CN109001660B - Film imaging method and magnetic resonance imaging system - Google Patents
Film imaging method and magnetic resonance imaging system Download PDFInfo
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- CN109001660B CN109001660B CN201810601448.7A CN201810601448A CN109001660B CN 109001660 B CN109001660 B CN 109001660B CN 201810601448 A CN201810601448 A CN 201810601448A CN 109001660 B CN109001660 B CN 109001660B
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- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2576/00—Medical imaging apparatus involving image processing or analysis
- A61B2576/02—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part
- A61B2576/023—Medical imaging apparatus involving image processing or analysis specially adapted for a particular organ or body part for the heart
Abstract
The embodiment of the invention provides a film imaging method and a magnetic resonance imaging system. The method comprises the steps of radially acquiring magnetic resonance scanning data of a heart, recording heartbeat signals corresponding to the data, distributing the data to corresponding phase phases based on the number of specified phase phases and the heartbeat signals, and filling specified angle intervals in a phase k space of each phase by using specified magnetic resonance scanning data in adjacent phase phases of the phase; when the specified conditions are met, acquiring the data filled with the phase in the period as data to be reconstructed; the phase-to-phase reconstruction method comprises the steps of carrying out image reconstruction according to data to be reconstructed to obtain a reconstructed image of the phase, and filling a larger angle interval in a phase k space by using data of adjacent phases of the phase, so that the angle direction distribution of the phase k space tends to be uniform, radial artifacts in the reconstructed image are weakened, the image quality is improved, and the problem of low image quality in the prior art during cardiac cine imaging is solved to a certain extent.
Description
[ technical field ] A method for producing a semiconductor device
The scheme relates to the technical field of magnetic resonance imaging, in particular to a film imaging method and a magnetic resonance imaging system.
[ background of the invention ]
Compared with a traditional cartesian acquisition mode, a radial Resonance Imaging (MRI) acquisition technology has the advantages of better insensitivity to motion and the like. When the angle of two adjacent radial sampling increases by the golden angle (111.25 degrees), the golden angle is radially sampled. The golden angle radial sampling has a very special mathematical property that when any piece of data is intercepted in a continuous acquisition, the trajectory of the golden angle radial sampling in k space forms a relatively uniform distribution in the angular direction. Due to this advantage of golden angle radial sampling, it is possible to allow any time resolution to be chosen for reconstruction, rather than the number of good phases at the start of the sequence as is required in conventional techniques.
However, when radial acquisition techniques are used for cardiac signal triggered, retrospective cardiac cine imaging, the continuously acquired radial data may be distributed into different phases based on the cardiac electrical signal. In this case, the data of the same phase comes from some set of separate segments in the continuous acquired data, rather than a continuous segment, which results in an extremely uneven distribution of the angular directions of k-space, resulting in "clustering" of radial data in the angular directions. This "clustering" results in severe radial artifacts in the reconstructed image, thus reducing image quality.
[ summary of the invention ]
In view of this, the present disclosure provides a cine imaging method and a magnetic resonance imaging system, so as to solve the problems of severe radial artifacts and low image quality in cardiac cine imaging in the prior art.
In a first aspect, an embodiment of the present invention provides a movie imaging method, where the method includes:
radially acquiring magnetic resonance scanning data of a heart, and recording heartbeat signals corresponding to the magnetic resonance scanning data;
assigning the magnetic resonance scan data to corresponding phases based on a specified number of phases and the heartbeat signals;
for each phase, filling a specified angular interval in the phase k-space with specified magnetic resonance scan data in a phase adjacent to the phase; when the specified conditions are met, acquiring the data filled with the phase in the period as data to be reconstructed; and carrying out image reconstruction according to the data to be reconstructed to obtain a reconstructed image of the phase.
The above-described aspects and any possible implementations further provide an implementation in which assigning the magnetic resonance scan data to corresponding phases based on a specified number of phases and the heartbeat signals includes:
determining each heartbeat cycle corresponding to the magnetic resonance scanning data according to the heartbeat signal;
equally dividing each heartbeat cycle in each heartbeat cycle into a period phase with a specified period phase number;
for each phase, extracting data of the phase at the acquisition time from the magnetic resonance scanning data as first distribution data corresponding to the phase.
