CN113269845B - Image reconstruction method, device, storage medium and electronic equipment - Google Patents
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Abstract
The disclosure relates to an image reconstruction method, an image reconstruction device, a storage medium and electronic equipment, which aim at prospective triggering gating heart film imaging, reduce motion artifacts generated due to irregular cardiac cycles and improve image quality. The image reconstruction method comprises the following steps: after detecting an R wave peak of the electrocardiographic gating, scanning a scanning object according to a preset phase number, and collecting scanning data; when scanning data of a cardiac cycle are acquired, screening the scanning data according to the numerical relation between the actual interval time of an R wave crest in the cardiac cycle and the preset interval time to obtain target scanning data; and mapping the target scanning data corresponding to different dynamic periods to the same phase position to obtain reconstruction data. And reconstructing an image based on the reconstruction data.
Description
Technical Field
The present disclosure relates to the field of medical imaging technologies, and in particular, to an image reconstruction method, an image reconstruction device, a storage medium, and an electronic device.
Background
The heart film imaging technology can rapidly image the heart at different periods in one cardiac cycle, acquire a plurality of images, and play the images of the heart in the systolic period and the diastolic period in the form of films. Specifically, the cardiac cine imaging technology adopts segmented imaging, mainly scans through a two-dimensional balanced steady-state free precession sequence or a rapid field echo, and reduces the interference of heart pulsation and respiratory motion by matching with electrocardiographic gating and respiration in the scanning process.
The electrocardiographic gating technique mainly comprises a prospective electrocardiographic gating technique and a retrospective electrocardiographic gating technique. For forward-looking type electrocardiographic gating cardiac film imaging, after detecting the peak of an electrocardiographic signal R wave, segment data are acquired, the acquisition of the segment data is stopped at the beginning of the next systole, the segment data are acquired after a new R wave peak, and so on. And during reconstruction, filling K space with the data of different sectional scans, and obtaining heart images of different phases through space Fourier transformation. However, if the heart rate of the scanned object is uneven, the relative phase positions of the data of different segments acquired by the segment scanning are inconsistent, and the direct filling of the K space may cause motion artifacts to the image.
Disclosure of Invention
The disclosure aims to provide an image reconstruction method, an image reconstruction device, a storage medium and electronic equipment, so as to reduce motion artifacts generated due to irregular cardiac cycles and improve image quality for prospective-type trigger-gated cardiac film imaging.
To achieve the above object, in a first aspect, the present disclosure provides an image reconstruction method, the method comprising:
after detecting an R wave peak of the electrocardiographic gating, scanning a scanning object according to a preset phase number, and collecting scanning data;
when scanning data of a cardiac cycle are acquired, screening the scanning data according to the numerical relation between the actual interval time of an R wave crest in the cardiac cycle and the preset interval time to obtain target scanning data;
mapping the target scanning data corresponding to different dynamic periods to the same phase position to obtain reconstruction data;
and reconstructing an image based on the reconstruction data.
Optionally, the preset interval time is determined according to an interval time of R-wave peaks in an average cardiac cycle of the scan subject.
Optionally, each time scan data of one cardiac cycle is acquired, the scan data of the cardiac cycle is screened according to a numerical relation between an actual interval time of an R peak in the cardiac cycle and a preset interval time, including:
whenever scan data for one cardiac cycle is acquired, the following screening operation is performed:
if the interval time of the R wave crest in the scanning data is larger than or equal to the first preset interval time and smaller than or equal to the second preset interval time, reserving the scanning data;
if the interval time of the R wave crest in the scanning data is smaller than the first preset interval time or larger than the second preset interval time, discarding the scanning data and re-collecting the scanning data;
wherein the first preset interval time is less than the second preset interval time.
Optionally, the filtering the scan data in the cardiac cycle according to the numerical relation between the actual interval time of the R peak in the cardiac cycle and the preset interval time to obtain target scan data includes:
determining whether a phase number of the scan data in the cardiac cycle reaches the preset phase number;
and if the phase number of the scanning data in the cardiac cycle reaches the preset phase number, screening the scanning data in the cardiac cycle according to the numerical relation between the actual interval time of the R wave crest and the preset interval time to obtain target scanning data.
