CN111084635B - CT scanning method and device, CT equipment and CT system - Google Patents
CT scanning method and device, CT equipment and CT system Download PDFInfo
- Publication number
- CN111084635B CN111084635B CN202010001646.7A CN202010001646A CN111084635B CN 111084635 B CN111084635 B CN 111084635B CN 202010001646 A CN202010001646 A CN 202010001646A CN 111084635 B CN111084635 B CN 111084635B
- Authority
- CN
- China
- Prior art keywords
- bulb
- scanning
- phase
- heart
- detected object
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
- 238000002591 computed tomography Methods 0.000 title claims abstract description 60
- 238000000034 method Methods 0.000 title claims abstract description 58
- 230000008569 process Effects 0.000 claims abstract description 21
- 230000000747 cardiac effect Effects 0.000 claims description 21
- 238000012545 processing Methods 0.000 claims description 11
- 238000012544 monitoring process Methods 0.000 claims description 6
- 238000003384 imaging method Methods 0.000 description 8
- 238000010586 diagram Methods 0.000 description 6
- 238000013459 approach Methods 0.000 description 2
- 239000002872 contrast media Substances 0.000 description 2
- 230000009977 dual effect Effects 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 230000002123 temporal effect Effects 0.000 description 2
- 230000006978 adaptation Effects 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 238000004590 computer program Methods 0.000 description 1
- 210000004351 coronary vessel Anatomy 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- 238000011160 research Methods 0.000 description 1
- 230000004044 response Effects 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
- A61B6/032—Transmission computed tomography [CT]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
- A61B6/4007—Arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/54—Control of apparatus or devices for radiation diagnosis
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/58—Testing, adjusting or calibrating thereof
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Medical Informatics (AREA)
- Radiology & Medical Imaging (AREA)
- Molecular Biology (AREA)
- Biophysics (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Optics & Photonics (AREA)
- Pathology (AREA)
- Physics & Mathematics (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- High Energy & Nuclear Physics (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Pulmonology (AREA)
- Theoretical Computer Science (AREA)
- Apparatus For Radiation Diagnosis (AREA)
Abstract
The embodiment of the invention provides a CT scanning method, a CT scanning device, CT equipment and a CT system. According to the embodiment of the invention, before scanning, the target distance in the Z direction between the first bulb and the second bulb is determined according to the heart rate information of the detected object, the first phase and the second phase, the positions of the first bulb and the second bulb in the Z direction are adjusted according to the target distance, the first bulb and the second bulb are arranged along the Z direction, after scanning is started, the first bulb and the second bulb are respectively scanned, the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase, the reconstructed image of the heart of the detected object in the first phase is obtained according to the scanning data of the first bulb, the reconstructed image of the heart of the detected object in the second phase is obtained according to the scanning data of the second bulb, the reconstructed images of the two phases can be obtained in one scanning process, the success rate of obtaining the reconstructed images qualified is improved, and the scanning efficiency is improved.
Description
Technical Field
The invention relates to the technical field of medical image processing, in particular to a CT scanning method, a device, CT equipment and a CT system.
Background
CT (Computed Tomography) coronary vessel imaging is currently in widespread clinical use as a safe and accurate noninvasive imaging technique and has been a popular research direction in cardiac imaging. A difficulty with cardiac imaging is that the heart is constantly in motion during scanning. In one cardiac cycle, reconstructing an image of the optimal phase position with the highest temporal resolution is a key factor in ensuring image quality and diagnostic accuracy.
In the related art, a large pitch imaging mode is used, and only one phase, such as the end diastole phase, is reconstructed during one scan. In the technology, if the reconstruction effect of the selected phase is not ideal, the phase needs to be modified and scanned again, and the efficiency is low.
Disclosure of Invention
In order to overcome the problems in the related art, the invention provides a CT scanning method, a device, CT equipment and a CT system, and the scanning efficiency is improved.
According to a first aspect of the embodiments of the present invention, there is provided a CT scanning method applied to a dual-bulb large-pitch CT scanning process of a heart, a first bulb of the dual bulbs is used for scanning data of a first phase of the heart, and a second bulb of the dual bulbs is used for scanning data of a second phase of the heart; the method comprises the following steps:
before scanning, determining a Z-direction target distance between the first bulb and the second bulb according to heart rate information of a detected object and the first phase and the second phase;
adjusting the positions of the first bulb and the second bulb in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction vertical to the cross section of the scanning cavity;
after the scanning is started, the first bulb and the second bulb are respectively scanned, and the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase;
and acquiring a reconstructed image of the heart of the detected object in the first phase according to the scanning data of the first bulb, and acquiring a reconstructed image of the heart of the detected object in the second phase according to the scanning data of the second bulb.