The above-described aspects and any possible implementations further provide an implementation in which assigning the magnetic resonance scan data to corresponding phases based on a specified number of phases and the heartbeat signals includes:
determining each heartbeat cycle corresponding to the magnetic resonance scanning data according to the heartbeat signal;
normalizing each heartbeat cycle of the respective heartbeat cycles to a standard cycle;
normalizing the acquisition time of the magnetic resonance scanning data to the standard period to obtain normalized acquisition time;
equally dividing the standard period into a specified number of period phases;
for each phase, extracting data of the phase with the normalized acquisition time from the magnetic resonance scanning data as first distribution data corresponding to the phase.
The above-described aspects and any possible implementations further provide an implementation in which a specified angular interval in k-space of a phase is filled with specified magnetic resonance scan data in phases adjacent to the phase, including:
searching an angle interval larger than an angle interval threshold value in the phase k space in the period as a designated angle interval;
searching data matched with the specified angle interval from second distribution data corresponding to the adjacent period of the period as filling data;
filling the specified angular interval with the padding data.
The foregoing aspect and any possible implementation manner further provide an implementation manner, where searching for data matching the specified angle interval from second allocation data corresponding to a neighboring period of the period as padding data includes:
acquiring a data line corresponding to the second distribution data as a preselected data line;
searching data lines with angles within the specified angle interval from the preselected data lines to serve as matched data lines, wherein the data on the matched data lines are the data matched with the specified angle interval;
and acquiring data on the matched data line as filling data.
The above-described aspect and any possible implementation manner further provide an implementation manner, where the specified condition is: all angle intervals in the phase k-space of the phase are smaller than an angle interval threshold; alternatively, the first and second electrodes may be,
the specified conditions are as follows: in the second allocation data corresponding to the period adjacent to the period, there is no data matching the specified angle interval.
The above-described aspect and any possible implementation further provide an implementation in which the angular interval threshold is equal to a product of an average angular interval of all angular intervals in the phase k-space of the phase multiplied by a specified multiple.
The above-described aspect and any possible implementation manner further provide an implementation manner, before acquiring the data after the phase filling in the period as the data to be reconstructed when a specified condition is met, the method further includes:
and judging whether the specified conditions are met.
The above-described aspects and any possible implementations further provide an implementation in which the magnetic resonance scan data is assigned to a corresponding phase before the magnetic resonance scan data is assigned to the corresponding phase based on a specified number of phases and the heartbeat signal, the method further comprising:
according to the heartbeat signal, searching a heartbeat cycle out of the range of the heartbeat cycle as a heartbeat cycle to be deleted;
deleting the data corresponding to the heartbeat cycle to be deleted from the magnetic resonance scanning data to obtain qualified magnetic resonance scanning data;
assigning the magnetic resonance scan data to corresponding phases based on a specified number of phases and the heartbeat signals, including: assigning the qualified magnetic resonance scan data to a corresponding phase based on a specified number of phases and the heartbeat signal.
The above-described aspects and any possible implementations further provide an implementation of radially acquiring magnetic resonance scan data of a heart, comprising: the golden angle radially acquires magnetic resonance scan data of the heart.
In a second aspect, an embodiment of the present invention provides a magnetic resonance imaging system, which includes a processor and a memory; the memory is for storing instructions that, when executed by the processor, cause the system to implement the method of any of the first aspects.
The embodiment of the invention has the following beneficial effects:
according to the embodiment of the invention, the magnetic resonance scanning data of the heart is radially acquired, the heartbeat signals corresponding to the magnetic resonance scanning data are recorded, the magnetic resonance scanning data are distributed to corresponding phase phases based on the number of specified phase phases and the heartbeat signals, and for each phase, the specified magnetic resonance scanning data in the adjacent phase phases of the phase are used for filling the specified angle interval in the k space of the phase; when the specified conditions are met, acquiring the data filled with the phase in the period as data to be reconstructed; and carrying out image reconstruction according to data to be reconstructed to obtain a reconstructed image of the phase, and filling a larger angle interval in the phase k space by using data of adjacent phases of the phase, so that the angular direction distribution of the phase k space tends to be uniform, thereby weakening the radial artifact in the reconstructed image and improving the image quality.