Optionally, the method further comprises:
and if the phase number of the scanning data in the cardiac cycle reaches the preset phase number, screening the scanning data in the cardiac cycle according to the numerical relation between the interval time of the R wave crest and the preset interval time after the scanning data acquisition of all cardiac cycles is completed, and obtaining target scanning data.
Optionally, the mapping the target scan data corresponding to different cardiac cycles to the same phase position includes:
for each target scan data corresponding to different cardiac cycles, determining whether a phase position of the target scan data in the corresponding cardiac cycle is the same as a target phase position, wherein the target phase position is determined according to a phase position of scan data acquired in an average cardiac cycle of the scan object;
and if the phase position corresponding to the target scanning data is different from the target phase position, performing time sequence interpolation on the target scanning data.
Optionally, before acquiring the scan data, the method further comprises:
and after detecting the R wave peak of the electrocardio gating, performing null scanning through pulse or radio frequency so as to enable the acquisition of the scanning data to be in a steady state.
In a second aspect, the present disclosure provides an image reconstruction apparatus, the apparatus comprising:
the acquisition module is used for scanning the scanning object according to the preset phase number after detecting the R wave crest of the electrocardiographic gate control, and acquiring scanning data;
the screening module is used for screening the scanning data according to the numerical relation between the actual interval time of the R wave crest in the cardiac cycle and the preset interval time when the scanning data of one cardiac cycle are acquired, so as to obtain target scanning data;
the mapping module is used for mapping the target scanning data corresponding to different dynamic periods to the same phase position to obtain reconstruction data;
and the reconstruction module is used for reconstructing an image based on the reconstruction data.
In a third aspect, the present disclosure provides a computer readable storage medium having stored thereon a computer program which when executed by a processor performs the steps of the method of any of the first aspects.
In a fourth aspect, the present disclosure provides an electronic device comprising:
a memory having a computer program stored thereon;
a processor for executing the computer program in the memory to implement the steps of the method of any of the first aspects.
By the technical scheme, the image reconstruction can be carried out after the target scanning data corresponding to different dynamic periods are mapped to the same phase position. Therefore, the images of each phase can be ensured to be aligned to the uniform cardiac cycle interval, the motion artifact generated by irregular cardiac cycle is reduced, and the image quality is improved. Moreover, the target scanning data are obtained by screening according to the interval time of the R wave crest in each cardiac cycle, and the phase-in-phase mapping aims at the scanning data in a proper proportion range, so that the problem of low phase-in-phase mapping accuracy caused by too high or too low heart rate can be effectively avoided, and the image quality is further improved.
Additional features and advantages of the present disclosure will be set forth in the detailed description which follows.
Drawings
The accompanying drawings are included to provide a further understanding of the disclosure, and are incorporated in and constitute a part of this specification, illustrate the disclosure and together with the description serve to explain, but do not limit the disclosure. In the drawings:
FIG. 1 is a scanning schematic of a prospective electrocardiographic gating;
FIG. 2 is a scanning schematic of retrospective electrocardiographic gating;
FIG. 3 is a flowchart illustrating a method of image reconstruction according to an exemplary embodiment of the present disclosure;
FIG. 4 is a schematic diagram illustrating screening of scan data in an image reconstruction method according to an exemplary embodiment of the present disclosure;
FIG. 5 is a schematic diagram illustrating time-series interpolation in an image reconstruction method according to an exemplary embodiment of the present disclosure;
FIG. 6 is a block diagram of an image reconstruction apparatus according to an exemplary embodiment of the present disclosure;
fig. 7 is a block diagram of an electronic device, according to an exemplary embodiment of the present disclosure.
