Medical imaging method and device, computer equipment and storage medium

Abstract

The invention relates to a medical imaging method and device, computer equipment and a storage medium. The method comprises the following steps: acquiring motion information of a bulb tube of the medical imaging equipment in a rotary scanning process; adjusting the target shooting position of an electron beam in the bulb tube according to the motion information of the bulb tube, and enabling the focus position of the bulb tube to be within a preset range of the initial focus position corresponding to each scanning point when the focus position is at each scanning point of rotary scanning; and performing medical imaging scanning based on the bulb tube after focus position adjustment. In the rotary scanning process, the target shooting position of an electron beam in the bulb tube is adjusted according to the movement information of the bulb tube, so that movement confrontation is formed between movement of the target shooting position of the electron beam and movement of a focus of the bulb tube, and at each scanning point, the focus position of the bulb tube is always kept within a preset range of an initial focus position corresponding to the scanning point; the focus position at each scanning point is unchanged or slightly changed, so that the spatial resolution can be improved, and the image quality is improved.

Description

Technical Field

[0001] This application relates to the field of medical imaging technology, and in particular to a medical imaging method, apparatus, computer equipment, and storage medium. Background Technology

[0002] Medical imaging examinations have become the most effective auxiliary means for disease examination and early screening. The quality of medical imaging is the key to medical imaging examinations. The higher the quality of medical imaging, the higher the spatial resolution of the medical images.

[0003] For medical imaging equipment that performs limited-angle scanning, such as mammography and digital radiography (DR), the equivalent focal size increases due to the change in the focal position of the X-ray tube during the limited-angle scanning process, which in turn leads to a decrease in spatial resolution.

[0004] Therefore, how to improve spatial resolution and thus image quality has become an urgent technical problem to be solved. Summary of the Invention

[0005] Therefore, it is necessary to provide a medical imaging method, apparatus, computer equipment, computer-readable storage medium, and computer program product that can improve the spatial resolution of scanned images and thus improve image quality, in order to address the above-mentioned technical problems.

[0006] In a first aspect, this application provides a medical imaging method, comprising:

[0007] Acquire information about the movement of the X-ray tube during rotational scanning in medical imaging equipment;

[0008] The target position of the electron beam in the X-ray tube is adjusted according to the motion information of the X-ray tube, so that the focal position of the X-ray tube is within the preset range of the initial focal position corresponding to each scanning point during the rotational scanning.

[0009] Medical imaging scans are performed using an X-ray tube with the focal position adjusted.

[0010] In one embodiment, adjusting the target position of the electron beam in the X-ray tube based on the tube's motion information includes:

[0011] Determine the target bias voltage based on the motion information of the X-ray tube;

[0012] A target bias voltage is applied to the grid in the X-ray tube to bias the electron beam in the opposite direction to the movement direction of the focal point of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube.

[0013] In one embodiment, the motion information of the X-ray tube includes the motion velocity and motion time of the focal point of the X-ray tube. Determining the target bias voltage based on the motion information of the X-ray tube includes:

[0014] The target movement distance during the rotational scanning process is determined based on the focal point's movement speed and movement time.

[0015] Based on the preset correspondence between the moving distance and the bias voltage, the target bias voltage corresponding to the target moving distance is determined.

[0016] In one embodiment, adjusting the target position of the electron beam in the X-ray tube based on the tube's motion information includes:

[0017] Determine the target bias current based on the motion information of the X-ray tube;

[0018] A target bias current is applied to the magnetic bias coil of the X-ray tube to bias the electron beam in the opposite direction of the focal point movement of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube.

[0019] In one embodiment, the method further includes:

[0020] During the non-scanning period of the rotational scan, the target position of the electron beam is restored.

[0021] In one embodiment, the medical imaging device is a medical imaging device that performs limited-angle tomography scans.

[0022] In one embodiment, the medical imaging equipment includes a mammography X-ray imaging device, a dual-energy or multi-energy digital three-dimensional tomography imaging device for the breast, a fusion imaging device for breast X-ray and ultrasound, and a digital X-ray imaging device.