[ description of the drawings ]
In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the drawings needed to be used in the embodiments will be briefly described below, and it is obvious that the drawings in the following description are only some embodiments of the present invention, and it is obvious for those skilled in the art to obtain other drawings based on these drawings without creative efforts.
Fig. 1 is a diagram illustrating a first flow of a movie imaging method according to an embodiment of the present invention.
Fig. 2 is a diagram illustrating a heartbeat signal according to an embodiment of the present invention.
Fig. 3 is a diagram illustrating a second flow of a movie imaging method according to an embodiment of the present invention.
Fig. 4 is a diagram illustrating a comparison between a short axis image of the heart obtained by a cine imaging method according to an embodiment of the present invention and a short axis image of the heart obtained according to the prior art.
Fig. 5 is a comparison example of cardiac images obtained by the cine imaging method according to an embodiment of the present invention when arrhythmia data is removed and cardiac images obtained according to the prior art when arrhythmia data is removed.
[ detailed description ] embodiments
For better understanding of the technical solutions of the present invention, the following detailed descriptions of the embodiments of the present invention are provided with reference to the accompanying drawings.
It should be understood that the described embodiments are only some embodiments of the invention, and not all embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
The terminology used in the embodiments of the invention is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. As used in the examples of the present invention and the appended claims, the singular forms "a," "an," and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise.
It should be understood that the term "and/or" as used herein is merely one type of association that describes an associated object, meaning that three relationships may exist, e.g., a and/or B may mean: a exists alone, A and B exist simultaneously, and B exists alone. In addition, the character "/" herein generally indicates that the former and latter related objects are in an "or" relationship.
The word "if" as used herein may be interpreted as "at … …" or "when … …" or "in response to a determination" or "in response to a detection", depending on the context. Similarly, the phrases "if determined" or "if detected (a stated condition or event)" may be interpreted as "when determined" or "in response to a determination" or "when detected (a stated condition or event)" or "in response to a detection (a stated condition or event)", depending on the context.
Example one
The embodiment of the invention provides a film imaging method which can be applied to a magnetic resonance scanning retrospective film imaging process of a heart.
Fig. 1 is a diagram illustrating a first flow of a movie imaging method according to an embodiment of the present invention. As shown in fig. 1, in this embodiment, the movie imaging method may include the following steps:
s101, radially acquiring magnetic resonance scanning data of a heart, and recording heartbeat signals corresponding to the magnetic resonance scanning data.
S102, distributing the magnetic resonance scanning data to corresponding phase phases based on the specified phase number and the heartbeat signals.
S103, for each phase, filling specified angle intervals in k space of the phase by using specified magnetic resonance scanning data in adjacent phases of the phase; when the specified conditions are met, acquiring the data filled with the phase in the period as data to be reconstructed; and carrying out image reconstruction according to the data to be reconstructed to obtain a reconstructed image of the phase.
According to the method, the magnetic resonance image corresponding to each phase heart can be obtained, and the heart images can be dynamically displayed according to the phase sequence.
Through step S103, after the data of the neighboring phase of the phase is used to fill the larger angle interval in the phase k space, the angular direction distribution of each phase k space tends to be uniform, so that the radial artifacts in the reconstructed image are reduced, and thus the image quality of the reconstructed image can be improved.
Wherein the magnetic resonance scan data is recorded by data lines of the magnetic resonance scan. Each data line has a time stamp (timestamp), and the time point displayed by the timestamp is the acquisition time of the data on the data line.
The heartbeat signal (i.e., an ECG (electrocardiogram) signal) may provide time information of each heartbeat cycle during the magnetic resonance scan, and may be used as reference information of acquisition time corresponding to the magnetic resonance scan data, so as to divide the magnetic resonance scan data into the heartbeat cycles according to the acquisition time, and further allocate the magnetic resonance scan data corresponding to the same heartbeat cycle into the heartbeat cycles.