Detailed Description
Specific embodiments of the present disclosure are described in detail below with reference to the accompanying drawings. It should be understood that the detailed description and specific examples, while indicating and illustrating the disclosure, are not intended to limit the disclosure.
Magnetic resonance imaging (Magnetic Resonance Imaging, MRI) has become an important imaging modality in the medical imaging arts by virtue of its non-radiation, good soft tissue contrast, and arbitrary slice imaging characteristics. The cardiac magnetic resonance imaging technique (Cardiac Cine Imaging, which is abbreviated as cardiac cine imaging hereinafter) can rapidly image hearts in different periods in a cardiac cycle, acquire a plurality of images, and play images in systole and diastole of the hearts in a cine mode.
Specifically, the cardiac cine imaging technology adopts segmented imaging, mainly scans through a two-dimensional balanced steady-state free precession (balanced Steady State Free Precession, bSSFP) sequence or a Fast Field Echo (FFE), and reduces interference of heart pulsation and respiratory motion by matching with electro-cardiac gating (ECG) and respiration in the scanning process, so that not only can the motion functions of heart chambers and heart chamber walls be evaluated, but also the valve morphology and functions of the heart can be evaluated.
The electrocardiographic gating technique mainly includes a prospective electrocardiographic gating (pro-elective gating) technique and a retrospective electrocardiographic gating (retroelective gating) technique.
For forward-looking electrocardiographic gated cardiac cine imaging, after detecting the peak of the electrocardiographic signal R wave, the scan sequence is triggered to start, after which the radio frequency pulse excitation and segmented data acquisition is started until the next systole. Referring to fig. 1, a prospective electrocardiographic gate acquires a plurality of segmented data (segmented data represented by a plurality of squares, such as A1 and A2, in fig. 1) after an R-peak, stops the acquisition of segmented data the next time before systole, acquires segmented data again after a new R-peak, and so on. And during reconstruction, filling K space with the data of different sectional scans, and obtaining heart images of different phases through space Fourier transformation. However, if the heart rate of the scanned object is uneven, the relative phase positions of the data of different segments acquired by the segment scanning are inconsistent, and the direct filling of the K space may cause motion artifacts to the image.
Referring to fig. 2, the retrospective electrocardiograph gating technology performs radio frequency pulse excitation and signal acquisition in the whole cardiac cycle, and after the acquisition process is terminated, the electrocardiograph gating signal is utilized to retrospectively and synchronously reconstruct a heart film image, so that motion artifacts of the heart can be reduced. However, because of the continuous acquisition, the scanning time is longer than the prospective electrocardiographic gating, and the scanning efficiency is relatively low. Furthermore, since the electrocardiographic signal and the acquisition signal are not synchronous, the stability of retrospective electrocardiographic gating is generally poor, and the motion artifact of the image is more serious in the case of arrhythmia.
In view of this, the embodiments of the present disclosure provide a new image reconstruction method, apparatus, storage medium and electronic device, so as to reduce motion artifacts generated due to irregular cardiac cycle and improve image quality for prospective-type triggered gating cardiac cine imaging.
Fig. 3 is a flowchart illustrating an image reconstruction method according to an exemplary embodiment of the present disclosure. Referring to fig. 3, the image reconstruction method may be based on a look-ahead trigger gating, comprising:
And step 303, mapping the target scanning data corresponding to different cardiac cycles to the same phase position to obtain reconstruction data.
For example, the phase is used to represent the cardiac motion phase of each cardiac cycle, for example, the preset phase number is set to 11, and then the scan object is scanned according to the preset phase number, and 11 scan data corresponding to the cardiac motion phases can be acquired in each cardiac cycle. For example, referring to fig. 1, each cardiac cycle may include 11 phase scan data, where the phase positions corresponding to scan data arranged in the same position are the same, such as the same phase position corresponding to scan data A1 of the 1 st phase in the first cardiac cycle and scan data A2 of the 1 st phase in the second cardiac cycle, and so on.