According to a second aspect of the embodiments of the present invention, there is provided a CT scanning apparatus for a large pitch CT scanning procedure with two bulbs of hearts, a first bulb of the two bulbs being used for scanning data of a first phase of the heart, and a second bulb of the two bulbs being used for scanning data of a second phase of the heart; the device comprises:
the distance determining module is used for determining a target distance in the Z direction between the first bulb and the second bulb according to the heart rate information of the detected object, the first phase and the second phase before scanning;
the position adjusting module is used for adjusting the positions of the first bulb tube and the second bulb tube in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction perpendicular to the cross section of the scanning cavity;
the scanning module is used for respectively scanning the first bulb and the second bulb after scanning starts, and the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase;
and the reconstruction module is used for acquiring a reconstructed image of the heart of the detected object in the first phase according to the scanning data of the first bulb and acquiring a reconstructed image of the heart of the detected object in the second phase according to the scanning data of the second bulb.
According to a third aspect of embodiments of the present invention, there is provided a CT apparatus including: the system comprises an internal bus, a memory, a processor and an external interface which are connected through the internal bus; the external interface is used for connecting a detector of the CT system, and the detector comprises a plurality of detector chambers and corresponding processing circuits;
the memory is used for storing machine readable instructions corresponding to CT scanning logic;
the processor is configured to read the machine-readable instructions on the memory and perform the following operations:
before scanning, determining a Z-direction target distance between a first bulb and a second bulb according to heart rate information of a detected object, a first phase and a second phase;
adjusting the positions of the first bulb and the second bulb in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction perpendicular to the cross section of the scanning cavity;
after the scanning is started, the first bulb and the second bulb are respectively scanned, and the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase;
and acquiring a reconstructed image of the heart of the detected object in the first phase according to the scanning data of the first bulb, and acquiring a reconstructed image of the heart of the detected object in the second phase according to the scanning data of the second bulb.
According to a fourth aspect of the embodiments of the present invention, there is provided a CT system, comprising a detector, a scanning bed and a CT apparatus, the detector comprising a plurality of detector chambers and corresponding processing circuitry; wherein:
the detector chamber is used for detecting X-rays passing through a scanned object and converting the X-rays into electric signals in the scanning process of the CT system;
the processing circuit is used for converting the electric signal into a pulse signal and acquiring energy information of the pulse signal;
the CT device is used for:
before scanning, determining a Z-direction target distance between a first bulb and a second bulb according to heart rate information of a detected object, a first phase and a second phase;
adjusting the positions of the first bulb and the second bulb in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction perpendicular to the cross section of the scanning cavity;
after the scanning is started, the first bulb and the second bulb are respectively scanned, and the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase;
and acquiring a reconstructed image of the heart of the detected object in the first phase according to the scanning data of the first bulb, and acquiring a reconstructed image of the heart of the detected object in the second phase according to the scanning data of the second bulb.
The technical scheme provided by the embodiment of the invention has the following beneficial effects:
according to the embodiment of the invention, before scanning, a target distance in the Z direction between a first bulb and a second bulb is determined according to heart rate information of a detected object, a first phase and a second phase, the positions of the first bulb and the second bulb in the Z direction are adjusted according to the target distance, the first bulb and the second bulb are arranged along the Z direction, after scanning starts, the first bulb and the second bulb are respectively scanned, the heart of the detected object is in the scanning range of the first bulb in the first phase and is in the scanning range of the second bulb in the second phase, a reconstructed image of the heart of the detected object in the first phase is obtained according to the scanning data of the first bulb, a reconstructed image of the heart of the detected object in the second phase is obtained according to the scanning data of the second bulb, the scanning data of the two phases can be obtained in one scanning process, the reconstructed images of the two phases are obtained, the reconstruction times of the two phases are improved, and the success rate of obtaining the reconstructed images is improved.
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 specification.
Drawings
The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments consistent with the present specification and together with the description, serve to explain the principles of the specification.
Fig. 1 is a flowchart illustrating a CT scanning method according to an embodiment of the present invention.
Fig. 2 is a schematic diagram of the position of the bulb in different coordinate systems.
Fig. 3 is a functional block diagram of a CT scanning apparatus according to an embodiment of the present invention.
Fig. 4 is a hardware configuration diagram of a CT apparatus according to an embodiment of the present invention.
Detailed Description
Reference will now be made in detail to the exemplary embodiments, examples of which are illustrated in the accompanying drawings. When the following description refers to the accompanying drawings, like numbers in different drawings represent the same or similar elements unless otherwise indicated. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with the present invention. Rather, they are merely examples of apparatus and methods consistent with certain aspects of embodiments of the invention, as detailed in the following claims.
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 embodiments of the invention. As used in the description of the 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 also be understood that the term "and/or" as used herein refers to and encompasses any and all possible combinations of one or more of the associated listed items.
It should be understood that although the terms first, second, third, etc. may be used to describe various information in embodiments of the present invention, the information should not be limited by these terms. These terms are only used to distinguish one type of information from another. For example, the first information may also be referred to as second information, and similarly, the second information may also be referred to as first information, without departing from the scope of embodiments of the present invention. The word "if," as used herein, may be interpreted as "at … …" or "at … …" or "in response to a determination," depending on the context.
