CN110859622B - Imaging method, imaging device and nuclear magnetic system - Google Patents
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Abstract
The application provides an imaging method, an imaging device and a nuclear magnetic system. The imaging method is applied to a nuclear magnetic system with an ADC image acquisition function, and comprises the following steps: the method comprises the steps of obtaining multiple layers of apparent diffusion coefficient ADC images of a scanned brain, determining at least one first communication area from infarct core candidate areas of each layer of ADC images, determining an area which is symmetrical to the first communication area in tissue in the ADC images as a second communication area, determining a target infarct core area and a target ischemia semi-dark zone from the first communication area and the second communication area according to first relative ADCs of pixel points in the first communication area and second relative ADCs of pixel points in the second communication area, and marking the target infarct core area and the target ischemia semi-dark zone in the ADC images.
Description
Technical Field
The present application relates to the field of medical imaging technologies, and in particular, to an imaging method, an imaging device, and a nuclear magnetic system.
Background
In magnetic resonance imaging, diffusion-weighted imaging (DWI) and apparent diffusion coefficient (apparent diffusion coefficients, ADC) imaging are imaging methods that can reflect the diffusion specificity of water molecules. In the acute phase of cerebral infarction, the blood diffusion movement is weakened due to arterial occlusion, the ADC image presents a remarkably low signal, and the intensity of the remarkably low signal of the ADC image gradually rises along with the development of the disease course.
In the related art, an ADC threshold is predetermined, and a region where the ADC of the pixel is smaller than the ADC threshold is determined as a lesion region. Based on different patients and different brain tissues of different brain positions of one patient, focus area detection is carried out on the brains of different patients by using the same ADC threshold value, focus detection is carried out on the brain tissues of different positions of one patient, and the detection result is inaccurate, so that the marking result of the focus area of the brain on the ADC image is inaccurate.
Disclosure of Invention
To overcome the problems in the related art, the present application provides an imaging method, apparatus, and nuclear magnetic system.
In a first aspect, an imaging method is provided, applied to a nuclear magnetic system with an ADC image acquisition function, the method comprising:
acquiring a multi-layer apparent diffusion coefficient ADC image of a scanned brain;
determining at least one first communication area from infarct core candidate areas of each layer of the ADC image, and determining an area which is tissue-symmetrical to the first communication area in the ADC image as a second communication area;
determining a target infarction core region and a target ischemic penumbra from the first communication region and the second communication region according to a first relative ADC of the pixel points in the first communication region and a second relative ADC of the pixel points in the second communication region;
Marking the target infarct core zone and the target ischemic penumbra in the ADC image;
the first relative ADC is a ratio between the ADC of the pixel point in the first communication area and the ADC average value of all the pixel points in the second communication area, and the second relative ADC is a ratio between the ADC of the pixel point in the second communication area and the ADC average value of all the pixel points in the first communication area.
In a second aspect, there is provided an imaging apparatus applied to a nuclear magnetic system having an ADC image acquisition function, the apparatus comprising:
an acquisition module configured to acquire a multi-layered apparent diffusion coefficient ADC image of the scanned brain;
a first determining module configured to determine at least one first communication area from among infarct core candidate areas of each layer of the ADC image, and determine an area of the ADC image that is tissue-symmetrical to the first communication area as a second communication area;
a second determining module configured to determine a target infarct core region and a target ischemic penumbra from the first communication region and the second communication region according to a first relative ADC of a pixel point in the first communication region and a second relative ADC of a pixel point in the second communication region;
A labeling module configured to label the target infarct core zone and the target ischemic penumbra in the ADC image;
the first relative ADC is a ratio between the ADC of the pixel point in the first communication area and the ADC average value of all the pixel points in the second communication area, and the second relative ADC is a ratio between the ADC of the pixel point in the second communication area and the ADC average value of all the pixel points in the first communication area.
In a third aspect, there is provided a nuclear magnetic system comprising: an internal bus, and a memory, a processor and an external interface connected through the internal bus; wherein,,
the external interface is used for acquiring a multi-layer apparent diffusion coefficient ADC image of the scanned brain;
the memory is used for storing machine-readable instructions corresponding to imaging;
the processor is configured to read the machine-readable instructions on the memory and execute the instructions to implement operations comprising:
determining at least one first communication area from infarct core candidate areas of each layer of the ADC image, and determining an area which is tissue-symmetrical to the first communication area in the ADC image as a second communication area;
Determining a target infarction core region and a target ischemic penumbra from the first communication region and the second communication region according to a first relative ADC of the pixel points in the first communication region and a second relative ADC of the pixel points in the second communication region;
marking the target infarct core zone and the target ischemic penumbra in the ADC image;
the first relative ADC is a ratio between the ADC of the pixel point in the first communication area and the ADC average value of all the pixel points in the second communication area, and the second relative ADC is a ratio between the ADC of the pixel point in the second communication area and the ADC average value of all the pixel points in the first communication area.