Alternatively, a heart cycle refers to the process that the cardiovascular system undergoes from the start of one heart beat to the start of the next heart beat. Changes of ventricular pressure, ventricular volume, blood flow and valve activity in each phase of the cardiac cycle are centered on the diastole and systole of the ventricles, and the whole cardiac cycle can move according to 8 phases: isovolumetric contraction phase, rapid ejection phase, slowed ejection phase, pre-diastole phase, isovolumetric relaxation phase, rapid filling phase, slowed filling phase, and atrial contraction phase.
Fig. 2 is a diagram illustrating a heartbeat signal according to an embodiment of the present invention. Referring to fig. 2, the heartbeat signal may be obtained through an Electrocardiograph (ECG), the waveform of the heartbeat signal is periodic, the highest peak in the waveform is an R wave, and the waveform between two adjacent R waves corresponds to one heartbeat cycle/cardiac cycle.
In the actually acquired data, the time lengths of the respective heart cycles may not be uniform. For example, the first heartbeat cycle has a length of 873ms (milliseconds, the same applies below), and the second heartbeat cycle has a length of 771ms, … ….
After the time length of each heartbeat cycle is obtained through the heartbeat signals, the magnetic resonance scanning data of abnormal heartbeat cycles such as arrhythmia and the like can be removed according to the specified time length range of the normal heartbeat cycle. For example, a heartbeat cycle having a time length less than the minimum value of the time length range of the normal heartbeat cycle, or a heartbeat cycle having a time length greater than the maximum value of the time length range of the normal heartbeat cycle, etc.
Wherein the specified number of epochs can be selected or entered by the user.
In one exemplary implementation, assigning the magnetic resonance scan data to the corresponding phase based on the specified number of phases and the heartbeat signal may include: determining each heartbeat period corresponding to the magnetic resonance scanning data according to the heartbeat signals; averagely dividing each heartbeat cycle in each heartbeat cycle into a phase with a designated phase number; for each phase, data at the phase at the acquisition time is extracted from the magnetic resonance scan data as first assignment data corresponding to the phase.
For example. Assume that the first heartbeat cycle length, determined from the heartbeat signal, is 873ms and the second heartbeat cycle length is 771 ms. The time stamp of the first data line after the arrival of the electrocardiosignal R wave is 3ms, the time stamp of the second data line is 6ms, the time stamp of the third data line is 9ms and …, and the time stamp of the second ninety data line is 873 ms. At this time, a new R wave arrives, and thereafter, the time stamp of the first data line is 3ms, the time stamp of the second data line is 6ms, the time stamp of the third data line is 9ms, …, and the time stamp of the second seventy-five data line is 771 ms. At this time a new R-wave arrives, after which the first data line timestamp is 3ms, … ….
Assuming that the number of phases selected by the user is 20, each phase in the first heartbeat cycle has a length of 873ms/20 to 43.65ms, such that the first phase in the first heartbeat cycle corresponds to a time period of 0ms to 43.65ms, the second phase corresponds to a time period of 43.65ms to 87.3ms, … …, and the twenty phases correspond to a time period of 829.35ms to 873 ms. The timestamp of the first data line in the first heartbeat cycle is 3ms, and the 3ms is in the time period of 0ms to 43.65ms, so that the data of the first data line in the first heartbeat cycle belongs to the first phase of the first heartbeat cycle. The timestamp of the second data line in the first heartbeat cycle is 6ms, and 6ms is also in the time period of 0 ms-43.65 ms, so that the data of the second data line in the first heartbeat cycle belongs to the first phase of the first heartbeat cycle, … …, and so on, all the magnetic resonance scanning data can be distributed to each phase of each heartbeat cycle, and then the data of the same phase of each heartbeat cycle can be extracted, so that the first distribution data corresponding to each phase can be obtained.