First, the Z direction in this document will be explained. Herein, the Z direction refers to a direction perpendicular to the cross section of the scanning chamber. The Z direction is parallel to the direction of the scanning bed.
Next, the concept of a next phase is explained. In a CT scan of the heart, the time period between two adjacent R peaks of the corresponding electrocardiogram is one cardiac cycle. Each cardiac cycle is divided on average into 100 fractions, each fraction corresponding to a time period of one phase. For example, phase 45% represents the 45 th time period, and phase 75% represents the 75 th time period.
Currently, there are several methods for CT scanning of the heart:
the first is the common look-behind helical cardiac image. This approach results in a higher radiation exposure to the patient due to the lower pitch, which ensures a higher temporal resolution.
The second is the OneBeat imaging mode of single tube CT. In this way, a bulb is used for scanning, the image is built in a single cardiac cycle by using a large pitch, and only one phase is reconstructed in one scanning. The mode can effectively reduce the radiation quantity of a patient and simultaneously ensure better time resolution.
The third is a super-pitch imaging mode of the double bulb tube. This way, double bulbs are used for scanning, and the two bulbs are respectively located at two sides of the scanning bed and located at the same Z coordinate. This approach also uses a large pitch to complete the imaging within a single cardiac cycle, with only one phase being reconstructed for a scan.
In the mode, no matter in the oneBeat image-building mode of single-bulb tube CT or in the ultra-large pitch image-building mode of double-bulb tube CT, one scanning only rebuilds one phase, and if the rebuilding effect of the selected phase is not ideal, the phase can be modified for scanning again. Thus, not only the number of scans and the scan dose are increased, but also the contrast agent needs to be injected again and tracked, and the risk that the reconstructed image is not ideal due to uncontrollable state in the patient scan is increased.
The CT scanning method of the present invention will be described in detail below with reference to examples.
Fig. 1 is a flowchart illustrating a CT scanning method according to an embodiment of the present invention. The CT scanning method provided by the embodiment of the invention is applied to a double-bulb large-pitch CT scanning process of the heart, wherein a first bulb in the double bulbs is used for scanning data of a first phase of the heart, and a second bulb in the double bulbs is used for scanning data of a second phase of the heart;
as shown in fig. 1, in this embodiment, the CT scanning method may include:
s101, before scanning, determining a Z-direction target distance between a first bulb and a second bulb according to heart rate information of a detected object, a first phase and a second phase.
S102, adjusting the positions of the first bulb and the second bulb in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction perpendicular to the cross section of the scanning cavity;
and S103, after the scanning is started, the first bulb and the second bulb are respectively scanned, and the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase.
S104, acquiring a reconstructed image of the heart of the detected object in the first phase according to the scanning data of the first bulb, and acquiring a reconstructed image of the heart of the detected object in the second phase according to the scanning data of the second bulb.
In this embodiment, the heart rate information of the subject may be obtained from an electrocardiogram of the subject.
In an exemplary implementation process, before step S101, the method may further include:
heart rate information of a subject is acquired.
The heart rate of a person is different in different situations, e.g. the heart rate is higher during exercise than at rest. Therefore, in order to ensure that the heart rate of the detected object can be accurately predicted during scanning, the heart rate of the detected object in a period before scanning can be used for prediction.
In one exemplary implementation, acquiring heart rate information of the subject may include:
and determining the heart rate information of the detected object according to the electrocardiogram of the detected object in a set time period before scanning.
For example, the heart rate information of the detected object is determined by using the heart rate information in the electrocardiogram of the 3 rd, 4 th and 5 th cardiac cycles before scanning.
Assuming that the heart rates in the electrocardiograms of the 3 rd, 4 th and 5 th cardiac cycles before scanning are respectively 61 times/second, 60 times/second and 60 times/second, it can be seen that the heart rate of the detected object can be determined to be 60 times/second if the value of the heart rate is gradually stabilized at 60 times/second. The heart rate information during scanning is determined by using the heart rate value during stable before scanning, so that a more accurate prediction result can be obtained.
In another example, assuming that the heart rates in the electrocardiograms of the 3 rd, 4 th and 5 th cardiac cycles before scanning are respectively 62/s, 60/s and 61/s, the average value of the heart rate values of the 3 cardiac cycles of 61/s can be taken as the heart rate value of the detected object at the scanning time. In the example, the average value of the heart rate values of a plurality of cardiac cycles before scanning is used as the heart rate value of the detected object during scanning, so that a more accurate prediction result can be obtained.
In an exemplary implementation, acquiring the heart rate information of the subject may include:
receiving input heart rate information, and determining the input heart rate information as the heart rate information of the detected object.