The technical scheme provided by the embodiment of the application can comprise the following beneficial effects:
in the embodiment of the application, based on the symmetry of brain tissues, the property difference of the symmetrical brain tissues is small, when no pathology occurs in the symmetrical brain tissues, the ADCs of the pixel points corresponding to the symmetrical brain tissues in the ADC image are the same, and when one brain tissue has a pathology and the other brain tissue does not have a pathology, the ADCs of the pixel points corresponding to the symmetrical brain tissues in the ADC image are different. Based on this, this application is according to the relative ADC of the pixel point in the first intercommunication district of tissue symmetry and the second intercommunication district, confirms brain focus district from first intercommunication district and the second intercommunication district, compares in the correlation technique and uses fixed ADC to confirm brain focus district from all brain tissue districts, and this application provides the method has the advantage that focus district testing result accuracy is high, can accurately mark brain focus district on the ADC image.
It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the application.
Drawings
The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments consistent with the application and together with the description, serve to explain the principles of the application.
FIG. 1 is a flow chart of an imaging method according to an exemplary embodiment of the present application;
fig. 2 is a flowchart of a second communication area determining method according to an exemplary embodiment of the present application;
FIG. 3 is a flow chart illustrating a method of determining an angle of deflection of an axis of symmetry according to an exemplary embodiment of the present application;
FIG. 4 is a schematic diagram of an imaging device according to an exemplary embodiment of the present application;
FIG. 5 is a schematic diagram of a nuclear magnetic system according to an exemplary embodiment of the present application.
Detailed Description
Reference will now be made in detail to exemplary embodiments, examples of which are illustrated in the accompanying drawings. When the following description refers to the accompanying drawings, the same numbers in different drawings refer to the same or similar elements, unless otherwise indicated. The implementations described in the following exemplary examples are not representative of all implementations consistent with the present application. Rather, they are merely examples of apparatus and methods consistent with some aspects of the present application as detailed in the accompanying claims.
The application provides an imaging method which is applied to a nuclear magnetic system, wherein the nuclear magnetic system has an ADC (analog to digital converter) (apparent diffusion coefficients) image acquisition function.
Embodiments of the present application will be described in detail below with reference to the accompanying drawings.
Fig. 1 is a flow chart of an imaging method according to an exemplary embodiment of the present application, which may include the steps of:
in step 101, a multi-layered ADC image of the scanned brain is acquired.
After the scanning is finished, an ADC image sequence of the brain to be scanned is obtained, and based on an image acquisition principle, the ADC image sequence comprises a plurality of layers of ADC images, and the ADC images are cross-sectional images of the brain to be scanned.
The brain tissue structures displayed by the ADC images of different layers are different, the brain tissue area in the ADC image collected at the top of the brain is smaller, the brain tissue area in the ADC image collected at the middle of the brain is larger, and the brain tissue area in the ADC image collected at the bottom of the brain is smaller.
In an alternative embodiment, after the scanned head is scanned, the nuclear magnetic system acquires an ADC image sequence of the scanned brain, screens out a plurality of layers of ADC images with the brain tissue area ratio larger than the duty ratio threshold value from the ADC image sequence, and uses the screened plurality of layers of ADC images to detect the focus area.
The brain tissue area ratio refers to the ratio of the brain tissue area to the ADC image area in the ADC image. The size of the duty cycle threshold may be set as desired or empirically.
In step 102, at least one first communication region is determined from the infarct core candidate region of each layer of ADC image, and a region of the ADC image that is tissue-symmetrical to each first communication region is determined as a second communication region.
After the nuclear magnetic system acquires the multi-layer ADC image of the scanned brain, the following operations are performed for each layer of ADC image.
Firstly, determining an infarct core candidate area from an ADC image, specifically, judging whether the ADC of each pixel point in the ADC image is smaller than an ADC threshold value, and determining the infarct core candidate area of which the ADC of the pixel point is smaller than the ADC threshold value from the ADC image. The ADC threshold may be sized as desired or empirically, for example, the ADC threshold is 620.
Next, generally, the infarct core candidate region includes discrete pixels, and the nuclear magnetic system needs to determine a first communication region composed of a plurality of pixels having a communication relationship from the infarct core candidate region.
The plurality of pixels having a connected relationship are disposed adjacently and do not include pixels in which the ADC is greater than or equal to the ADC threshold. The number of the first communication areas is one or more than two.
Again, after the first communication region is determined based on the symmetry of the brain tissue, a region of the ADC image that is tissue symmetric to the first communication region is determined as a second communication region.
The tissue symmetry described in this application is various, such as tissue complete symmetry, tissue partial symmetry, and needs to be determined according to the nature of the brain tissue and the specific determination method of the second communication region.