In one exemplary implementation, assigning the magnetic resonance scan data to the corresponding phase based on the specified number of phases and the heartbeat signal may include: determining each heartbeat period corresponding to the magnetic resonance scanning data according to the heartbeat signals; normalizing each heartbeat cycle in each heartbeat cycle to a standard cycle; normalizing the acquisition time of the magnetic resonance scanning data to a standard period to obtain normalized acquisition time; averagely dividing the standard period into period phases with the designated period phase number; for each phase, data at the phase at the normalized acquisition time is extracted from the magnetic resonance scan data as first assignment data corresponding to the phase.
For example. Still, it is assumed that the length of the first heartbeat cycle determined from the heartbeat signal is 873ms, in the first heartbeat cycle, the timestamp of the first data line after the arrival of the R wave of the electrocardiographic signal is 3ms, the timestamp of the second data line is 6ms, the timestamp of the third data line is 9ms, …, and the timestamp of the second ninety data line is 873 ms. The first heartbeat cycle is normalized to the standard cycle, assuming a standard cycle of 1000 ms.
Firstly, a normalization coefficient of the first heartbeat cycle is calculated to be 1000ms/873ms, and the product of the normalization coefficient and the timestamp of each data line is the normalized acquisition time of the data on the data line. For example, the normalized acquisition time of data on the first data line in the first heartbeat cycle is 3 × 1000/873-3.43 ms, the normalized acquisition time of data on the second data line is 6 × 1000/873-6.87 ms, …, and the normalized acquisition time of data on the second ninety data line is 873 × 1000/873-1000 ms.
Assuming that the specified number of phase phases selected by the user is 20, the length of each phase is 1000ms/20 to 50 ms. That is, the first heartbeat cycle corresponds to 0ms to 50ms in the first period, 50ms to 100ms in the second period, … in the second period, and 950ms to 1000ms in the twentieth period.
For the data after the normalization of the first heartbeat cycle, the normalized acquisition time of the data on the first data line is 3.43ms, and the data is in the time period of 0 ms-50 ms, so the data belongs to the first phase. The normalized acquisition time of the data on the second data line is 6.87ms, and is also in the time period of 0ms to 50ms, and thus belongs to the first phase, … …, and so on, the normalized acquisition time line of the data on the second ninety data lines is 1000ms, and is in the time period of 950ms to 1000ms, and belongs to the twentieth phase.
And distributing the data of other heartbeat cycles to corresponding phases of the respective heartbeat cycles according to the processing mode of the data of the first heartbeat cycle. And then extracting the data of the same phase of each heartbeat cycle to obtain first distribution data corresponding to each phase.
In one exemplary implementation, filling a specified angular interval in the phase k-space with specified magnetic resonance scan data in phases adjacent to the phase may include: searching an angle interval larger than an angle interval threshold value in the phase k space in the period as a designated angle interval; searching data matched with the specified angle interval from second distribution data corresponding to the adjacent period of the period phase to serve as filling data; the specified angular interval is filled with padding data.
Wherein, the specified angle interval is filled with padding data, which refers to copying the padding data to the phase in which the specified angle interval is located.
Wherein the angular interval threshold may be equal to the product of the average angular interval of all angular intervals in the phase k-space of the phase multiplied by a specified multiple.
For example. Assuming that there are 300 data lines in the previous period, the average angular interval is 360/300 to 1.2 degrees. Assuming that the coefficient of the set threshold is 1.5, the angular interval threshold is 1.2 degrees by 1.5 degrees by 1.8 degrees. Then all angular intervals in phase k-space of more than 1.8 degrees are designated angular intervals.
In an exemplary implementation, searching for data matching the specified angle interval from the second allocation data corresponding to the adjacent period of the period as the padding data may include: acquiring a data line corresponding to the second distribution data as a preselected data line; searching data lines with angles within a specified angle interval from the preselected data lines to serve as matched data lines, wherein the data on the matched data lines are data matched with the specified angle interval; and acquiring data on the matched data line as filling data.
In one exemplary implementation, the specified conditions are: all angle intervals in the phase k-space of the phase are smaller than an angle interval threshold; alternatively, the specified conditions are: in the second allocation data corresponding to the period adjacent to the period, there is no data matching the specified angle interval.
