wherein the generation method of the medical image comprises the following steps: receiving a desired layer thickness and a desired layer spacing; receiving scanning data; generating a first tomographic image group including a plurality of first tomographic images from the scanning data, the first tomographic images being associated with a preset layer thickness and a preset layer distance, the preset layer thickness being smaller than the desired layer thickness, the preset layer distance being smaller than the desired layer distance; a second tomographic image group including at least one second tomographic image associated with the desired layer thickness and the desired layer distance is generated from the first tomographic image group. The medical image generation method and the medical image processing system can effectively inhibit the artifact problem when generating the second tomographic image group with the expected layer thickness and the expected layer distance.
Description
Technical Field
The present invention relates to the field of medical images, and in particular, to a medical image generation method and a medical image processing system.
Background
Medical imaging devices such as CT, PET-CT, MR, PET-MR, and XR ray machines are increasingly used for examination of various diseases because they can acquire medical images reflecting the internal conditions of a subject at a relatively high speed. Taking a CT system as an example, the CT system generally has a scanning unit, a bed, and an image generating device. The examination couch is used for carrying a subject. Generally, after the examinee is in place on the bed in a posture such as lying on the stomach, lying on the back, or the like, the examination bed moves the part to be scanned of the examinee to a preset position suitable for detection by its own movement. At this time, the scanning means obtains scan data including the condition in the subject by emitting and receiving rays penetrating the part to be scanned, and transmits the scan data to the image generating device. The image generation device can obtain a medical image by reconstructing these scan data. The medical image obtained by examining the examinee by using the medical image equipment can clearly reflect the condition in the examinee, so the medical image equipment has very important significance for diagnosing the examinee.
However, the existing medical image generation method and medical image processing system still have the advantages that the improvement can be realized. Continuing with the CT system example, when the layer thickness to be reconstructed is large, the difference of the range of influence on the detector will be different for the same size object at different positions. This can lead to artifacts in the image. It is therefore necessary to provide a medical image generation method and a medical image processing system capable of effectively suppressing artifacts.
Disclosure of Invention
An object of the present invention includes providing a medical image generation method and a medical image processing system capable of effectively suppressing an artifact.
In order to solve at least a part of technical problems of the present invention, the present invention provides a method for generating a medical image, including:
receiving a desired layer thickness and a desired layer spacing;
receiving scanning data;
generating a first tomographic image group including a plurality of first tomographic images from the scanning data, the first tomographic images being associated with a preset layer thickness and a preset layer distance, the preset layer thickness being smaller than the desired layer thickness, the preset layer distance being smaller than the desired layer distance;
a second tomographic image group including at least one second tomographic image associated with the desired layer thickness and the desired layer distance is generated from the first tomographic image group.
In at least one embodiment of the invention, the predetermined layer distance is equal to the predetermined layer thickness.
In at least one embodiment of the invention, the preset layer thickness and the preset layer distance are determined as a function of the desired layer thickness and the desired layer distance.
In at least one embodiment of the present invention, generating the second tomogram group includes:
determining a spatial range corresponding to each second tomographic image to be generated;
and generating a corresponding second tomographic image from at least a part of the first tomographic image falling in the corresponding spatial range.
In at least one embodiment of the present invention, the step of generating the corresponding second tomographic image from the first tomographic image at least a part of which falls within the corresponding spatial range includes:
determining the proportion of the part of the first tomographic image in the space range to the first tomographic image;
determining a weight coefficient for the first tomographic image according to the ratio;
and generating the corresponding second tomographic image according to the first tomographic image and the weight coefficient.
In at least one embodiment of the present invention, generating the corresponding second tomographic image from the first tomographic image and the weight coefficient includes:
normalizing the weight coefficient of the first tomographic image including the spatial range and then multiplying the normalized weight coefficient by the corresponding first tomographic image to obtain an effective first image;
and superposing the effective first images to obtain the corresponding second tomographic images.
In at least one embodiment of the present invention, in generating the first tomogram group, only the first tomograms having at least a part thereof falling within the spatial range are generated.