Fig. 2 is a schematic diagram of the position of the bulb in different coordinate systems. In fig. 2, the XY plane is a plane parallel to the scanning chamber, wherein the Y direction is a direction perpendicular to the scanning bed plane, and the X direction is a direction parallel to the scanning chamber and perpendicular to the Y direction. In fig. 2, R represents the gantry rotation radius, i.e. the distance from the focal point of the bulb to the center of rotation.
As shown in fig. 2, when the first bulb and the second bulb are arranged in the Z direction, the first bulb and the second bulb are overlapped as viewed from the XY plane; the position of the first bulb in the Z direction is Z1, the position of the second bulb in the Z direction is Z2, and the distance between Z1 and Z2 is equal to the target distance D determined in step S101, as viewed from the YZ plane.
In this embodiment, the target distance D in the Z direction between the first bulb and the second bulb may be calculated by the following formula (1):
D＝(Phase2-Phase1)*HL (1)
in the formula (1), phase1 represents a first Phase, phase2 represents a second Phase, and HL represents a bed moving distance in one heartbeat time in mm (millimeters).
Wherein, HL can be calculated by the following formula (2):
in formula (2), HR represents heart rate; rotSpeed denotes gantry rotation speed in units of s (seconds); cirLen denotes the bed distance of one gantry rotation in mm (millimeters).
Wherein CirLen can be calculated by the following formula (3):
CirLen＝nSliceNum*fThickness*fPitch (3)
in the formula (3), nSliceNum represents the number of detector rows; fThickness represents the z-direction thickness of the detector cell in mm; fPitch denotes the pitch.
In one example, the first Phase1 is the end-systolic Phase, 45%; the second Phase2 is the end-diastolic Phase and is 75%.
In step S102, after the positions of the first bulb and the second bulb in the Z direction are adjusted according to the target distance, the distance between the first bulb and the second bulb in the Z direction is equal to the target distance.
In this embodiment, the time for starting the scanning may be determined according to a real-time electrocardiogram of the subject.
In an exemplary implementation process, before step S103, the method may further include:
monitoring an electrocardiogram of the detected object in real time, and determining the phase of the heart of the detected object according to the electrocardiogram;
when the heart of the detected object is monitored to be in the first phase, starting the first bulb tube to scan; and when the heart of the detected object is monitored to be in the second phase, starting the second bulb tube to scan. The scanning bed moves in the negative Z direction during scanning. When the scanning is started, the heart of the detected object is in a first phase, and the heart is in the scanning range of the first bulb tube at the moment, and the scanning of the first bulb tube is started; when the heart is in the second phase, the heart moves to the scanning range of the second bulb along with the movement of the scanning bed, and the scanning of the second bulb is started. Thus, in one cardiac cycle, data for a first phase is acquired by a first balloon and data for a second phase is acquired by a second balloon, i.e., data for both phases are acquired for one scan.
Taking fig. 2 as an example, when the scanning bed moves along the Z direction in the negative direction, i.e. the bed enters into the movement, the coarse pitch scanning is performed with the first ball tube scanning end systole (45%) as the standard, and when the heart position reaches Z1, the phase of the scanning is 45%; when the heart position reaches Z2, the heart motion state is 75% of the phase, and the scanning range of Z2 is reached, so that after one scanning, the heart data of two phase phases can be obtained.
It should be noted that, for each phase, the start scanning time is the starting time point of the time period in which the phase is located. For example, when the first phase is 45%, the corresponding time period is 40% -50% phase, and therefore, when the phase of the heart is detected to be 40%, the scanning of the first bulb is started. Similarly, when the second phase is 75%, the corresponding time period is 70% -80% of the phase, so that when the phase of the heart is monitored to be 70%, scanning of the second bulb is started.
In the embodiment, the scanning is started before the first phase, and certain redundancy is provided for the starting scanning position, so that the problem of inaccurate target phase reconstruction caused by heart rate fluctuation can be reduced.
The duration of the entire scanning process is one cardiac cycle. During scanning, the first bulb and the second bulb are respectively scanned. The first bulb tube scans to obtain data of a first phase, and the second bulb tube scans to obtain data of a second phase.
In an exemplary implementation process, after step S103 and before step S104, the method may further include:
when the scan duration reaches one cardiac cycle, the scan is stopped.
The embodiment can simultaneously obtain the scanning data of two different phases in the scanning process of one cardiac cycle.
In step S104, the reconstructed images of the heart of the examined object in the first phase and the second phase are obtained according to the scan data of the first bulb and the scan data of the second bulb, respectively, so that the success rate of obtaining a qualified reconstructed image in one scan is improved, and the probability of needing multiple scans is reduced, thereby reducing the number of scans and improving the scanning efficiency.
For the detected object, the scanning frequency is reduced, the scanning dosage is also reduced, the contrast agent does not need to be injected again and tracked, and the time of both the detected object and a scanning doctor is saved.