Wherein the process of filling the specified angular intervals in the phase k-space with the specified magnetic resonance scan data in the phase's neighboring phases may be a process that is performed cyclically until a specified condition is met. That is, after filling a larger angle interval in the phase k-space with the specified magnetic resonance scan data in the phase adjacent to the phase, the angle interval threshold is changed (the angle interval threshold is decreased), whether or not there is a larger angle interval in the phase is re-detected, and if so, the filling of the larger angle interval in the phase k-space with the magnetic resonance scan data in the phase adjacent to the phase is continued until the specified condition is satisfied.
For example. When the previous period has 300 data lines, the average angle interval is 360 degrees/300 degrees to 1.2 degrees, and the angle interval threshold is 1.2 degrees to 1.5 degrees to 1.8 degrees. Then all angular intervals in phase k-space of more than 1.8 degrees are designated angular intervals. Assuming that there is an angle interval of 22 angles exceeding 1.8 degrees in the previous phase, it is necessary to traverse all data lines inside two adjacent phase to see whether the angles of the data lines can fall within the 22 angle intervals. Assuming that 20 angular intervals can be 'filled up' and 2 cannot, the data of the corresponding 20 data lines are copied to the current phase. For gaps that cannot be 'filled up', no action is done.
After filling, the current phase has 300+20 to 320 data lines, and the average angle interval is 360 degrees/320 to 1.125 degrees. The new angular interval threshold is 1.125 degrees 1.5 degrees 1.6875 degrees. Repeating the above steps, finding all the angular intervals exceeding 1.6875 degrees in the k-space angular distribution of the previous phase, filling the corresponding angular intervals exceeding 1.6875 degrees with data of data lines in two adjacent phases whose angles fall in the angular interval exceeding 1.6875 degrees, … …, after filling, recalculating the angular interval threshold and the value of the specified angular interval, and repeating the above steps until all the angular intervals are less than the angular interval threshold or all the angular intervals are no longer able to be 'filled up' (i.e. there is no data matching the specified angular interval in the second distribution data corresponding to the adjacent phase of the phase).
In an exemplary implementation, when a specified condition is satisfied, before the phase-filled data is acquired as the data to be reconstructed, the cine imaging method further includes: and judging whether the specified conditions are met.
In one exemplary implementation, radially acquiring magnetic resonance scan data of a heart may include: the golden angle radially acquires magnetic resonance scan data of the heart. And during the gold angle radial acquisition, the reconstruction of randomly selected time resolution is supported.
Fig. 3 is a diagram illustrating a second flow of a movie imaging method according to an embodiment of the present invention. As shown in fig. 3, in this embodiment, the movie imaging method may include the following steps:
s301, magnetic resonance scanning data of the heart are radially acquired, and heartbeat signals corresponding to the magnetic resonance scanning data are recorded.
S302, according to the heartbeat signal, searching a heartbeat cycle out of the range of the heartbeat cycle as a heartbeat cycle to be deleted.
And S303, deleting the data corresponding to the heartbeat cycle to be deleted from the magnetic resonance scanning data to obtain qualified magnetic resonance scanning data.
And S304, distributing qualified magnetic resonance scanning data to corresponding phases based on the specified phase number and the heartbeat signals.
S305, for each phase, filling a specified angle interval in k-space of the phase by using specified magnetic resonance scanning data in adjacent phases of the phase; when the specified conditions are met, acquiring the data filled with the phase in the period as data to be reconstructed; and carrying out image reconstruction according to the data to be reconstructed to obtain a reconstructed image of the phase. And displaying the reconstructed images of each phase according to the corresponding phase sequence to obtain the heart cine images.
In the reconstructed data of the embodiment shown in fig. 3, the radial artifacts are further reduced by the data (i.e., the data corresponding to the heart cycle to be deleted) from which the arrhythmia is removed, so that the image quality is further improved.
Fig. 4 is a diagram illustrating a comparison between a short axis image of the heart obtained by a cine imaging method according to an embodiment of the present invention and a short axis image of the heart obtained according to the prior art. In fig. 4, a and c are end-diastole cardiac images, b and d are end-systole cardiac images, a and b are obtained according to the prior art method, and c and d are obtained according to the cine imaging method provided by the embodiment of the present invention. As can be seen from fig. 4, due to the very uneven distribution of k-space, there are significant radial artifacts in a and b, while the radial artifacts in c and d are much reduced, and the image quality of c and d is significantly better than that of a and b.