Fig. 2 is a flowchart of a second communication area determining method according to an exemplary embodiment of the present application, and referring to fig. 2, the second communication area may be determined by: in step 1021, performing binarization processing on the ADC image to obtain a brain tissue binarization image; in step 1022, determining a symmetry axis deflection angle set for the brain tissue binarized image, wherein the symmetry axis deflection angle is an included angle between the symmetry axis and an X axis in an image coordinate system; in step 1023, determining an axis of symmetry based on the image centroid of the brain tissue binarized image and the axis of symmetry deflection angle; in step 1024, a symmetrical second communication region is determined based on each first communication region and the symmetry axis.
Aiming at step 1021, in order to facilitate subsequent image processing, binarization processing is performed on each layer of ADC image to obtain a corresponding brain tissue binarization image. In the brain tissue binarized image, the pixel value corresponding to the brain tissue is 1, and the pixel value corresponding to the non-brain tissue is 0.
For step 1022, first, a rough deflection angle of the scanned brain with respect to the X-axis is calculated based on the deflection angles of the brain tissue regions in all brain tissue binarized images with respect to the X-axis in the image coordinate system; and secondly, adding the rough deflection angle and a preset angle, and subtracting the rough deflection angle and the preset angle to obtain a rotation angle interval of the brain binarized image. The rotation angle interval is set for all brain binarized images.
The brain tissue in the cross section brain image is in an elliptical structure, a nuclear magnetic system determines a minimum circumscribed rectangular area of the brain tissue in each layer of brain tissue binarization image, determines an included angle between the long side of the minimum circumscribed rectangle and an X axis in an image coordinate system, calculates an average value of included angles between the long side of the minimum circumscribed rectangle and the X axis in all brain tissue binarization images after the calculation of the included angle of all brain tissue binarization images is completed, and obtains a rough deflection angle of the scanned brain.
After the rough deflection angle is obtained, the rough deflection angle is added with a preset angle to obtain a deflection angle upper limit, the rough deflection angle is subtracted from the preset angle to obtain a deflection angle lower limit, and a rotation angle interval of the brain tissue binarization image is determined according to the deflection angle upper limit and the deflection angle lower limit. The magnitude of the preset angle may be set as desired or empirically, for example, the preset angle is 8-15, alternatively 10.
The rotation angle section may be determined by other means than the above, such as presetting a rotation angle section based on experience, or the like. However, the method for acquiring the focus region determines the rotation angle interval according to the brain structure of the current patient, accords with the actual condition of the patient, and ensures the accuracy of the focus region detection result.
Fig. 3 is a flowchart of a method for determining a deflection angle of a symmetry axis according to an exemplary embodiment of the present application, where after a rotation angle interval is determined by a nuclear magnetic system, a deflection angle of a symmetry axis corresponding to a binarized image of each layer of brain tissue may be determined by the method shown in fig. 3. The method shown in fig. 3 comprises the following steps: in step 1022-1, in a predetermined rotation angle interval, after each pair of brain tissue binarization images rotates by a predetermined angle, according to a predetermined vertical line in the rotated brain tissue binarization images, horizontally overturning the brain tissue binarization images to obtain mirror images of the brain tissue binarization images; in step 1022-2, calculating a F-norm of a difference between the brain tissue binarized image and the mirror image; in step 1022-3, a minimum F-norm is determined from the plurality of F-norms obtained after the plurality of rotations; in step 1022-4, the angle of deflection of the brain tissue region in the brain tissue binarized image with respect to the X-axis at the time of determining the minimum F-norm is determined as the axis of symmetry deflection angle.
For step 1022-1, for each layer of brain tissue binarization image, rotating the brain tissue binarization image, and after each rotation by a preset angle, horizontally overturning the brain tissue binarization image according to a preset vertical line in the rotated brain tissue binarization image to obtain a mirror image of the brain tissue binarization image. The mirror image is also a binarized image.
In the implementation, after each pair of brain tissue binarization images rotates by a preset angle, the rotated brain tissue binarization images can be translated, so that the image centroid of the rotated brain tissue binarization images coincides with the original point in an image coordinate system, and the translated brain tissue binarization images are horizontally turned according to the Y axis in the image coordinate system to obtain mirror images. In this processing mode, the preset vertical line is the Y axis.
Or, after each pair of brain tissue binarization images rotates by a preset angle, image translation is not performed, and a preset vertical line is directly determined from the brain tissue binarization images. The preset vertical line is typically a vertical line through or within the brain tissue.
The preset angle may be set as desired or empirically, for example, the preset rotation angle step is 0.25 °.
It should be noted that, in order to distinguish the two preset angles, the preset angle used in step 1022-1 and the preset angle used in the process of determining the rotation angle interval are different, and the preset angle used in step 1022-1 may be referred to as a first preset angle and the preset angle used in the process of determining the rotation angle interval may be referred to as a second preset angle.
For step 1022-2, the brain tissue binarized image and the mirror image are both binarized images, and an F-norm of a difference between pixel values of the brain tissue binarized image and pixel values of the mirror image is calculated.