According to the CT scanning method provided by the embodiment of the invention, before scanning, the target distance in the Z direction between the first bulb and the second bulb is determined according to the heart rate information of the detected object, the first phase and the second phase, the positions of the first bulb and the second bulb in the Z direction are adjusted according to the target distance, the first bulb and the second bulb are arranged along the Z direction, after scanning starts, the first bulb and the second bulb are respectively scanned, the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase, the reconstructed image of the heart of the detected object in the first phase is obtained according to the scanning data of the first bulb, the reconstructed image of the heart of the detected object in the second phase is obtained according to the scanning data of the second bulb, the reconstructed image of the heart of the detected object in the first phase can be obtained in the scanning process of one time, the reconstructed image of the two phases is obtained, the reconstruction efficiency of the reconstructed image is improved, and the reconstruction efficiency of the reconstructed image is improved.
Based on the above method embodiment, the embodiment of the present invention further provides corresponding apparatus, device, and storage medium embodiments.
Fig. 3 is a functional block diagram of a CT scanning apparatus according to an embodiment of the present invention. The CT scanning device is applied to a double-bulb large-pitch CT scanning process of the heart, a first bulb in the double bulbs is used for scanning data of a first phase of the heart, and a second bulb in the double bulbs is used for scanning data of a second phase of the heart; as shown in fig. 3, in this embodiment, the CT scanning apparatus may include:
a distance determining module 310, configured to determine, before scanning, a target distance in the Z direction between the first bulb and the second bulb according to heart rate information of a subject, the first phase and the second phase;
a position adjusting module 320, configured to adjust positions of the first bulb and the second bulb in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction perpendicular to the cross section of the scanning cavity;
a scanning module 330, configured to perform scanning on the first bulb and the second bulb respectively after the scanning starts, where the heart of the object under examination is in a scanning range of the first bulb in the first phase, and is in a scanning range of the second bulb in the second phase;
a reconstruction module 340, configured to acquire a reconstructed image of the heart of the object under examination in the first phase according to the scan data of the first bulb, and acquire a reconstructed image of the heart of the object under examination in the second phase according to the scan data of the second bulb.
In an exemplary implementation process, the method may further include:
and the heart rate acquisition module is used for acquiring the heart rate information of the detected object.
In an exemplary implementation, the heart rate acquisition module may be specifically configured to:
and determining the heart rate information of the detected object according to the electrocardiogram of the detected object in a set time period before scanning.
In an exemplary implementation, the heart rate acquisition module may be specifically configured to:
receiving input heart rate information, and determining the input heart rate information as the heart rate information of the detected object.
In an exemplary implementation, the apparatus may further include:
the monitoring module is used for monitoring the electrocardiogram of the detected object in real time and determining the phase of the heart of the detected object according to the electrocardiogram;
the starting scanning module is used for starting the first bulb tube to scan when the heart of the detected object is monitored to be in the first phase; and when the heart of the detected object is monitored to be in the second phase, starting the second bulb tube to scan.
In an exemplary implementation, the apparatus may further include:
and the stopping module is used for stopping scanning when the scanning time length reaches one cardiac cycle.
In one exemplary implementation, the first phase is end systole and the second phase is end diastole.
The embodiment of the invention also provides CT equipment which is applied to a double-bulb large-pitch CT scanning process of the heart, wherein a first bulb in the double bulbs is used for scanning data of a first phase of the heart, and a second bulb in the double bulbs is used for scanning data of a second phase of the heart.
Fig. 4 is a hardware configuration diagram of a CT apparatus according to an embodiment of the present invention. As shown in fig. 4, the CT apparatus includes: an internal bus 401, and a memory 402, a processor 403 and an external interface 404 connected via the internal bus, wherein the external interface is used for connecting a detector of the CT system, the detector comprising a plurality of detector chambers and corresponding processing circuits;
the memory 402 is used for storing machine readable instructions corresponding to CT scanning logic;
the processor 403 is configured to read the machine-readable instructions in the memory 402 and execute the instructions to implement the following operations:
before scanning, determining a Z-direction target distance between a first bulb and a second bulb according to heart rate information of a detected object, a first phase and a second phase;
adjusting the positions of the first bulb and the second bulb in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction perpendicular to the cross section of the scanning cavity;
after the scanning is started, the first bulb and the second bulb are respectively scanned, and the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase;
and acquiring a reconstructed image of the heart of the detected object in the first phase according to the scanning data of the first bulb, and acquiring a reconstructed image of the heart of the detected object in the second phase according to the scanning data of the second bulb.
In an exemplary implementation, before the target distance in the Z direction between the first bulb and the second bulb according to the heart rate information of the subject, the first phase and the second phase, further comprising:
and acquiring the heart rate information of the detected object.
In one exemplary implementation, acquiring heart rate information of the subject includes:
and determining the heart rate information of the detected object according to the electrocardiogram of the detected object in a set time period before scanning.