Fig. 5 is a diagram illustrating a comparison between a reconstructed cardiac image obtained by removing arrhythmia data according to a cine imaging method provided by an embodiment of the present invention and a reconstructed cardiac image obtained by removing arrhythmia data according to the prior art. In fig. 5, the first row is a reconstructed cardiac image obtained according to the prior art when arrhythmia data is removed, and the data discarding degrees increase sequentially from left to right; second, according to the reconstructed cardiac images obtained by the cine imaging method provided by the embodiment of the present invention, the discarding degree of the cardiac arrhythmia data increases from left to right. The data discarding degrees of the upper and lower corresponding images in the first and second lines are the same. As can be seen from fig. 5, the images obtained according to the prior art show significant artifacts and severely deteriorate in image quality as the discarding degree of data increases, while the images obtained by the cine imaging method provided by the embodiment of the present invention are always better and can be used for diagnosis. The second row last graph shows better quality even when 10 heart beat cycles are discarded, which almost means that 59% of the data is discarded.
According to the film imaging method provided by the embodiment of the invention, through radially acquiring the magnetic resonance scanning data of the heart, recording the heartbeat signals corresponding to the magnetic resonance scanning data, distributing the magnetic resonance scanning data to the corresponding phase phases based on the number of the specified phase phases and the heartbeat signals, and for each phase, filling the specified angle interval in the k space of the phase by using the specified magnetic resonance scanning data in the adjacent phase phases of the phase; when the specified conditions are met, acquiring the data filled with the phase in the period as data to be reconstructed; and carrying out image reconstruction according to data to be reconstructed to obtain a reconstructed image of the phase, and filling a larger angle interval in the phase k space by using data of adjacent phases of the phase, so that the angular direction distribution of the phase k space tends to be uniform, thereby weakening the radial artifact in the reconstructed image and improving the image quality.
Example two
The embodiment of the invention provides a magnetic resonance imaging system, which comprises a processor and a memory; the memory is configured to store instructions that, when executed by the processor, cause the system to implement any of the method for cinema imaging according to one embodiment.
It can be clearly understood by those skilled in the art that, for convenience and brevity of description, the specific working processes of the system, the apparatus and the module described above may refer to the corresponding processes in the foregoing method embodiments, and are not described herein again.
In the embodiments provided in the present invention, it should be understood that the disclosed system, apparatus and method may be implemented in other ways. For example, the apparatus embodiments described above are merely illustrative of additional divisions, e.g., multiple modules or components may be combined or integrated into another system, or some features may be omitted, or not implemented. In addition, the shown or discussed mutual coupling or direct coupling or communication connection may be an indirect coupling or communication connection through some interfaces, devices or modules, and may be in an electrical, mechanical or other form.
The modules described as separate parts may or may not be physically separate, and parts displayed as modules may or may not be physical modules, may be located in one place, or may be distributed on a plurality of network units. Some or all of the modules may be selected according to actual needs to achieve the purpose of the solution of the present embodiment.
In addition, functional modules in the embodiments of the present invention may be integrated into one processing unit, or each module may exist alone physically, or two or more modules are integrated into one unit. The integrated unit can be realized in a form of hardware, or in a form of hardware plus a software functional unit.
The integrated unit implemented in the form of a software functional unit may be stored in a computer readable storage medium. The software functional unit is stored in a storage medium and includes several instructions for causing a computer device (which may be a personal computer, a server, or a network device) or a Processor (Processor) to execute some steps of the methods according to the embodiments of the present invention. And the aforementioned storage medium includes: various media capable of storing program codes, such as a usb disk, a removable hard disk, a Read-Only Memory (ROM), a Random Access Memory (RAM), a magnetic disk, or an optical disk.