In order to solve at least part of the technical problems of the present invention, the present invention also provides a medical image processing system, comprising,
a data receiving port configured to receive scan data;
a user interface configured to receive a desired layer thickness and a desired layer distance and to display a second set of tomograms associated with the desired layer thickness and the desired layer distance;
an operator configured to generate a first tomogram group including a plurality of first tomograms from the scan data, and generate the second tomogram group from the first tomogram group, the first tomograms being associated with a preset layer thickness smaller than the desired layer thickness and a preset layer distance smaller than the desired layer distance.
In at least one embodiment of the invention, the operator is configured to:
determining a spatial range corresponding to each second tomogram in the second tomogram group;
determining the proportion of the part of each first tomographic image falling in the space range in the first tomographic image in the space range;
normalizing a weight coefficient of the first tomographic image including the spatial range;
multiplying the first tomographic image including the spatial range by the respective normalized weight coefficients to obtain a valid first image;
and superposing the effective first images to obtain the corresponding second tomographic images.
In the medical image generation method and the medical image processing system according to the present invention, since the first tomographic image group having a small layer thickness and a small layer distance is generated from the scan data, and the second tomographic image group having a desired layer thickness and a desired layer distance is generated from the first tomographic image group, the problem of the artifact can be suppressed more effectively when the second tomographic image group having a desired layer thickness and a desired layer distance is generated.
Drawings
The above and other features, properties and advantages of the present invention will become more apparent from the following description of the embodiments with reference to the accompanying drawings, in which:
FIG. 1 is a schematic illustration of an operating environment in which an image processing system according to some embodiments of the present invention is shown;
FIG. 2 is a schematic diagram of an imaging system according to some embodiments of the invention;
FIG. 3 is a schematic block diagram of a medical image processing system according to an embodiment of the present invention;
FIG. 4 is a flow chart diagram of a method of generating a medical image according to an embodiment of the invention;
FIG. 5 is a schematic diagram showing a method of generating a second tomogram group from a first tomogram group in an embodiment of the present invention;
FIG. 6 is a schematic diagram showing a method of generating a second tomogram group from a first tomogram group in another embodiment of the present invention.
Description of the reference numerals
A working environment 100;
an imaging system 110;
an image processing system 120;
a network 130;
a scanning module 201;
a frame 210;
a rotatable portion 220;
a source of radiation 230;
a detector 240;
an examination table 250;
a scanning chamber 270;
an image acquisition device 310;
an image generating device 320;
a data receiving port 321;
an arithmetic unit 322;
a memory 323;
a user interface 324;
the desired layer thickness Texp;
the desired layer distance Iexp;
a preset layer thickness Tpre;
presetting a layer distance Ipre;
the first tomogram group N1;
a first image N11 of the first tomogram group;
a second image N12 of the first tomogram group;
the second tomogram group N2;
the first image N21 of the second tomogram group;
a second image N22 of the second tomogram group;
a spatial range S11 corresponding to the first image of the first tomogram group;
a spatial range S21 corresponding to the first image of the second tomogram group;
a portion N12in of the second image of the first tomogram group in the spatial range;
the portion N12out where the second image of the first tomographic image group is not in the spatial range.
Detailed Description
In order to make the aforementioned objects, features and advantages of the present invention comprehensible, embodiments accompanied with figures are described in detail below.
In the following description, numerous specific details are set forth in order to provide a thorough understanding of the present invention, but the present invention may be practiced in other ways than those specifically described herein, and thus the present invention is not limited to the specific embodiments disclosed below.
Certain terms referring to particular system components are used throughout the specification. As one skilled in the art will appreciate, different companies may refer to a component by different names. This document does not intend to distinguish between components that differ in name but not function. In the specification, the terms "include" and "comprise" are used in an open-ended fashion, and thus should be interpreted to mean "include, but not limited to …".
As used in this application, the terms "a," "an," "the," and/or "the" are not intended to be inclusive in the singular, but rather are intended to be inclusive in the plural, unless the context clearly dictates otherwise. In general, the terms "comprises" and "comprising" merely indicate that steps and elements are included which are explicitly identified, that the steps and elements do not form an exclusive list, and that a method or apparatus may include other steps or elements.