For step 1022-3 and step 1022-4, a brain tissue binarized image is rotated multiple times, a minimum F-norm is determined from a plurality of F-norms obtained after the multiple rotations, a deflection angle of a brain tissue region in the brain tissue binarized image with respect to an X-axis is determined as θ when the minimum F-norm is determined, and the θ is determined as a symmetry axis deflection angle. The calculation formula of θ is as follows:
wherein B (theta) is a brain tissue binarization image under a theta rotation deflection angle; b (B) LR (θ) is a mirror image of B (θ).
From the above formula, it can be determined that
And the value of theta corresponding to the minimum time.
For step 1023, after determining the image centroid and the axis of symmetry deflection angle of the brain tissue binarized image, a straight line that intersects the image centroid and has the axis of symmetry deflection angle is determined, and the straight line is determined as the axis of symmetry.
For step 1024, an area symmetrical to the first communication area with respect to the symmetry axis is determined, and the area is determined as the second communication area. Or after determining the area symmetrical to the first communication area relative to the symmetry axis, expanding the area, removing the pixel points of which the ADC is larger than the preset ADC in the expanded area, and determining the area formed by a plurality of pixel points which are remained in the expanded area and have a communication relation as a second communication area.
And removing the pixel points of the ADC in the enlarged area, which are larger than the preset ADC, for example, removing the pixel points of the ADC in the enlarged area, which are larger than 750, so as to prevent the blood vessel or cerebrospinal fluid with higher ADC value from being used as a reference object.
Assuming that the symmetry axis is denoted as y=ax+b, where a is the slope of the symmetry axis, B is the intercept of the symmetry axis, the point set in the first communication region is denoted as R (x, y), then the point set in the region symmetrical to the first communication region with respect to the symmetry axis is denoted as
The expansion method of the region, the size of the region after expansion, and the like may be set as needed or empirically. For example, the expansion radius is determined as the square root of the area of the infarct core candidate region, and the region is expanded and enlarged according to the expansion radius. The expansion radius is understood to be the distance between the expanded region boundary and the unexpanded region boundary.
In step 103, a target infarct core region and a target ischemic penumbra are determined from the first and second connected regions according to the first relative ADC of the pixel point in the first connected region and the second relative ADC of the pixel point in the second connected region.
After the nuclear magnetic system determines a first communication area and a second communication area which are symmetrical, the first relative ADC and the second relative ADC are calculated, and a target infarction core area and a target ischemia semi-dark zone are determined from the first communication area and the second communication area according to the first relative ADC and the second relative ADC.
In the case where a plurality of first communication areas and a plurality of second communication areas are determined from the ADC image, for each first communication area and its symmetrical second communication area, the target infarct core area and the target ischemic penumbra may be determined in the following manner:
a first step of: calculating a first ADC average value of all pixel points in a first communication area;
and a second step of: calculating a first ratio of ADC to a first ADC mean value of each pixel point in the symmetrical second communication area;
and a third step of: determining an area formed by pixel points with a first ratio less than or equal to a as a first target infarction core area, and determining an area formed by pixel points with a first ratio belonging to (a, b) as a first target ischemia penumbra, wherein a is greater than zero and less than b;
Fourth step: calculating a second ADC average value of all pixel points in the second communication area;
fifth step: calculating a second ratio of ADC to a second ADC mean value of each pixel point in the first communication area;
sixth step: and determining an area formed by pixels with a second ratio less than or equal to a as a second target infarction core area, and determining an area formed by pixels with a second ratio belonging to (a, b) as a second target ischemia penumbra.
The sizes of a and b may be set as desired or empirically, for example, a ranging from 0.6 to 0.75 and b ranging from 0.15 to 0.25 as a difference from a. Alternatively, a is 0.65 and b is 0.85.
In step 104, the target infarct core zone and the target ischemic penumbra are marked in the ADC image.
The infarcted core area is an irreversible area of brain tissue necrosis caused by cerebral ischemia.
Ischemic penumbra is brain tissue surrounding the necrotic area following cerebral ischemia, whose blood flow perfusion level is lower than that which maintains normal brain function, but higher than that which causes changes in brain morphology.
For each layer of ADC, after the target infarction core area and the target ischemia penumbra are determined from the ADC image, the target infarction core area and the target ischemia penumbra are marked in the ADC image so that a doctor can check the focus area. In an implementation, contours of the target infarct core region and the target ischemic penumbra may be marked in the ADC image.
According to the embodiment of the application, based on the symmetry of brain tissues, the property difference of the symmetrical brain tissues is small, when no pathology occurs in the symmetrical brain tissues, the ADC of the pixel points corresponding to the symmetrical brain tissues in the ADC image is the same, and when one brain tissue is diseased and the other brain tissue is not diseased, the ADC of the pixel points corresponding to the symmetrical brain tissues in the ADC image is different. Based on this, this application is according to the relative ADC of the pixel point in the first intercommunication district of tissue symmetry and the second intercommunication district, confirms brain focus district from first intercommunication district and the second intercommunication district, compares in the correlation technique and uses fixed ADC to confirm brain focus district from all brain tissue districts, and this application provides the method has the advantage that focus district testing result accuracy is high, can accurately mark brain focus district on the ADC image of brain.