[0023] Secondly, this application also provides a medical imaging device, comprising:

[0024] The acquisition module is used to acquire the motion information of the X-ray tube during the rotational scanning process of the medical imaging equipment;

[0025] The adjustment module is used to adjust the target position of the electron beam in the X-ray tube at each scanning point of the rotational scan according to the motion information of the X-ray tube, so that the focal position of the X-ray tube at each scanning point is within the preset range of the initial focal position corresponding to each scanning point.

[0026] An imaging module for medical imaging based on an adjusted X-ray tube.

[0027] Thirdly, this application also provides a computer device, including a memory and a processor, wherein the memory stores a computer program, and the processor executes the computer program to implement the steps of the medical imaging method in the first aspect described above.

[0028] Fourthly, this application also provides a computer-readable storage medium having a computer program stored thereon, which, when executed by a processor, implements the steps of the medical imaging method described in the first aspect above.

[0029] Fifthly, this application also provides a computer program product, including a computer program that, when executed by a processor, implements the steps of the medical imaging method described in the first aspect above.

[0030] In the aforementioned medical imaging methods, devices, computer equipment, storage media, and computer program products, during rotational scanning, the medical imaging equipment can acquire the motion information of the X-ray tube during the rotational scanning process, and adjust the target position of the electron beam in the X-ray tube according to the motion information of the X-ray tube, so that the focal position of the X-ray tube is within the preset range of the initial focal position corresponding to each scanning point in the rotational scanning; and then perform medical imaging scanning based on the X-ray tube after the focal position is adjusted. In other words, the medical imaging method proposed in this application allows the medical imaging equipment to adjust the target position of the electron beam in the X-ray tube based on the motion information of the X-ray tube during rotational scanning. This creates a motion counteraction between the movement of the electron beam's target position and the movement of the X-ray tube's focal point, thereby compensating for the focal point's movement through the movement of the electron beam's target position. This ensures that at each scanning point, the focal point position of the X-ray tube remains within a preset range of the initial focal point position corresponding to the scanning point. Compared to the traditional method where the equivalent focal window continuously enlarges due to focal point movement, leading to a decrease in spatial resolution, the method proposed in this application can control the focal point position to remain unchanged or undergo only minor changes at each scanning point. That is, the size of the equivalent focal window remains unchanged or undergoes only minor changes, thereby improving the spatial resolution of the image scan and thus improving image quality. Attached Figure Description

[0031] To more clearly illustrate the technical solutions in the embodiments or related technologies of this application, the accompanying drawings used in the description of the embodiments or related technologies will be briefly introduced below. Obviously, the accompanying drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0032] Figure 1 This is a diagram illustrating the application environment of a medical imaging method in one embodiment;

[0033] Figure 2 This is a flowchart illustrating a medical imaging method in one embodiment;

[0034] Figure 3This is a schematic diagram of a rotating scanning process performed by an X-ray tube in one embodiment;

[0035] Figure 4(a) is a schematic diagram of the structure of the X-ray tube in one embodiment;

[0036] Figure 4(b) is a schematic diagram of the movement of the X-ray tube focus in one embodiment;

[0037] Figure 5 This is a schematic diagram comparing the equivalent focus window of the conventional technique and the focusless technology using the present application in one embodiment;

[0038] Figure 6 This is a flowchart illustrating a medical imaging method in another embodiment;

[0039] Figure 7 This is a schematic diagram illustrating electron beam adjustment via a gate in one embodiment;

[0040] Figure 8 This is a flowchart illustrating a medical imaging method in another embodiment;

[0041] Figure 9 This is a flowchart illustrating a medical imaging method in another embodiment;

[0042] Figure 10 This is a structural block diagram of a medical imaging device in one embodiment;

[0043] Figure 11 This is an internal structural diagram of a computer device in one embodiment. Detailed Implementation

[0044] To make the objectives, technical solutions, and advantages of this application clearer, the following detailed description is provided in conjunction with the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the scope of this application.