It will be understood that when an element is referred to as being "on," "connected to," "coupled to" or "contacting" another element, it can be directly on, connected or coupled to or contacting the other element or intervening elements may be present. In contrast, when an element is referred to as being "directly on," "directly connected to," "directly coupled to" or "directly contacting" another element, there are no intervening elements present. Similarly, when a first component is said to be "in electrical contact" or "electrically coupled" to a second component, there is an electrical path between the first component and the second component that allows current to flow. The electrical path may include capacitors, coupled inductors, and/or other components that allow current to flow even without direct contact between the conductive components.
Furthermore, each of the embodiments described below has one or more technical features, and thus, the use of the technical features of any one embodiment does not necessarily mean that all of the technical features of any one embodiment are implemented at the same time or that only some or all of the technical features of different embodiments are implemented separately. In other words, those skilled in the art can selectively implement some or all of the features of any embodiment or combinations of some or all of the features of multiple embodiments according to the disclosure of the present invention and according to design specifications or implementation requirements, thereby increasing the flexibility in implementing the invention.
FIG. 1 is a schematic illustration of an operating environment 100 in which an image processing system 120 is located according to some embodiments of the present invention. In these embodiments, the work environment 100 in which the image processing system 120 is located may include an imaging system 110, an image processing system 120, and a network 130. In some embodiments, the imaging system 110 may be a single modality imaging device, or a multi-modality imaging system, or a combination of multiple different imaging systems. The imaging system 110 may be used to image by scanning an object, and in some embodiments, the imaging system 110 may be a medical imaging system. The medical imaging system can acquire image information of all parts of a human body. The medical Imaging system may be a single modality system, such as a Digital Radiography (DR) system, a C-arm X-ray (C-arm) system for X-rays, a Computed Tomography (CT) system, a Magnetic Resonance Imaging (MRI) system, etc., and a multi-modality system or any combination thereof. Exemplary multi-modality systems may include computed tomography-positron emission tomography (CT-PET) systems, computed tomography-magnetic resonance imaging (CT-MRI) systems, and the like.
In some embodiments, the image processing system 120 may process the acquired data information to obtain an image and/or related information. In some embodiments, the data information may include one or a combination of text information, image information, sound information, and the like. In some embodiments, the image processing system 120 may include one or a combination of a processor, a processing core, one or more memories, and the like. For example, the image Processing system 120 may include one or more of a Central Processing Unit (CPU), an Application-Specific Integrated Circuit (ASIC), an Application-Specific Instruction Processor (ASIP), a Graphics Processing Unit (GPU), a physical computing Unit (PPU), a Digital Signal Processor (DSP), a Field Programmable Gate Array (Field Programmable Gate Array, FPGA), a Programmable Logic Device (PLD), a Controller (Controller), a Microcontroller Unit (Microcontroller Unit), a Processor (Processor), a Microprocessor (Microprocessor), an ARM (Advanced RISC), and the like. In some embodiments, the image processing system 120 may process image information acquired from the imaging system 110.
The network 130 may be a single network, or a combination of multiple different networks. For example, the network 130 may be one or a combination of Local Area Networks (LANs), Wide Area Networks (WANs), public networks, private networks, Public Switched Telephone Networks (PSTNs), the internet, wireless networks, virtual networks, metropolitan area networks, telephone networks, and the like. The network 130 may include a plurality of network access points, such as wired or wireless access points, e.g., wired access points, wireless access points, base stations, internet switching points, etc. Through these access points, a data source may access the network 130 and send data information through the network 130. In some embodiments, the network 130 may be used for communication of the image processing system 120, receiving information internal or external to the image processing system 120, and sending information to other parts internal or external to the image processing system 120.
It should be noted that the image processing system 120 may actually exist in the imaging system 110, or perform corresponding functions through a cloud computing platform. The cloud computing platform can comprise a storage type cloud platform mainly used for storing data, a computing type cloud platform mainly used for processing data and a comprehensive cloud computing platform considering data storage and processing. The cloud platform used by the imaging system 110 may be a public cloud, a private cloud, a community cloud, a hybrid cloud, or the like. For example, some image information and/or data information output by the imaging system 110 may be calculated and/or stored by the user cloud platform according to actual needs. Other image information and/or data information may be calculated and/or stored by the local image processing system 120.