It should be appreciated that since cardiac cine imaging employs segmented imaging, the scan data corresponding to each session may be referred to as segmented data, which is a fixed number of K-space lines. In the related art, the K-space line of each piece of segmented data is directly filled into the K space and then fourier transformed to obtain a reconstructed image. If the heart rate of the scanned object is not uniform, the phase position of the K-space line of each segmented data is different, which can lead to motion artifacts in the reconstructed image.
In the embodiment of the disclosure, the image reconstruction can be performed after the target scanning data in different dynamic periods are mapped to the same phase position. Therefore, the images of each phase can be ensured to be aligned to the uniform cardiac cycle interval, the motion artifact generated by irregular cardiac cycle is reduced, and the image quality is improved. Moreover, the target scanning data are obtained by screening according to the interval time of the R wave crest in each cardiac cycle, and the phase-in-phase mapping aims at the scanning data in a proper proportion range, so that the problem of low phase-in-phase mapping accuracy caused by too high or too low heart rate can be effectively avoided, and the image quality is further improved.
In a possible manner, each time scan data of one cardiac cycle is acquired, the scan data is screened according to a numerical relationship between an actual interval time of an R-peak in the cardiac cycle and a preset interval time, where the preset interval time may be determined according to an interval time of the R-peak in an average cardiac cycle of the scan subject. Therefore, a proper preset interval time can be set according to the average cardiac cycle, so that target scanning data in a proper proportion range are screened out, the accuracy of a time sequence interpolation result is improved, and the quality of a reconstructed image is further improved.
For example, the interval time of R wave peak in the average cardiac cycle of the scanned object is determined to be
Then the preset interval time may be set to +.>
(/>
Eighty percent) or can be set to +.>
(/>
One hundred twenty percent) or can be set to include +.>
And->
The embodiments of the present disclosure are not limited in this regard.
In a possible manner, the following screening operations may also be performed each time scan data for one cardiac cycle is acquired: if the interval time of the R wave crest in the scanning data is larger than or equal to the first preset interval time and smaller than or equal to the second preset interval time, the scanning data is reserved; if the interval time of the R wave crest in the scanning data is smaller than the first preset interval time or larger than the second preset interval time, discarding the scanning data and re-collecting the scanning data, wherein the first preset interval time is smaller than the second preset interval time.
For example, the first preset interval time is set to
The second preset interval time is set to +.>
In this case, referring to FIG. 4, if the interval (RR) of R-peaks in the scan data is greater than +.>
The scan data is discarded and the scan data is re-acquired. If the interval time (RR) of R peak in the scan data in another cardiac cycle is greater than +.>
And is less than->
The scan data is retained. If the interval time (RR) of R peak in scan data in another cardiac cycle is less than +.>
The scan data is discarded and the scan data is re-acquired. Therefore, the interval time range of the R wave crest in the target scanning data obtained by screening is as follows:
in practical applications, the acquisition of the scan data of the preset phase number may not be completed in one cardiac cycle, for example, refer to the last cardiac cycle shown in fig. 4, and the acquisition of the scan data of the preset phase number is not completed due to the too fast heart rate. In this case, in order to avoid the influence on the data acquisition and screening in the next cardiac cycle, the sequential scan may be regarded as a first priority, and the scan data in the cardiac cycle may be screened after the acquisition of all scan data is completed.
Specifically, in a possible manner, it may be determined whether the phase number of the scan data in the cardiac cycle reaches the preset phase number, and if the phase number of the scan data in the cardiac cycle reaches the preset phase number, the scan data in the cardiac cycle is screened according to the numerical relationship between the actual interval time of the R peak and the preset interval time, so as to obtain the target scan data.
In other possible modes, if the phase number of the scanning data in the cardiac cycle reaches the preset phase number, after the scanning data acquisition of all cardiac cycles is completed, the scanning data in the cardiac cycle is screened according to the numerical relation between the interval time of the R wave crest and the preset interval time, so as to obtain target scanning data.