[0045] Currently, breast disease examinations and early breast cancer screening are mainly performed using mammography or breast ultrasound. The principle of mammography is the same as other X-ray equipment in terms of exposure. Traditional mammography machines primarily utilize the penetrating power of X-rays and the differences in how different tissues react to X-rays during penetration. Finally, by accumulating different energies, different levels of grayscale are generated on the image (including two-dimensional and three-dimensional tomographic imaging). Three-dimensional tomographic imaging obtains projection data from different angles by rotating the X-ray tube, and then reconstructs the final tomographic image.

[0046] However, as is well known, for 3D breast tomography, the velocity of the X-ray tube focal spot multiplied by its movement time equals the distance traveled by the X-ray tube focal spot, and the equivalent focal window is equal to the convolution of the focal spot size and the distance traveled by the X-ray tube focal spot. For some individuals with thick breast tissue, the system's spatial resolution is limited to the X-ray tube end, not the detector end. Therefore, the system's spatial resolution suffers a significant loss. How to improve spatial resolution, and thus image quality, has become an urgent technical problem to be solved.

[0047] Based on this, the embodiments of this application propose a medical imaging method that can be applied to medical imaging with limited angle scanning, such as mammography and digital X-ray photography, thereby improving spatial resolution and image quality.

[0048] The medical imaging method provided in this application embodiment can be applied to, for example... Figure 1 The application environment shown. Among them, the medical imaging equipment 102 can be a medical imaging equipment with limited angle scanning, including but not limited to mammography, digital X-ray imaging, etc.

[0049] In one exemplary embodiment, such as Figure 2 As shown, a medical imaging method is provided, which is applied to... Figure 1 Taking medical imaging equipment as an example, the explanation includes the following steps 202 to 206. Wherein:

[0050] Step 202: Obtain the motion information of the X-ray tube during the rotational scanning process of the medical imaging equipment.

[0051] Taking a mammography machine as an example, refer to Figure 3 The diagram illustrates a rotational scanning process using a mammography machine. During 3D tomography, the X-ray tube in the machine rotates around the detector, scanning the object within a certain scanning angle range—that is, scanning the object at multiple different scanning angles. Typically, the X-ray tube rotates to different scanning angles, and at each angle, the object is scanned for a preset duration. Simultaneously, the detector acquires the raw scan data (also known as raw scan data) of the object at each scanning angle.

[0052] Typically, when the X-ray tube rotates to a certain scanning angle for a preset scanning time, it continues to rotate at a constant speed. Therefore, during the preset scanning time at a certain scanning angle, the X-ray tube remains in motion, and its focal position may change. Referring to Figure 4(a), the X-ray tube includes a cathode filament and a rotating anode target. The electron beam emitted by the cathode filament irradiates the target surface of the rotating anode target. The focal position of the X-ray tube is the target position of the electron beam on the anode target surface. During the rotational scanning process, the target position of the electron beam may change, that is, the focal position of the X-ray tube will change. For example, at a certain scanning angle, from the start of the scan to the end of the scan, the focal position of the X-ray tube moves from position a on the anode target surface to position b. Here, position a is the initial focal position corresponding to the start of the scan at that scanning angle, and position b is the focal position corresponding to the end of the scan at that scanning angle. At this time, the equivalent focal window of the X-ray tube is the union of the focal size at position a and the focal size at position b, as shown in Figure 4(b). The black box is the initial focal position a corresponding to the start of the scan at that scanning angle. During the rotational scan, the focal point will translate along one direction. The equivalent focal window is the union of the initial focal position corresponding to the start of the scan at that scanning angle and the focal position after each translation. That is, the convolution of the focal size and the movement distance of the X-ray tube focal point during the scan at that scanning angle. Compared with the focal window at position a (i.e., the focal size at position a), the equivalent focal window is larger at position b. In other words, during the rotational scan, the equivalent focal window corresponding to the scanning angle will increase, which will correspondingly reduce the spatial resolution of the scanned image at the scanning angle.