FIG. 2 is a schematic diagram of an imaging system 110 shown in accordance with some embodiments of the invention. In this embodiment, the imaging system 110 is an electronic computed tomography system (CT system). The imaging system 110 includes a scanning module 201. The scan module 201 is capable of performing a scan of a subject and obtaining data. It should be noted that the scan module 201 described below is merely provided as an example and is not intended to limit the scope of the present invention. For example, the scanning module 201 of the present invention may be a radiation scanning module or a magnetic scanning module. The radiation used by the radiation scanning module includes particle rays, photon rays, or the like, or any combination thereof. The particle rays may include neutrons, atoms, electrons, μ -mesons, heavy ions, or the like, or any combination thereof. The photon beam may include radiation, gamma radiation, alpha radiation, beta radiation, ultraviolet radiation, laser light, or the like, or any combination thereof.
In this embodiment, the scanning module 201 of the imaging system 110 may include a gantry 210 and a couch 250. Wherein the couch 250 is adapted to carry a subject. The couch 250 is movable so that a portion to be scanned of the subject is moved to a position suitable for detection.
In some embodiments, the gantry 210 can include a rotatable portion 220 that rotates about the axis of the scan module 201. The spatial structure of the rotatable part 220 may be one or a combination of a plurality of cylinders, ellipsoids, cuboids, etc. In some embodiments, the rotatable portion 220 may include a source of radiation 230, a detector 240, and a scanning volume 270. The radiation source 230 may be configured or used to emit radiation to a portion of a subject to be scanned to generate scan data for a medical image. The portion of the subject to be scanned may comprise a substance, tissue, organ, sample, body, or the like, or any combination thereof. In certain embodiments, the portion of the subject to be scanned may comprise the subject or a portion thereof, i.e., may comprise the head, chest, lung, pleura, mediastinum, abdomen, large intestine, small intestine, bladder, gall bladder, pelvic cavity, diaphysis, end, skeleton, blood vessels, or the like, or any combination thereof. The radiation source 230 is configured or operable to generate radiation or other types of radiation. The radiation is capable of passing through a portion of a subject to be scanned. After passing through the portion of the subject to be scanned, it is received by the detector 240. The radiation source 230 may include a radiation generator, a high voltage generator, or other accessories. The ray generator may comprise one or more ray tubes. The tube may emit radiation (or referred to as a radiation beam) through the tube. The radiation source 230 may be a cold cathode ion tube, a high vacuum hot cathode tube, a rotating anode tube, or the like. The shape of the emitted radiation beam may be linear, narrow pencil, narrow fan, cone, wedge, or the like, or irregular, or any combination thereof. The fan angle of the radiation beam may be a certain value in the range of 0-360. The tube in source 230 may be fixed in one position. In some cases, the tube may be translated or rotated.
The detector 240 may be configured to receive radiation from the radiation source 230 or other radiation source. Radiation from the radiation source 230 may pass through the object under examination and then to the detector 240. After receiving the radiation, the detector 240 produces detection results of the radiographic image of the inspection object. The term "detection results" may refer to data detected by detector 240 that may be used to construct a radiographic image. The detector 240 may be configured to receive radiation and generate scan data for a radiographic image of an object under examination. The detector 240 includes a radiation detector or other components. The shape of the radiation detector may be flat, arcuate, circular, or the like, or any combination thereof. The sector angle of the arcuate detector may range from 0 to 360. The fan angle may be fixed or adjustable from case to case, including desired image resolution, image size, detector sensitivity, detector stability, or the like, or any combination thereof. In some embodiments, a pixel of the detector may be the number of minimum detection cells, such as the number of detector cells (e.g., scintillator or photosensor, etc.). The pixels of the detector may be arranged in a single row, two rows, or another number of rows. The radiation detector is one-dimensional, two-dimensional, or three-dimensional.
The rotatable portion 220 of the gantry 210 can rotate about an axis 260 of the scan module 201. The radiation source 230 and the radiation detector 240 are rotatable with the rotatable portion 220 about an axis 260.