In one exemplary implementation, acquiring heart rate information of the subject includes:
receiving input heart rate information, and determining the input heart rate information as the heart rate information of the detected object.
In an exemplary implementation, the method further includes:
monitoring an electrocardiogram of the detected object in real time, and determining the phase of the heart of the detected object according to the electrocardiogram;
when the heart of the detected object is monitored to be in the first phase, starting the first bulb tube to scan; and starting the second bulb to scan when the heart of the detected object is monitored to be in the second phase.
In an exemplary implementation, the method further includes:
when the scan duration reaches one cardiac cycle, the scan is stopped.
In one exemplary implementation, the first phase is end systole and the second phase is end diastole.
The embodiment of the invention also provides a CT system, which comprises a detector, a scanning bed and CT equipment, wherein the detector comprises a plurality of detector chambers and corresponding processing circuits; wherein:
the detector chamber is used for detecting X-rays passing through a scanned object and converting the X-rays into electric signals in the scanning process of the CT system;
the processing circuit is used for converting the electric signal into a pulse signal and acquiring energy information of the pulse signal;
the CT device is used for executing any one of the CT scanning methods.
An embodiment of the present invention further provides a computer-readable storage medium, having stored thereon a computer program for a dual-bulb large-pitch CT scanning process for a heart, a first bulb of the dual-bulb being used for scanning data of a first phase of the heart, and a second bulb of the dual-bulb being used for scanning data of a second phase of the heart; wherein the program when executed by a processor performs the following:
before scanning, determining a Z-direction target distance between a first bulb and a second bulb according to heart rate information of a detected object, a first phase and a second phase;
adjusting the positions of the first bulb and the second bulb in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction perpendicular to the cross section of the scanning cavity;
after the scanning is started, the first bulb and the second bulb are respectively scanned, and the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase;
and acquiring a reconstructed image of the heart of the detected object in the first phase according to the scanning data of the first bulb, and acquiring a reconstructed image of the heart of the detected object in the second phase according to the scanning data of the second bulb.
In an exemplary implementation process, before the target distance in the Z direction between the first bulb and the second bulb according to the heart rate information of the subject, the first phase and the second phase, further comprising:
and acquiring the heart rate information of the detected object.
In one exemplary implementation, acquiring heart rate information of the subject includes:
and determining the heart rate information of the detected object according to the electrocardiogram of the detected object in a set time period before scanning.
In one exemplary implementation, acquiring heart rate information of the subject includes:
receiving input heart rate information, and determining the input heart rate information as the heart rate information of the detected object.
In an exemplary implementation, the method further includes:
monitoring an electrocardiogram of the detected object in real time, and determining the phase of the heart of the detected object according to the electrocardiogram;
when the heart of the detected object is monitored to be in the first phase, starting the first bulb tube to scan; and when the heart of the detected object is monitored to be in the second phase, starting the second bulb tube to scan.
In an exemplary implementation, the method further includes:
when the scan duration reaches one cardiac cycle, the scan is stopped.
In one exemplary implementation, the first phase is end systole and the second phase is end diastole.
For the device and apparatus embodiments, as they correspond substantially to the method embodiments, reference may be made to the partial description of the method embodiments for relevant points. The above-described embodiments of the apparatus are merely illustrative, and the modules described as separate components may or may not be physically separate, and the components 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 modules. Some or all of the modules can be selected according to actual needs to achieve the purpose of the solution in the specification. One of ordinary skill in the art can understand and implement it without inventive effort.
The foregoing description has been directed to specific embodiments of this disclosure. Other embodiments are within the scope of the following claims. In some cases, the actions or steps recited in the claims may be performed in a different order than in the embodiments and still achieve desirable results. In addition, the processes depicted in the accompanying figures do not necessarily require the particular order shown, or sequential order, to achieve desirable results. In some embodiments, multitasking and parallel processing may also be possible or may be advantageous.
Other embodiments of the present description will be apparent to those skilled in the art from consideration of the specification and practice of the invention disclosed herein. This specification is intended to cover any variations, uses, or adaptations of the specification following, in general, the principles of the specification and including such departures from the present disclosure as come within known or customary practice within the art to which the specification pertains. It is intended that the specification and examples be considered as exemplary only, with a true scope and spirit of the specification being indicated by the following claims.
It will be understood that the present description is not limited to the precise arrangements described above and shown in the drawings, and that various modifications and changes may be made without departing from the scope thereof. The scope of the present description is limited only by the appended claims.
The above description is only a preferred embodiment of the present disclosure, and should not be taken as limiting the present disclosure, and any modifications, equivalents, improvements, etc. made within the spirit and principle of the present disclosure should be included in the scope of the present disclosure.