By the method, the target scanning data can be obtained by screening according to the interval time of the R wave crest in each cardiac cycle, then the target scanning data is subjected to time sequence interpolation, the problem of low accuracy of time sequence interpolation caused by too high or too low heart rate can be avoided, and the image quality is improved. And by setting a scanning judgment strategy, the problem that the end diastole image is further lost due to incomplete end diastole data collection when the heart rate is too high can be avoided, and the image quality is further improved.
After screening to obtain target scan data, the target scan data corresponding to different cardiac cycles may be mapped to the same phase position, for example, the segmented K-space lines of different cardiac cycles are mapped to the average RR interval. It has been explained above that the relative phase positions in which the K-space lines of the respective phases are located at the time of the segmented scan are not identical, since the RR of each cardiac cycle is not identical. If the K-space lines corresponding to the different segment data are directly spliced, motion artifacts may be brought to the reconstructed image. Thus, in embodiments of the present disclosure, the interval time of the R-peak in the average cardiac cycle may be determined
For example, 80%, and then maps the acquired segmented scan data to the preset phase position by a linear or nonlinear interpolation method, thereby solving the problem of misalignment of phase positions of different segmented data. />
For example, referring to FIG. 5, the scan data is exactly aligned in the first cardiac cycle
Is the reference phase position. If the phase position of the scan data in the second cardiac cycle exceeds the reference phase position, the scan data may be interpolated, i.e., the phase position of the scan data is reduced, and the phase position of the scan data is aligned to the reference phase position. If the phase position of the scan data in the third cardiac cycle does not reach the reference phase position, the scan data may be extrapolated, i.e., the phase position of the scan data may be increased, to align the phase position of the scan data to the reference phase position.
For example, the interpolation method may employ a linear interpolation method such as a neighborhood interpolation method, a weight interpolation method, or the like. Furthermore, considering that in case of arrhythmia, the length of the systole usually remains unchanged, mainly the length of the diastole, the linear interpolation may not conform to the physiological facts, so that more complex nonlinear interpolation methods may be considered instead of the linear interpolation method. Also, the interpolation operation may involve interpolation and extrapolation, such as the latter two interpolation cases shown in FIG. 5. It should be appreciated that since the time-series interpolation is performed with respect to the screened target scan data, the interpolation is already eliminated
The data with larger phase difference is not large in proportion to interpolation and extrapolation, so that errors caused by interpolation can be reduced to a certain extent.
It should be appreciated that if the deadline data of the scan data is already the same as the target deadline phase, the scan data may not be time-sequentially interpolated in order to improve interpolation efficiency and thus image reconstruction efficiency. That is, in a possible manner, for each target scan data corresponding to different cardiac cycles, it may be determined whether the phase position of the target scan data in the corresponding cardiac cycle is the same as the target phase position, where the target phase position is determined according to the phase position of the scan data acquired in the average cardiac cycle of the scan object, and if the phase position corresponding to the target scan data is different from the target phase position, time-series interpolation is performed on the target scan data.
For example, the target phase position is determined based on the phase position of the scan data acquired in the 80% RR range of the scan subject, i.e., the phase position of the scan data acquired in the first cardiac cycle as shown in fig. 5. In this case, if the deadline position of the target scan data is the same as the target deadline position, no time-series interpolation is necessary. If the deadline position of the target scanning data is different from the target period phase position, time sequence interpolation is carried out so as to map the target scanning data to the target period phase position. Therefore, motion artifacts caused by arrhythmia can be reduced, the image quality can be improved, and the image reconstruction efficiency can be improved.
In a possible manner, the scan data acquisition may also be in a steady state by performing an empty scan with a pulse or radio frequency after detecting an electrocardiographically gated R-peak prior to acquiring the scan data. Therefore, the acquisition of the scanning data can be more in line with the actual heart motion condition of the scanning object, and the accuracy of the reconstructed image is improved.