In conducting an examination, an object (e.g., a patient, a phantom, etc.) may be placed on the couch 250. The couch 250 may be pushed into the scanning chamber 270 in the Z-axis direction. While rotating about the axis 260, the radiation source 230 and the radiation detector 240 may acquire scan data of the subject. The scan data may be used to reconstruct, for example, an image to be corrected, a reference image of the image to be corrected, and the like.
In some embodiments, the scanning module 201 may perform a helical scan. In helical scanning, the object to be scanned may move back and forth along the axis 260 while the X-ray source may rotate about the axis 260. The radiation source 230 may produce a helical trajectory with respect to the object.
Those skilled in the art will appreciate that various modifications and improvements may be made to the disclosure herein. For example, the different system components described above are implemented by hardware devices, but may also be implemented by software solutions only. For example: the system is installed on an existing server. Further, the location information disclosed herein may be provided via a firmware, firmware/software combination, firmware/hardware combination, or hardware/firmware/software combination.
The medical image generation method and the medical image processing system 120 described in the embodiment of the present invention may be implemented in the working environment 100 shown in fig. 1 and the imaging system 110 shown in fig. 2.
Fig. 3 is a block diagram of a medical image processing system 120 according to an embodiment of the present invention. Referring to fig. 3, the medical image processing system 120 comprises an image acquisition device 310 and an image generation device 320.
The image acquisition device 310 functions to generate at least one tomographic image from scan data obtained by the imaging system 200. Specifically, the imaging system 200 controls the scanning module 201 to scan. The scanning module 201 continuously or intermittently transmits the scan data to the image acquisition device 310. After obtaining the scan data, the image acquisition device 310 can reconstruct the scan data to generate one or more tomographic images. Generally, tomographic images reflect "sectional views" of the subject at various locations.
The image generating device 320 includes a data receiving port 321, an operator 322, a memory 323, and a user interface 324.
The data receiving port 321 receives the scan data transmitted from the image acquisition device 310 and transmits the scan data to the arithmetic unit 322.
The operator 322 may be comprised of one or more processors that can execute program instructions to perform any of the functions of the image processing system 120 described herein. The arithmetic unit 322 performs arithmetic processing on the scan data to obtain image data required by the user.
The memory 323 is used for storing programs to be executed by the arithmetic unit 322, intermediate data during arithmetic operation, or final data after arithmetic operation is completed. The memory 323 may include various forms of program storage units and data storage units, such as a hard disk, a Read Only Memory (ROM), a Random Access Memory (RAM), and the like.
The user interface 324 is used for user interaction with the medical image processing system 120, and the user can input various control parameters to the medical image processing system 120 through the user interface 324, and the user interface 324 displays image data after being processed by the operator 322 in various ways.
It is understood that the medical image processing system 120 of the present invention can be implemented by one or more computers through hardware devices, software programs, firmware, and combinations thereof. Such a computer may be a general purpose computer or a computer having a specific purpose. The various components thereof may be connected by an internal communication bus. The medical image processing system 120 may also exchange information and data with the network 130 in a wireless manner.
Fig. 4 is a flowchart illustrating a method of generating a medical image according to an embodiment of the present invention. Referring to fig. 4, the method for generating a medical image includes the steps of:
in step 510, the medical image processing system 120 receives a user input of a desired layer thickness Texp and a desired layer distance Iexp by the user interface 324. The desired layer thickness Texp refers to a layer thickness of the reconstructed image desired by the user. The expected layer distance Iexp refers to the distance between the center points of two adjacent reconstructed images expected by a user. Taking spiral CT as an example, when volume sampling of spiral scanning is finished, a two-dimensional image can be reconstructed from any point on the Z-axis, and data can be used repeatedly. The reconstruction layer thickness is the width of the data used in the Z-axis direction when reconstructing the image.
In step 520, the data receiving port 321 receives scan data from the image acquisition device 310. In the present embodiment, the scan data is obtained by the scan module 201 of the imaging system 110.
In step 530, the arithmetic unit 322 performs arithmetic operation based on the scan data, and generates a first tomogram group N1 including a plurality of first tomograms. In this step, the first tomographic image generated by the operator 322 is associated with the preset layer thickness Tpre and the preset layer pitch Ipre. The preset layer thickness Tpre is smaller than the desired layer thickness Texp input by the user and the preset layer pitch Ipre is smaller than the desired layer pitch Iexp input by the user. The preset layer thickness Tpre and the preset layer distance Ipre may be preset in the medical image processing system 120, or may be determined according to a desired layer thickness Texp and a desired layer distance Iexp input by a user.