Claims (10)
1. A CT scanning method is characterized in that the method is applied to a double-bulb large-pitch CT scanning process of the heart, a first bulb in the double bulbs is used for scanning data of a first phase of the heart, and a second bulb in the double bulbs is used for scanning data of a second phase of the heart; the method comprises the following steps:
before scanning, determining a Z-direction target distance between the first bulb and the second bulb according to heart rate information of a detected object, the first phase and the second phase;
adjusting the positions of the first bulb and the second bulb in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction perpendicular to the cross section of the scanning cavity;
after the scanning is started, the first bulb and the second bulb are respectively scanned, and the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase;
and acquiring a reconstructed image of the heart of the detected object in the first phase according to the scanning data of the first bulb, and acquiring a reconstructed image of the heart of the detected object in the second phase according to the scanning data of the second bulb.
2. The method according to claim 1, further comprising, before the target distance in the Z direction between the first and second bulbs according to the heart rate information of the subject, the first and second phases:
and acquiring the heart rate information of the detected object.
3. The method of claim 2, wherein obtaining heart rate information of the subject comprises:
and determining the heart rate information of the detected object according to the electrocardiogram of the detected object in a set time period before scanning.
4. The method according to claim 2, wherein acquiring heart rate information of the subject comprises:
receiving input heart rate information, and determining the input heart rate information as the heart rate information of the detected object.
5. The method of claim 1, further comprising:
monitoring an electrocardiogram of the detected object in real time, and determining the phase of the heart of the detected object according to the electrocardiogram;
when the heart of the detected object is monitored to be in the first phase, starting the first bulb tube to scan; and when the heart of the detected object is monitored to be in the second phase, starting the second bulb tube to scan.
6. The method of claim 1, further comprising:
when the scan duration reaches one cardiac cycle, the scan is stopped.
7. The method of claim 1, wherein the first phase is end systole and the second phase is end diastole.
8. A CT scanning device is characterized by being applied to a double-bulb large-pitch CT scanning process of a heart, wherein a first bulb in the double bulbs is used for scanning data of a first phase of the heart, and a second bulb in the double bulbs is used for scanning data of a second phase of the heart; the device comprises:
the distance determining module is used for determining a target distance in the Z direction between the first bulb and the second bulb according to the heart rate information of the detected object, the first phase and the second phase before scanning;
the position adjusting module is used for adjusting the positions of the first bulb tube and the second bulb tube in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction perpendicular to the cross section of the scanning cavity;
the scanning module is used for respectively scanning the first bulb and the second bulb after scanning starts, and the heart of the detected object is in the scanning range of the first bulb in the first phase and is in the scanning range of the second bulb in the second phase;
and the reconstruction module is used for acquiring a reconstructed image of the heart of the detected object in the first phase according to the scanning data of the first bulb and acquiring a reconstructed image of the heart of the detected object in the second phase according to the scanning data of the second bulb.
9. A CT apparatus, comprising: the system comprises an internal bus, a memory, a processor and an external interface which are connected through the internal bus; the external interface is used for connecting a detector of the CT system, and the detector comprises a plurality of detector chambers and corresponding processing circuits;
the memory is used for storing machine readable instructions corresponding to CT scanning logic;
the processor is configured to read the machine-readable instructions on the memory and perform the following operations:
before scanning, determining a Z-direction target distance between a first bulb and a second bulb according to heart rate information of a detected object, a first phase and a second phase;
adjusting the positions of the first bulb tube and the second bulb tube in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction perpendicular to the cross section of the scanning cavity;
after the scanning is started, the first bulb and the second bulb are respectively scanned, and the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase;
and acquiring a reconstructed image of the heart of the detected object in the first phase according to the scanning data of the first bulb, and acquiring a reconstructed image of the heart of the detected object in the second phase according to the scanning data of the second bulb.