By the method, the time sequence interpolation is carried out on the target scanning data corresponding to different cardiac cycles, and the target scanning data corresponding to different cardiac cycles can be mapped to the same phase position to obtain reconstruction data. The reconstructed data is a K-space line acquired under different segments, so that the reconstructed data is filled into K-space, and complete K-space data for image reconstruction can be obtained. Then, fourier transform is performed on the K-space data, and a heart movie image can be obtained.
It should be understood that any of the image reconstruction methods provided in the present disclosure may be compatible with other reconstruction techniques, for example, a navigator echo technique, parallel imaging, echo sharing, and other reconstruction techniques may be combined, so as to further improve the image reconstruction quality.
By means of any image reconstruction mode, aiming at forward-looking triggering gating cardiac film imaging, segmented scanning data (namely K space lines) can be interpolated to uniform and reasonable interval time of cardiac cycles in the time domain, images of phases in each period are ensured to be aligned to uniform cardiac cycle intervals, and motion artifacts generated due to irregular cardiac cycles are reduced, so that image quality is improved. In addition, data screening can be carried out according to the actual interval time of the R wave crest in each cardiac cycle before phase mapping, and the phase mapping is aimed at scanning data in a proper proportion range, so that the problem of low phase mapping accuracy caused by too high or too low heart rate can be effectively avoided, and the image quality is further improved.
Based on the same inventive concept, the embodiments of the present disclosure further provide an image reconstruction apparatus, where the image reconstruction apparatus may be part or all of an electronic device such as a magnetic resonance device by using software, hardware, or a combination of the two. Referring to fig. 6, the image reconstruction apparatus 600 may include:
the acquisition module 601 is configured to scan a scan object according to a preset phase number after detecting an R peak of an electrocardiographic gate, and acquire scan data;
the first screening module 602 is configured to screen, when scan data of one cardiac cycle is acquired, the scan data according to a numerical relation between an actual interval time of an R peak in the cardiac cycle and a preset interval time, so as to obtain target scan data;
the mapping module 603 is configured to map the target scan data corresponding to different dynamic periods to the same phase position, so as to obtain reconstructed data;
a reconstruction module 604, configured to reconstruct an image based on the reconstruction data.
Optionally, the preset interval time is determined according to an interval time of R-wave peaks in an average cardiac cycle of the scan subject.
Optionally, the first screening module 602 is configured to:
whenever scan data for one cardiac cycle is acquired, the following screening operation is performed:
when the interval time of the R wave crest in the scanning data is larger than or equal to the first preset interval time and smaller than or equal to the second preset interval time, reserving the scanning data;
discarding the scanning data and re-collecting the scanning data when the interval time of the R wave crest in the scanning data is smaller than the first preset interval time or larger than the second preset interval time;
wherein the first preset interval time is less than the second preset interval time.
Optionally, the first screening module 602 is configured to:
determining whether a phase number of the scan data in the cardiac cycle reaches the preset phase number;
and when the phase number of the scanning data in the cardiac cycle reaches the preset phase number, screening the scanning data in the cardiac cycle according to the numerical relation between the actual interval time of the R wave crest and the preset interval time to obtain target scanning data.
Optionally, the apparatus 600 further includes:
and the second screening module is used for screening the scanning data in the cardiac cycle according to the numerical relation between the interval time of the R wave crest and the preset interval time after the scanning data acquisition of all cardiac cycles is completed when the phase number of the scanning data in the cardiac cycle reaches the preset phase number, so as to obtain target scanning data.
Optionally, the mapping module 603 is configured to:
for each target scan data corresponding to different cardiac cycles, determining whether a phase position of the target scan data in the corresponding cardiac cycle is the same as a target phase position, wherein the target phase position is determined according to a phase position of scan data acquired in an average cardiac cycle of the scan object;
and when the phase position corresponding to the target scanning data is different from the target phase position, performing time sequence interpolation on the target scanning data.
Optionally, the apparatus 600 further includes:
and the empty scanning module is used for carrying out empty scanning through pulse or radio frequency after detecting the R wave crest of the electrocardio gate control before acquiring the scanning data so as to enable the acquisition of the scanning data to be in a steady state.