Corresponding to the imaging method, the application also provides an imaging device and an embodiment of the nuclear magnetic system.
Referring to fig. 4, a schematic diagram of an imaging apparatus according to an exemplary embodiment of the present application is applied to a nuclear magnetic system having an ADC image acquisition function, the apparatus includes: an acquisition module 21, a first determination module 22, a second determination module 23 and a marking module 24; wherein,,
The acquisition module 21 is configured to acquire a multi-layer apparent diffusion coefficient ADC image of the scanned brain;
the first determining module 22 is configured to determine at least one first communication area from the infarct core candidate areas of each layer of the ADC image, and determine an area of the ADC image that is tissue-symmetrical to the first communication area as a second communication area;
the second determining module 23 is configured to determine a target infarct core area and a target ischemic penumbra from the first communication area and the second communication area according to the first relative ADC of the pixel points in the first communication area and the second relative ADC of the pixel points in the second communication area;
the labeling module 24 is configured to label the target infarct core zone and the target ischemic penumbra in the ADC image;
the first relative ADC is a ratio between the ADC of the pixel point in the first communication area and the ADC average value of all the pixel points in the second communication area, and the second relative ADC is a ratio between the ADC of the pixel point in the second communication area and the ADC average value of all the pixel points in the first communication area.
In an alternative embodiment, on the basis of the imaging apparatus shown in fig. 4, the first determining module may include: the system comprises a binarization processing sub-module, a first determination sub-module, a second determination sub-module and a third determination sub-module; wherein,,
the binarization processing submodule is configured to perform binarization processing on the ADC image to obtain a brain tissue binarization image;
the first determining submodule is configured to determine a symmetry axis deflection angle set for the brain tissue binarized image, wherein the symmetry axis deflection angle is an included angle between a symmetry axis and an X axis in an image coordinate system;
the second determination submodule is configured to determine the symmetry axis based on an image centroid of the brain tissue binarized image and the symmetry axis deflection angle;
the third determination submodule is configured to determine the second communication region of symmetry based on each of the first communication region and the symmetry axis.
In an alternative embodiment, the first determining sub-module may include: the device comprises a turnover unit, a calculation unit, a first determination unit and a second determination unit; wherein,,
the overturning unit is configured to horizontally overturn the brain tissue binarization image according to a preset vertical line in the rotated brain tissue binarization image after each pair of brain tissue binarization images rotates by a first preset angle in a preset rotation angle interval to obtain a mirror image of the brain tissue binarization image;
The calculating unit is configured to calculate an F-norm of a difference between the brain tissue binarized image and the mirror image;
the first determining unit is configured to determine a minimum F norm from a plurality of F norms obtained after a plurality of rotations;
the second determining unit is configured to determine a deflection angle of a brain tissue region in the brain tissue binarized image with respect to the X-axis when determining the minimum F-norm as the symmetry axis deflection angle.
In an alternative embodiment, the flipping unit may include: a translation subunit and a flip subunit; wherein,,
a translation subunit configured to translate the rotated brain tissue binarized image such that the image centroid coincides with an original point in the image coordinate system;
and the overturning subunit is configured to horizontally overturn the translated brain tissue binarization image according to a Y axis in the image coordinate system to obtain the mirror image.
In an alternative embodiment, the nuclear magnetic system further comprises: a calculation module and an obtaining module; wherein,,
the computing module is configured to compute a rough deflection angle of the scanned brain relative to the X axis based on the deflection angles of brain tissue areas relative to the X axis in all brain tissue binarized images;
The obtaining module is configured to add the rough deflection angle and a second preset angle, and subtract the rough deflection angle and the second preset angle, so as to obtain the rotation angle interval.
In an alternative embodiment, the computing module includes: the fourth determining sub-module, the fifth determining sub-module and the first calculating sub-module; wherein,,
the fourth determining submodule is configured to determine a minimum circumscribed rectangular area of brain tissue in each layer of the brain tissue binarized image;
the fifth determining submodule is configured to determine an included angle between the long side of each minimum circumscribed rectangle and the X axis;
and the first calculating submodule is configured to calculate the average value of the included angles between the long sides of all the minimum circumscribed rectangles and the X axis to obtain the rough deflection angle.
In an alternative embodiment, the third determining sub-module comprises: a third determination unit and a fourth determination unit; wherein,,
the third determination unit is configured to determine a region symmetrical to the first communication region with respect to the symmetry axis;
the fourth determination unit is configured to determine the area as the second communication area.