10. A CT system comprising a detector, a scanning bed and a CT apparatus, the detector comprising a plurality of detector chambers and corresponding processing circuitry; wherein:
the detector is used for detecting X-rays passing through a scanned object and converting the X-rays into electric signals during the scanning process of the CT system;
the processing circuit is used for converting the electric signal into a pulse signal and acquiring energy information of the pulse signal;
the CT device is used for:
before scanning, determining a Z-direction target distance between a first bulb and a second bulb according to heart rate information of a detected object, a first phase and a second phase;
adjusting the positions of the first bulb and the second bulb in the Z direction according to the target distance; the first bulb tube and the second bulb tube are arranged along the Z direction, and the Z direction is a direction vertical to the cross section of the scanning cavity;
after the scanning is started, the first bulb and the second bulb are respectively scanned, and the heart of the detected object is in the scanning range of the first bulb in the first phase and in the scanning range of the second bulb in the second phase;
and acquiring a reconstructed image of the heart of the detected object in the first phase according to the scanning data of the first bulb, and acquiring a reconstructed image of the heart of the detected object in the second phase according to the scanning data of the second bulb.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010001646.7A CN111084635B (en) | 2020-01-02 | 2020-01-02 | CT scanning method and device, CT equipment and CT system |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202010001646.7A CN111084635B (en) | 2020-01-02 | 2020-01-02 | CT scanning method and device, CT equipment and CT system |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN111084635A CN111084635A (en) | 2020-05-01 |
| CN111084635B true CN111084635B (en) | 2023-03-31 |
Family
ID=70399687
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202010001646.7A Active CN111084635B (en) | 2020-01-02 | 2020-01-02 | CT scanning method and device, CT equipment and CT system |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN111084635B (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN112330800B (en) * | 2020-10-28 | 2023-12-29 | 沈阳先进医疗设备技术孵化中心有限公司 | Image reconstruction method, device, console device and CT system |
| CN113345043B (en) * | 2021-06-01 | 2024-05-17 | 苏州晟诺医疗科技有限公司 | Method, device, medium and electronic equipment for eliminating CT image metal artifact |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104545973A (en) * | 2014-11-26 | 2015-04-29 | 沈阳东软医疗系统有限公司 | CT (Computed Tomography) scanning method and device for heart |
| CN110335671A (en) * | 2019-07-12 | 2019-10-15 | 四川明峰医疗科技有限公司 | A kind of modulated CT detector data compression acquisition mode |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7570733B2 (en) * | 2005-06-10 | 2009-08-04 | General Electric Company | Step-and-shoot cardiac CT imaging |
-
2020
- 2020-01-02 CN CN202010001646.7A patent/CN111084635B/en active Active
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104545973A (en) * | 2014-11-26 | 2015-04-29 | 沈阳东软医疗系统有限公司 | CT (Computed Tomography) scanning method and device for heart |
| CN110335671A (en) * | 2019-07-12 | 2019-10-15 | 四川明峰医疗科技有限公司 | A kind of modulated CT detector data compression acquisition mode |
Non-Patent Citations (1)
| Title |
|---|
| 夏平 ; 徐青松 ; 郝敬明 ; 胡春艾 ; 曹伟 ; 师毅冰 ; 夏有生 ; .时间分辨力-心动周期特性曲线在CT冠状动脉成像中的应用.中国医学影像技术.2015,(01),全文. * |
Also Published As
| Publication number | Publication date |
|---|---|
| CN111084635A (en) | 2020-05-01 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| Taguchi et al. | High temporal resolution for multislice helical computed tomography | |
| US7058440B2 (en) | Dynamic computed tomography imaging using positional state modeling | |
| US6539074B1 (en) | Reconstruction of multislice tomographic images from four-dimensional data | |
| CN110009709B (en) | Medical image imaging method and system | |
| US20040077941A1 (en) | Method and system for image improvement with ECG gating and dose reduction in CT imaging | |
| CN106539584B (en) | Magnetic resonance imaging method and system | |
| JP5954761B2 (en) | X-ray computed tomography apparatus and image processing method | |
| CN1907228A (en) | Medical imaging method and an associated apparatus | |
| US7313213B1 (en) | Step-and-shoot cardiac CT imaging | |
| CN111192228B (en) | Image processing method, device, CT equipment and CT system | |
| US11471065B2 (en) | Medical image diagnosis apparatus | |
| CN111084635B (en) | CT scanning method and device, CT equipment and CT system | |
| US11160523B2 (en) | Systems and methods for cardiac imaging | |
| US8699772B2 (en) | Scanning of a cyclically moved examination object using a contrast agent within the scope of a preliminary examination by means of a CT scanner | |
| US7831011B2 (en) | Computed tomography method and system | |
| WO2006086845A1 (en) | Method and system of motion artefact compensation in a subject | |
| CN110728730B (en) | Image reconstruction method, device, CT equipment and CT system | |
| CN111150419B (en) | Method and device for reconstructing image by spiral CT scanning | |
| Juergens et al. | Multi-detector row computed tomography of the heart: does a multi-segment reconstruction algorithm improve left ventricular volume measurements? | |
| US7558363B2 (en) | Step-and-shoot cardiac CT imaging | |
| CN107303184B (en) | CT scanning X-ray source tube current modulation method and computed tomography device | |
| CN112330800A (en) | Image reconstruction method and device, console equipment and CT system | |
| CN107569251B (en) | Medical imaging method and system and non-transitory computer readable storage medium | |
| JP2000262513A (en) | X-ray computed tomograph | |
| CN110215226B (en) | Image attenuation correction method, image attenuation correction device, computer equipment and storage medium |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant | ||
| TR01 | Transfer of patent right | ||
| TR01 | Transfer of patent right |
Effective date of registration: 20240202 Address after: 110167 No. 177-1 Innovation Road, Hunnan District, Shenyang City, Liaoning Province Patentee after: Shenyang Neusoft Medical Systems Co.,Ltd. Country or region after: China Address before: Room 336, 177-1, Chuangxin Road, Hunnan New District, Shenyang City, Liaoning Province Patentee before: Shenyang advanced medical equipment Technology Incubation Center Co.,Ltd. Country or region before: China |