It should be noted that, although the generation method of the medical image according to the above embodiment is described in the above order, it is not intended to represent that the steps in the generation method of the medical image can be performed only in the above order. For example, although step 520 is arranged after step 510, step 520 may actually be performed prior to step 510, or may be performed simultaneously with step 510.
In one embodiment, the predetermined layer distance Ipre is equal to the predetermined layer thickness Tpre. At this time, it is equivalent to that there is no intersection between data used by the plurality of first tomographic images, and there is no duplicated data or vacant data between two of the plurality of first tomographic images, and all the scanning data is covered. Therefore, in the subsequent step, when the operator 322 generates the second tomogram group N2 using the first tomogram group N1, the data of the first tomogram group N1 is sufficient to support the operation in this generation step, regardless of the desired layer thickness Texp and the desired layer distance Iexp input by the user.
In one embodiment, the predetermined layer thickness Tpre and the predetermined layer distance Ipre are determined according to the desired layer thickness Texp and the desired layer distance Iexp. For example, the ratio of the preset layer thickness Tpre and the desired layer thickness Texp is set to a fixed value. Assuming that the operator 322 sets the ratio of the preset layer thickness Tpre to the desired layer thickness Texp to 4, when the desired layer thickness Texp input by the user is 12mm, the preset layer thickness Tpre is 3 mm.
The preset layer thickness Tpre and the preset layer distance Ipre may be set as desired, for example, may be set to correspond to or be larger than the cell size of the probe. For example, the preset layer thickness Tpre may be set to be smaller 1.5mm or 2mm, and may also be set to be larger 2.5mm or 3 mm. Similarly, the preset pitch Ipre may be set to be smaller 1.5mm or 2mm, and may also be set to be larger 2.5mm or 3 mm. The preset layer thickness Tpre and the preset layer distance Ipre are set in a certain range so as to obtain a first tomographic image with smaller layer thickness and layer distance and improve the imaging effect of a second tomographic image; while not significantly increasing the computational load of the medical image processing system 120.
In step 540, a second tomogram group N2 including at least one second tomogram associated with the desired layer thickness Texp and the desired layer distance Iexp is generated from the first tomogram group N1.
It is understood that, in the present embodiment, the second tomographic image to be generated corresponds to a spatial range S21, and the spatial range S21 represents a spatial range to be scanned by the imaging system 110 in order to generate the second tomographic image. Accordingly, the first tomographic image corresponds to a first spatial range S11. From step 530, the first tomographic image is associated with a preset layer thickness Tpre and a preset layer distance Ipre; as can be seen from step 540, the second tomographic image is associated with the desired layer thickness Texp and the desired layer distance Iexp. The preset layer thickness Tpre is smaller than the desired layer thickness Texp and the preset layer pitch Ipre is smaller than the desired layer pitch Iexp. Therefore, the first spatial range S11 to which the first tomographic image actually corresponds is smaller than the spatial range S21 to which the second tomographic image corresponds. The first spatial range S11 corresponding to the first tomographic image may fall entirely within the spatial range S21 corresponding to the second tomographic image, or may partially fall within the spatial range S21 corresponding to the second tomographic image.
Specifically, the method of generating the second tomogram group N2 in step 540 includes the steps of:
in step 541, a spatial range S21 corresponding to each second tomographic image to be generated is determined.
In step 542, at least a part of the first tomographic image falling within the spatial range S21 is determined.
In step 543, the proportion of the first tomographic image in the spatial range S21 corresponding to the second tomographic image to be generated to the first tomographic image is determined.
In step 544, a weight coefficient is determined for the first tomographic image based on the ratio. Generally speaking, the larger the proportion of the first tomographic image in the spatial range S21 corresponding to the second tomographic image to be generated is, the larger the weight coefficient is, and the smaller the proportion is, the smaller the weight coefficient is.
In step 545, the weight coefficient of each first tomographic image is normalized;
in step 546, the multiplication is then performed to obtain a valid first image. It is understood that the spatial range corresponding to the valid first image is completely within the spatial range S21 corresponding to the second tomographic image.