In an alternative embodiment, the third determining sub-module comprises: a third determination unit, an expansion unit, a removal unit, and a fifth determination unit; wherein,,
the third determination unit is configured to determine a region symmetrical to the first communication region with respect to the symmetry axis;
the enlarging unit is configured to enlarge the area;
the removing unit is configured to remove pixel points in the expanded area, wherein the ADC is larger than a preset ADC;
the fifth determination unit is configured to determine an area composed of a plurality of pixel points remaining in the enlarged area and having a communication relationship as the second communication area.
In an alternative embodiment, based on the imaging apparatus shown in fig. 4, the second determining module includes: the second computing sub-module, the third computing sub-module, the sixth determining sub-module, the fourth computing sub-module, the fifth computing sub-module and the seventh determining sub-module; wherein,,
the second computing submodule is configured to compute a first ADC average value of all pixel points in the first communication area;
the third calculating submodule is configured to calculate a first ratio of the ADC of each pixel point in the symmetrical second communication area to the first ADC average value;
The sixth determination submodule is configured to determine an area formed by pixels with the first ratio being less than or equal to a as a first target infarct core area, and determine an area formed by pixels with the first ratio belonging to (a, b) as a first target ischemic penumbra, wherein a is greater than zero and less than b;
the fourth computing submodule is configured to compute a second ADC average value of all pixel points in the second communication region;
the fifth calculating submodule is configured to calculate a second ratio of the ADC of each pixel point in the symmetrical first communication area to the second ADC average value;
the seventh determination submodule is configured to determine an area composed of pixels whose second ratio is smaller than or equal to the a as a second target infarct core area, and determine an area composed of pixels whose second ratio belongs to (a, b) as a second target ischemic penumbra.
In an alternative embodiment, based on the imaging apparatus shown in fig. 4, the first determining module 22 may include: an eighth determination submodule and a ninth determination submodule; wherein,,
the eighth determining submodule is configured to determine, from each layer of the ADC image, an infarct core candidate region in which the ADC of the pixel point is smaller than an ADC threshold;
The ninth determination submodule is configured to determine the first connected region composed of a plurality of pixels having a connected relationship from among the infarct core candidate regions.
In an alternative embodiment, on the basis of the imaging apparatus shown in fig. 4, the acquiring module 21 may include:
an acquisition module configured to acquire a sequence of ADC images of the scanned brain;
and the screening module is configured to screen the multi-layer ADC image with the brain tissue area ratio larger than a ratio threshold value from the ADC image sequence.
Referring to fig. 5, which is a schematic diagram of a nuclear magnetic system according to an exemplary embodiment of the present application, the apparatus may include: a memory 320, a processor 330, and an external interface 340 connected by an internal bus 310.
Wherein, external interface 340 is used for obtaining the multilayer apparent diffusion coefficient ADC image of the brain to be scanned;
a memory 320 for storing machine-readable instructions corresponding to imaging;
a processor 330 for reading the machine readable instructions on the memory 320 and executing the instructions to perform the following operations:
determining at least one first communication area from infarct core candidate areas of each layer of the ADC image, and determining an area which is tissue-symmetrical to the first communication area in the ADC image as a second communication area;
Determining a target infarction core region and a target ischemic penumbra from the first communication region and the second communication region according to a first relative ADC of the pixel points in the first communication region and a second relative ADC of the pixel points in the second communication region;
marking the target infarct core zone and the target ischemic penumbra in the ADC image;
the first relative ADC is a ratio between the ADC of the pixel point in the first communication area and the ADC average value of all the pixel points in the second communication area, and the second relative ADC is a ratio between the ADC of the pixel point in the second communication area and the ADC average value of all the pixel points in the first communication area.
In the disclosed embodiments, the computer-readable storage medium may take many forms, such as, in different examples, the machine-readable storage medium may be: RAM (Radom Access Memory, random access memory), volatile memory, non-volatile memory, flash memory, a storage drive (e.g., hard drive), a solid state drive, any type of storage disk (e.g., optical disk, dvd, etc.), or a similar storage medium, or a combination thereof. In particular, the computer readable medium may also be paper or other suitable medium capable of printing a program. Using these media, the programs may be electronically captured (e.g., optically scanned), compiled, interpreted, and otherwise processed in a suitable manner, and then stored in a computer medium.
The foregoing description of the preferred embodiments of the present invention is not intended to limit the invention to the precise form disclosed, and any modifications, equivalents, improvements and alternatives falling within the spirit and principles of the present invention are intended to be included within the scope of the present invention.