The specific manner in which the various modules perform the operations in the apparatus of the above embodiments have been described in detail in connection with the embodiments of the method, and will not be described in detail herein.
Based on the same inventive concept, the embodiments of the present disclosure further provide an electronic device, including:
a memory having a computer program stored thereon;
and a processor for executing the computer program in the memory to implement the steps of any of the image reconstruction methods described above.
In a possible manner, the block diagram of the electronic device may be as shown in fig. 7. Referring to fig. 7, the electronic device 700 may include: a processor 701, a memory 702. The electronic device 700 may also include one or more of a multimedia component 703, an input/output (I/O) interface 704, and a communication component 705.
Wherein the processor 701 is configured to control the overall operation of the electronic device 700 to perform all or part of the steps in the image reconstruction method described above. The memory 702 is used to store various types of data to support operation at the electronic device 700, which may include, for example, instructions for any application or method operating on the electronic device 700, as well as application-related data, such as acquired scan data, images reconstructed pictures, and so forth. The Memory 702 may be implemented by any type or combination of volatile or non-volatile Memory devices, such as static random access Memory (Static Random Access Memory, SRAM for short), electrically erasable programmable Read-Only Memory (Electrically Erasable Programmable Read-Only Memory, EEPROM for short), erasable programmable Read-Only Memory (Erasable Programmable Read-Only Memory, EPROM for short), programmable Read-Only Memory (Programmable Read-Only Memory, PROM for short), read-Only Memory (ROM for short), magnetic Memory, flash Memory, magnetic disk, or optical disk. The multimedia component 703 can include a screen and an audio component. Wherein the screen may be, for example, a touch screen, the audio component being for outputting and/or inputting audio signals. For example, the audio component may include a microphone for receiving external audio signals. The received audio signals may be further stored in the memory 702 or transmitted through the communication component 705. The audio assembly further comprises at least one speaker for outputting audio signals. The I/O interface 704 provides an interface between the processor 701 and other interface modules, which may be a keyboard, mouse, buttons, etc. These buttons may be virtual buttons or physical buttons. The communication component 705 is for wired or wireless communication between the electronic device 700 and other devices. Wireless communication, such as Wi-Fi, bluetooth, near field communication (Near Field Communication, NFC for short), 2G, 3G, 4G, NB-IOT, eMTC, or other 5G, etc., or one or a combination of more of them, is not limited herein. The corresponding communication component 705 may thus comprise: wi-Fi module, bluetooth module, NFC module, etc.
In an exemplary embodiment, the electronic device 700 may be implemented by one or more application specific integrated circuits (Application Specific Integrated Circuit, abbreviated ASIC), digital signal processor (Digital Signal Processor, abbreviated DSP), digital signal processing device (Digital Signal Processing Device, abbreviated DSPD), programmable logic device (Programmable Logic Device, abbreviated PLD), field programmable gate array (Field Programmable Gate Array, abbreviated FPGA), controller, microcontroller, microprocessor, or other electronic components for performing the image reconstruction method described above.
In another exemplary embodiment, a computer readable storage medium is also provided comprising program instructions which, when executed by a processor, implement the steps of the image reconstruction method described above. For example, the computer readable storage medium may be the memory 702 including program instructions described above, which are executable by the processor 701 of the electronic device 700 to perform the image reconstruction method described above.
In another exemplary embodiment, a computer program product is also provided, comprising a computer program executable by a programmable apparatus, the computer program having code portions for performing the above described image reconstruction method when executed by the programmable apparatus.
The preferred embodiments of the present disclosure have been described in detail above with reference to the accompanying drawings, but the present disclosure is not limited to the specific details of the above embodiments, and various simple modifications may be made to the technical solutions of the present disclosure within the scope of the technical concept of the present disclosure, and all the simple modifications belong to the protection scope of the present disclosure.