In step 547, the valid first images are superimposed and normalized to obtain corresponding second tomographic images.
In an embodiment, a step of performing a noise reduction process may be further included before the step 547.
Flow charts are used herein to illustrate operations performed by methods according to embodiments of the present application. It should be understood that the preceding operations are not necessarily performed in the exact order in which they are performed. Rather, various steps may be processed in reverse order or simultaneously. Meanwhile, other operations are added to or removed from these processes. For example, the spatial range S21 corresponding to each second tomographic image to be generated may be determined (i.e., step 541), and then the step of generating the first tomographic image group N1 including a plurality of first tomographic images (i.e., step 530) may be performed.
Fig. 5 is a schematic diagram of a method of generating the second tomogram group N2 in the first tomogram group N1 in one embodiment of the present invention. Referring to fig. 5, the first tomogram group N1 includes a plurality of first tomograms, and a first image N11 and a second image N12 are shown. Both the first image N11 and the second image N12 are associated with a preset layer thickness Tpre and a preset layer distance Ipre. Taking the first image N11 as an example, the image represented by the first image N11 corresponds to image data within the first spatial range S11 having the layer thickness Tpre as the preset layer thickness. In this embodiment, the preset layer distance Ipre is equal to the preset layer thickness Tpre, so there is no gap between the first image N11 and the second image N12.
The second tomographic image group N2 includes a plurality of second tomographic images, of which the first image N21 and the second image N22 are indicated. Taking the first image N21 as an example, the image represented by the first image N21 corresponds to image data within the spatial range S21 having the layer thickness of the desired layer thickness Texp. Since the desired layer thickness Texp is greater than the preset layer thickness Tpre, the spatial range S21 is also greater than the first spatial range S11. In this embodiment, the desired layer distance Iexp is larger than the desired layer thickness Texp, and therefore, the first image N21 and the second image N22 in the second tomographic image group N2 have a certain interval therebetween.
Since the preset layer thickness Tpre is smaller than the desired layer thickness Texp and the preset layer pitch Ipre is smaller than the desired layer pitch Iexp, the first tomographic image in the first tomographic image group N1 may fall in the spatial range S21 corresponding to the second tomographic image in whole or in part. As shown in fig. 5, the first image N11 in the first tomogram group N1 is all within the spatial range S21. The second image N12in the first tomogram group N1 is such that a portion N12in falls within the spatial range S21 and another portion N12out does not fall within the spatial range S21.
In this embodiment, the first image N21 in the second tomogram group N2 is calculated using the portion N12in in the first image N11 and the second image N12in the first tomogram group N1 which fall within the spatial range S21. The remaining images in the second tomogram group N2 are calculated in a similar manner.
Fig. 6 is a schematic diagram of a method of generating the second tomogram group N2 in the first tomogram group N1 in another embodiment of the present invention. Referring to fig. 6, this embodiment is different from the embodiment shown in fig. 5 in that both the first image N11 and the second image N12in the first tomogram group N1 fall within the spatial range S21 corresponding to the second tomogram.
In this embodiment, the preset layer thickness Tpre and the preset layer pitch Ipre are determined according to the desired layer thickness Texp and the desired layer pitch Iexp. For example, the ratio of the preset layer thickness Tpre and the desired layer thickness Texp is an integer, and the preset layer thickness Tpre and the preset layer distance Ipre are adjusted according to the desired layer thickness Texp and the desired layer distance Iexp such that the first tomographic images in the first tomographic image group N1 are all located in the spatial range S21 to which the second tomographic image corresponds, and one edge of the first image N11 and the last image located in the first tomographic image group N1 corresponds to the edge of the spatial range S21 to which the second tomographic image corresponds.
In this embodiment, since the first tomographic image used for calculating the second tomographic image is an integer, in the process of generating the second tomographic image group N2, it is not necessary to perform the steps 543 and 544 in fig. 5. That is, the first image N11 and the second image N12in the first tomogram group N1 which fall within the spatial range S21 corresponding to the second tomogram have the same weight coefficient. Therefore, the calculation load of the calculator 322 can be reduced, and the calculation load of the medical image processing system 120 of the present invention can be reduced.