Claims (13)
1. An imaging method applied to a nuclear magnetic system having an ADC image acquisition function, the method comprising:
acquiring a multi-layer apparent diffusion coefficient ADC image of a scanned brain;
determining at least one first communication area from infarct core candidate areas of each layer of the ADC image, and determining an area which is tissue-symmetrical to the first communication area in the ADC image as a second communication area;
determining a target infarct core region and a target ischemic penumbra from the first communication region and the second communication region according to the first relative ADC of the pixel point in the first communication region and the second relative ADC of the pixel point in the second communication region, comprising: calculating a first ADC average value of all pixel points in the first communication area; calculating a first ratio of ADC to the first ADC mean value of each pixel point in the second communication area; determining a region formed by pixels with the first ratio less than or equal to a as a first target infarct core region, and determining a region formed by pixels with the first ratio belonging to (a, b) as a first target ischemic penumbra, wherein a is greater than zero and less than b;
Calculating a second ADC average value of all pixel points in the second communication area; calculating a second ratio of ADC to the second ADC mean value of each pixel point in the first communication area; determining a region formed by pixels with the second ratio less than or equal to the a as a second target infarct core region, and determining a region formed by pixels with the second ratio belonging to (a, b) as a second target ischemic penumbra;
marking the target infarct core zone and the target ischemic penumbra in the ADC image;
the first relative ADC is a ratio between the ADC of the pixel point in the first communication area and the ADC average value of all the pixel points in the second communication area, and the second relative ADC is a ratio between the ADC of the pixel point in the second communication area and the ADC average value of all the pixel points in the first communication area.
2. The method of claim 1, wherein determining a region of the ADC image that is tissue symmetric to the first communication region as a second communication region comprises:
performing binarization processing on the ADC image to obtain a brain tissue binarization image;
determining a symmetry axis deflection angle set for the brain tissue binarization image, wherein the symmetry axis deflection angle is an included angle between a symmetry axis and an X axis in an image coordinate system;
Determining the symmetry axis based on an image centroid of the brain tissue binarized image and the symmetry axis deflection angle;
the second communication region of symmetry is determined based on each of the first communication region and the symmetry axis.
3. The method of claim 2, wherein the determining the axis of symmetry deflection angle set for the brain tissue binarized image comprises:
in a predetermined rotation angle interval, after each pair of brain tissue binarization images rotates by a first preset angle, horizontally overturning the brain tissue binarization images according to a preset vertical line in the rotated brain tissue binarization images to obtain mirror images of the brain tissue binarization images;
calculating an F-norm of a difference between the brain tissue binarized image and the mirror image;
determining the minimum F norm from a plurality of F norms obtained after a plurality of times of rotation;
and determining the deflection angle of the brain tissue region in the brain tissue binarized image relative to the X axis when determining the minimum F norm as the deflection angle of the symmetrical axis.
4. The method according to claim 3, wherein after each pair of brain tissue binarization images rotates by a first preset angle within a predetermined rotation angle interval, the brain tissue binarization images are horizontally flipped according to a preset vertical line in the rotated brain tissue binarization images to obtain mirror images of the brain tissue binarization images, including:
Translating the rotated brain tissue binarization image to enable the centroid of the image to coincide with the original point in the image coordinate system;
and horizontally overturning the translated brain tissue binarization image according to a Y axis in the image coordinate system to obtain the mirror image.
5. A method according to claim 3, characterized in that the rotation angle interval is determined by:
calculating a rough deflection angle of the scanned brain relative to the X axis based on the deflection angles of brain tissue regions relative to the X axis in all brain tissue binarized images;
and adding the rough deflection angle and a second preset angle, and subtracting the rough deflection angle and the second preset angle to obtain the rotation angle interval.
6. The method of claim 5, wherein calculating a coarse angle of deflection of the scanned brain relative to the X-axis based on the angles of deflection of brain tissue regions relative to the X-axis in all brain tissue binarized images comprises:
determining the minimum circumscribed rectangular area of brain tissue in each layer of brain tissue binarization image;
determining an included angle between the long side of each minimum circumscribed rectangle and the X axis;
And calculating the average value of the included angles between the long sides of all the minimum circumscribed rectangles and the X axis to obtain the rough deflection angle.
7. The method of claim 2, wherein said determining the symmetric second communication region based on each of the first communication region and the symmetry axis comprises:
determining a region symmetrical to the first communication region with respect to the symmetry axis;
determining the region as the second communication region; or,
enlarging the region;
removing pixel points in the expanded area, wherein the ADC is larger than a preset ADC;
and determining an area formed by a plurality of pixel points which are remained in the enlarged area and have a communication relationship as the second communication area.
8. The method of claim 1, wherein the determining at least one first communication region from infarct core candidate regions of each layer of the ADC image comprises:
determining an infarct core candidate area of which the ADC of the pixel point is smaller than an ADC threshold value from each layer of the ADC image;
and determining the first communication area formed by a plurality of pixel points with communication relation from the infarct core candidate area.
9. The method of claim 1, wherein the acquiring a multi-layer ADC image of the scanned brain comprises:
acquiring an ADC image sequence of the scanned brain;
and screening the multi-layer ADC images with the brain tissue area ratio larger than a ratio threshold value from the ADC image sequence.