In addition, the specific features described in the foregoing embodiments may be combined in any suitable manner, and in order to avoid unnecessary repetition, the present disclosure does not further describe various possible combinations.
Moreover, any combination between the various embodiments of the present disclosure is possible as long as it does not depart from the spirit of the present disclosure, which should also be construed as the disclosure of the present disclosure.
Claims (9)
1. A method of image reconstruction, the method comprising:
after detecting an R wave peak of the electrocardiographic gating, scanning a scanning object according to a preset phase number, and collecting scanning data;
when scanning data of a cardiac cycle are acquired, screening the scanning data according to the numerical relation between the actual interval time of an R wave crest in the cardiac cycle and the preset interval time to obtain target scanning data;
if the phase position corresponding to the target scanning data is different from the target phase position, performing time sequence interpolation on the target scanning data to obtain reconstruction data, wherein the target phase position is determined according to the phase position of the scanning data acquired in the average cardiac cycle of the scanning object;
and reconstructing an image based on the reconstruction data.
2. The method of claim 1, wherein the preset interval is determined based on an interval of R-peaks in an average cardiac cycle of the scan subject.
3. The method according to claim 1, wherein each time scan data of a cardiac cycle is acquired, the scan data of the cardiac cycle is filtered according to a numerical relationship between an actual interval time of an R-wave peak and a preset interval time in the cardiac cycle, including:
whenever scan data for one cardiac cycle is acquired, the following screening operation is performed:
if the interval time of the R wave crest in the scanning data is larger than or equal to the first preset interval time and smaller than or equal to the second preset interval time, reserving the scanning data;
if the interval time of the R wave crest in the scanning data is smaller than the first preset interval time or larger than the second preset interval time, discarding the scanning data and re-collecting the scanning data;
wherein the first preset interval time is less than the second preset interval time.
4. A method according to any one of claims 1-3, wherein the screening the scan data in the cardiac cycle according to the numerical relationship between the actual interval time of the R-wave peak in the cardiac cycle and the preset interval time to obtain the target scan data includes:
determining whether a phase number of the scan data in the cardiac cycle reaches the preset phase number;
and if the phase number of the scanning data in the cardiac cycle reaches the preset phase number, screening the scanning data in the cardiac cycle according to the numerical relation between the actual interval time of the R wave crest and the preset interval time to obtain target scanning data.
5. The method according to claim 4, wherein the method further comprises:
and if the phase number of the scanning data in the cardiac cycle reaches the preset phase number, screening the scanning data in the cardiac cycle according to the numerical relation between the interval time of the R wave crest and the preset interval time after the scanning data acquisition of all cardiac cycles is completed, and obtaining target scanning data.
6. A method according to any one of claims 1-3, wherein prior to acquiring the scan data, the method further comprises:
and after detecting the R wave peak of the electrocardio gating, performing null scanning through pulse or radio frequency so as to enable the acquisition of the scanning data to be in a steady state.
7. An image reconstruction apparatus, the apparatus comprising:
the acquisition module is used for scanning the scanning object according to the preset phase number after detecting the R wave crest of the electrocardiographic gate control, and acquiring scanning data;
the screening module is used for screening the scanning data according to the numerical relation between the actual interval time of the R wave crest in the cardiac cycle and the preset interval time when the scanning data of one cardiac cycle are acquired, so as to obtain target scanning data;
the mapping module is used for carrying out time sequence interpolation on the target scanning data to obtain reconstruction data when the phase position corresponding to the target scanning data is different from the target phase position, wherein the target phase position is determined according to the phase position of the scanning data acquired in the average cardiac cycle of the scanning object, and the reconstruction data is obtained;
and the reconstruction module is used for reconstructing an image based on the reconstruction data.
8. A computer readable storage medium, on which a computer program is stored, characterized in that the program, when being executed by a processor, implements the steps of the method according to any one of claims 1-6.
9. An electronic device, comprising:
a memory having a computer program stored thereon;
a processor for executing the computer program in the memory to implement the steps of the method of any one of claims 1-6.
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