It is understood that in other embodiments, the desired layer distance Iexp may also be less than or equal to the desired layer thickness Texp. When the desired layer distance Iexp is equal to the desired layer thickness Texp, the second tomographic images in the second tomographic image group N2 are also adjacent two by two like the first tomographic images in the first tomographic image group N1 shown in fig. 5 and 6, and do not overlap with each other. When the desired layer distance Iexp is smaller than the desired layer thickness Texp, the second tomographic images in the second tomographic image group N2 partially overlap, and the width of the overlap depends on the setting of the desired layer distance Iexp.
The medical image generation method and the medical image processing system 120 of the present invention have a small difference in the range of influence of the first tomographic image group N1 on the detector 240 because the first tomographic image group N1 having a small layer thickness and layer distance is generated using the scan data in advance. By generating the second tomographic image group N2 having a large desired layer thickness Texp and a desired layer distance Iexp using the first tomographic image group N1, the problem of uneven artifacts due to a large layer thickness can be solved.
Although the present invention has been disclosed in terms of the preferred embodiment, it is not intended to limit the invention, and variations and modifications may be made by one skilled in the art without departing from the spirit and scope of the invention. Therefore, any modification, equivalent change and modification of the above embodiments according to the technical essence of the present invention are within the protection scope defined by the claims of the present invention, unless the technical essence of the present invention departs from the content of the present invention.
Claims (6)
1. A method of generating a medical image, comprising:
receiving a desired layer thickness and a desired layer spacing;
receiving scanning data;
generating a first tomographic image group including a plurality of first tomographic images according to the scanning data, wherein the first tomographic images are associated with a preset layer thickness and a preset layer distance, the preset layer thickness is smaller than the expected layer thickness, and the preset layer distance is smaller than the expected layer distance;
generating a second tomogram group including at least one second tomogram in the first tomogram group, the second tomogram being associated with the desired layer thickness and the desired layer distance;
wherein generating the second tomogram group includes:
determining a spatial range corresponding to each second tomographic image to be generated;
generating a corresponding second tomographic image from at least a part of the first tomographic image falling within the corresponding spatial range;
determining the proportion of the part of the first tomographic image in the space range to the first tomographic image;
determining a weight coefficient for the first tomographic image according to the proportion;
and generating the corresponding second tomographic image according to the first tomographic image and the weight coefficient.
2. A method for generating a medical image according to claim 1, characterized in that the preset layer distance is equal to the preset layer thickness.
3. A method for generating a medical image as claimed in claim 1, characterized in that the preset layer thickness and the preset layer distance are determined from the desired layer thickness and the desired layer distance.
4. The method according to claim 1, wherein generating the corresponding second tomographic image from the first tomographic image and the weight coefficient includes:
normalizing the weight coefficient of the first tomographic image including the spatial range and then multiplying the normalized weight coefficient by the corresponding first tomographic image to obtain a valid first image;
and superposing the effective first images to obtain the corresponding second tomographic images.
5. The method according to claim 1, wherein only the first tomogram at least a part of which falls within the spatial range is generated when the first tomogram group is generated.
6. A medical image processing system includes a plurality of image processing units,
a data receiving port configured to receive scan data;
a user interface configured to receive a desired layer thickness and a desired layer spacing and to display a second set of tomograms associated with the desired layer thickness and the desired layer spacing;
an arithmetic unit configured to generate a first tomogram group including a plurality of first tomograms from the scan data, and generate the second tomogram group from the first tomogram group, the first tomograms being associated with a preset layer thickness and a preset layer distance, the preset layer thickness being smaller than the desired layer thickness, the preset layer distance being smaller than the desired layer distance;
the operator is configured to:
determining a spatial range corresponding to each second tomogram in the second tomogram group;
determining the proportion of the part of each first tomographic image falling in the space range in the first tomographic image;
determining a weight coefficient for the first tomographic image according to the proportion;
normalizing a weight coefficient of the first tomographic image including the spatial range;
multiplying the first tomographic image including the spatial range by the respective normalized weight coefficients to obtain a valid first image;
and superposing the effective first images to obtain the corresponding second tomographic images.
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