10. An imaging apparatus for use in a nuclear magnetic system having an ADC image acquisition function, the apparatus comprising:
an acquisition module configured to acquire a multi-layered apparent diffusion coefficient ADC image of the scanned brain;
a first determining module configured to determine at least one first communication area from among infarct core candidate areas of each layer of the ADC image, and determine an area of the ADC image that is tissue-symmetrical to the first communication area as a second communication area;
a second determining module configured to determine a target infarct core region and a target ischemic penumbra from the first communication region and the second communication region according to a first relative ADC of a pixel point in the first communication region and a second relative ADC of a pixel point in the second communication region;
a labeling module configured to label the target infarct core zone and the target ischemic penumbra in the ADC image;
The first relative ADC is a ratio between the ADC of the pixel point in the first communication area and the ADC average value of all the pixel points in the second communication area, and the second relative ADC is a ratio between the ADC of the pixel point in the second communication area and the ADC average value of all the pixel points in the first communication area;
the second determining module includes: the second computing sub-module, the third computing sub-module, the sixth determining sub-module, the fourth computing sub-module, the fifth computing sub-module and the seventh determining sub-module; wherein,,
the second computing submodule is configured to compute a first ADC average value of all pixel points in the first communication area;
the third calculating submodule is configured to calculate a first ratio of the ADC of each pixel point in the symmetrical second communication area to the first ADC average value;
the sixth determination submodule is configured to determine an area formed by pixels with the first ratio being less than or equal to a as a first target infarct core area, and determine an area formed by pixels with the first ratio belonging to (a, b) as a first target ischemic penumbra, wherein a is greater than zero and less than b;
The fourth computing submodule is configured to compute a second ADC average value of all pixel points in the second communication region;
the fifth calculating submodule is configured to calculate a second ratio of the ADC of each pixel point in the symmetrical first communication area to the second ADC average value;
the seventh determination submodule is configured to determine an area composed of pixels whose second ratio is smaller than or equal to the a as a second target infarct core area, and determine an area composed of pixels whose second ratio belongs to (a, b) as a second target ischemic penumbra.
11. The apparatus of claim 10, wherein the first determining module comprises:
the binarization processing sub-module is configured to perform binarization processing on the ADC image to obtain a brain tissue binarization image;
a first determination submodule configured to determine an axis of symmetry deflection angle set for the brain tissue binarized image, the axis of symmetry deflection angle being an angle between an axis of symmetry and an X-axis in an image coordinate system;
a second determination submodule configured to determine the symmetry axis based on an image centroid of the brain tissue binarized image and the symmetry axis deflection angle;
A third determination sub-module configured to determine the second communication area of symmetry based on each of the first communication area and the symmetry axis.
12. The apparatus of claim 11, wherein the first determination submodule comprises:
the overturning unit is configured to horizontally overturn the brain tissue binarization image according to a preset vertical line in the rotated brain tissue binarization image after each pair of brain tissue binarization images rotates by a first preset angle in a preset rotation angle interval to obtain a mirror image of the brain tissue binarization image;
a calculation unit configured to calculate an F-norm of a difference between the brain tissue binarized image and the mirror image;
a first determining unit configured to determine a minimum F-norm from a plurality of F-norms obtained after a plurality of rotations;
a second determination unit configured to determine a deflection angle of a brain tissue region in the brain tissue binarized image with respect to the X-axis when determining the minimum F-norm as the symmetry axis deflection angle.
13. A nuclear magnetic system, comprising: an internal bus, and a memory, a processor and an external interface connected through the internal bus; wherein,,
The external interface is used for acquiring a multi-layer apparent diffusion coefficient ADC image of the scanned brain;
the memory is used for storing machine-readable instructions corresponding to imaging;
the processor is configured to read the machine-readable instructions on the memory and execute the instructions to implement operations comprising:
determining at least one first communication area from infarct core candidate areas of each layer of the ADC image, and determining an area which is tissue-symmetrical to the first communication area in the ADC image as a second communication area;
determining a target infarct core region and a target ischemic penumbra from the first communication region and the second communication region according to the first relative ADC of the pixel point in the first communication region and the second relative ADC of the pixel point in the second communication region, comprising: calculating a first ADC average value of all pixel points in the first communication area; calculating a first ratio of ADC to the first ADC mean value of each pixel point in the second communication area; determining a region formed by pixels with the first ratio less than or equal to a as a first target infarct core region, and determining a region formed by pixels with the first ratio belonging to (a, b) as a first target ischemic penumbra, wherein a is greater than zero and less than b;
Calculating a second ADC average value of all pixel points in the second communication area; calculating a second ratio of ADC to the second ADC mean value of each pixel point in the first communication area; determining a region formed by pixels with the second ratio less than or equal to the a as a second target infarct core region, and determining a region formed by pixels with the second ratio belonging to (a, b) as a second target ischemic penumbra;
marking the target infarct core zone and the target ischemic penumbra in the ADC image;
the first relative ADC is a ratio between the ADC of the pixel point in the first communication area and the ADC average value of all the pixel points in the second communication area, and the second relative ADC is a ratio between the ADC of the pixel point in the second communication area and the ADC average value of all the pixel points in the first communication area.
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