The above description is only for the purpose of illustrating the preferred embodiments of the present invention and is not to be construed as limiting the invention, and any modifications, equivalents, improvements and the like made within the spirit and principle of the present invention should be included in the scope of the present invention.
Claims (10)
1. A method of motion picture imaging, the method comprising:
radially acquiring magnetic resonance scanning data of a heart, and recording heartbeat signals corresponding to the magnetic resonance scanning data;
assigning the magnetic resonance scan data to corresponding phases based on a specified number of phases and the heartbeat signals;
for each phase, filling a specified angular interval in the phase k-space with specified magnetic resonance scan data in a phase adjacent to the phase; when the specified conditions are met, acquiring the data filled with the phase in the period as data to be reconstructed;
and carrying out image reconstruction according to the data to be reconstructed to obtain a reconstructed image of the phase.
2. The method of claim 1, wherein assigning the magnetic resonance scan data to corresponding phases based on a specified number of phases and the heartbeat signals comprises:
determining each heartbeat cycle corresponding to the magnetic resonance scanning data according to the heartbeat signal;
equally dividing each heartbeat cycle in each heartbeat cycle into a period phase with a specified period phase number;
for each phase, extracting data of the phase at the acquisition time from the magnetic resonance scanning data as first distribution data corresponding to the phase.
3. The method of claim 1, wherein assigning the magnetic resonance scan data to corresponding phases based on a specified number of phases and the heartbeat signals comprises:
determining each heartbeat cycle corresponding to the magnetic resonance scanning data according to the heartbeat signal;
normalizing each heartbeat cycle of the respective heartbeat cycles to a standard cycle;
normalizing the acquisition time of the magnetic resonance scanning data to the standard period to obtain normalized acquisition time;
equally dividing the standard period into a specified number of period phases;
for each phase, extracting data of the phase with the normalized acquisition time from the magnetic resonance scanning data as first distribution data corresponding to the phase.
4. The method of claim 1, wherein filling specified angular intervals in phase k-space with specified magnetic resonance scan data in phases adjacent to the phase comprises:
searching an angle interval larger than an angle interval threshold value in the phase k space in the period as a designated angle interval;
searching data matched with the specified angle interval from second distribution data corresponding to the adjacent period of the period as filling data;
filling the specified angular interval with the padding data.
5. The method of claim 4, wherein searching for data matching the specified angle interval from the second allocation data corresponding to the period adjacent to the period as padding data comprises:
acquiring a data line corresponding to the second distribution data as a preselected data line;
searching data lines with angles within the specified angle interval from the preselected data lines to serve as matched data lines, wherein the data on the matched data lines are the data matched with the specified angle interval;
and acquiring data on the matched data line as filling data.
6. The method of claim 4,
the specified conditions are as follows: all angle intervals in the phase k-space of the phase are smaller than an angle interval threshold; alternatively, the first and second electrodes may be,
the specified conditions are as follows: in the second allocation data corresponding to the period adjacent to the period, there is no data matching the specified angle interval.
7. The method according to claim 1, wherein when a specified condition is satisfied, before the phase-filled data is acquired as the data to be reconstructed, the method further comprises:
and judging whether the specified conditions are met.
8. The method of claim 1, wherein prior to assigning the magnetic resonance scan data to the corresponding phase based on the specified number of phases and the heartbeat signal, the method further comprises:
according to the heartbeat signal, searching a heartbeat cycle out of the range of the heartbeat cycle as a heartbeat cycle to be deleted;
deleting the data corresponding to the heartbeat cycle to be deleted from the magnetic resonance scanning data to obtain qualified magnetic resonance scanning data;
assigning the magnetic resonance scan data to corresponding phases based on a specified number of phases and the heartbeat signals, including: assigning the qualified magnetic resonance scan data to a corresponding phase based on a specified number of phases and the heartbeat signal.
9. The method of claim 1, wherein radially acquiring magnetic resonance scan data of the heart comprises: the golden angle radially acquires magnetic resonance scan data of the heart.
10. A magnetic resonance imaging system, characterized in that the system comprises a processor and a memory; the memory is for storing instructions which, when executed by the processor, cause the system to implement the method of any of claims 1 to 9.
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