[0053] In this embodiment, acquiring the motion information of the X-ray tube during rotational scanning of the medical imaging equipment can refer to the motion information of the focal point of the X-ray tube during rotational scanning, which may include the motion speed and motion time of the focal point. It should be noted that the motion information of the focal point can refer to the motion information of the focal point corresponding to a certain scanning angle. The motion speed of the focal point can be the motion speed of the X-ray tube as it rotates along the gantry, and the motion time of the focal point can be the scanning duration of the X-ray tube at a certain scanning angle, that is, the scanning duration from the start time to the end time of the scan at a certain scanning angle. Based on the motion information of the X-ray tube's focal point, the motion distance of the focal point can be calculated, that is, the distance between the initial focal position corresponding to the start time of the scan and the focal position corresponding to the end time of the scan at a certain scanning angle. Based on this motion distance, reverse motion compensation can be performed, that is, motion compensation is performed in the opposite direction of the focal point motion, so that when rotating scanning at that scanning angle, the focal position always remains near the initial focal position corresponding to the start time of the scan. This reduces the size of the equivalent focal window at each scanning angle during rotational scanning, thereby improving the spatial resolution of each scanning angle.

[0054] For example, medical imaging equipment can acquire motion information of the X-ray tube, including but not limited to the motion time and velocity of the X-ray tube. Then, based on the motion information of the X-ray tube, the motion information of the focal point in the X-ray tube can be determined. For example, the motion information of the focal point in the X-ray tube can be inferred from the motion information of the X-ray tube based on the motion correlation between the X-ray tube and the focal point in the X-ray tube.

[0055] Step 204: Adjust the target position of the electron beam in the X-ray tube according to the motion information of the X-ray tube, so that the focal position of the X-ray tube is within the preset range of the initial focal position corresponding to each scanning point when rotating the scan.

[0056] Rotational scanning refers to the X-ray tube rotating within a certain range so that the detector can acquire raw scan data at different scanning angles within that range. Each scanning point can be represented by a scanning angle of the X-ray tube. For example, with a rotation range of 0-30°, assuming data is acquired every 5°, the scanning points could be 0°, 5°, 10°, 15°, 20°, 25°, and 30°. That is, when the X-ray tube is at 0°, the detector acquires the raw scan data of the object at 0°; when the X-ray tube rotates to 5°, the detector acquires the raw scan data of the object at 5°, and so on. In other words, when the X-ray tube rotates to each scanning point, the detector acquires the raw scan data at that scanning point.

[0057] As the X-ray tube rotates, its focal point changes, causing it to continuously move in parallel along the same direction as it rotates, as shown in Figure 4(b). This direction of focal point movement can be referred to as the travel direction of the focal point. For example, before rotating to each scanning point, such as between the previous and next scanning points, or near the next scanning point, the medical imaging device can adjust the electron beam's target position in the X-ray tube based on the tube's motion information at the next scanning point. This ensures the focal point is within a preset range of the initial focal point position at the next scanning point. The initial focal point position can refer to the electron beam's target position at the start of the scanning at each scanning point, i.e., the focal point position at the start of the scanning at each scanning point. It should be noted that the focal point position refers to the position of the focal point relative to the X-ray tube.

[0058] For example, when the focal position of the X-ray tube moves parallel to the travel direction of the focal point, before rotating to each scanning point, the medical imaging equipment can adjust the target position of the electron beam in the X-ray tube, so that the target position moves in the opposite direction of the travel direction of the focal point. That is, the target position of the electron beam is adjusted to move parallel to the opposite direction of the travel direction of the focal point, while the focal position moves along the travel direction of the focal point. The two directions of movement are complementary, which can keep the focal position of the X-ray tube near the initial focal position of the X-ray tube corresponding to each scanning point. Even during the scanning process of each scanning point, the focal position of the X-ray tube always coincides with the initial focal position of the X-ray tube corresponding to each scanning point. In this way, during the rotational scanning process, the equivalent focal window corresponding to each scanning point can be kept at approximately the same size as the initial focal window of the corresponding scanning point, avoiding the enlargement of the equivalent focal window, thereby improving the spatial resolution of the image scanning.

[0059] It should be noted that during the rotational scanning process, the initial focal position of the X-ray tube should be different at each scanning point. For each scanning point, when performing reverse motion compensation, it is only necessary to ensure that the focal position is always near the initial focal position corresponding to that scanning point.

[0060] refer to Figure 5 As shown, it can be clearly seen that at each scanning point, after reverse motion compensation, the equivalent focal window of the X-ray tube during the rotational scanning process is always almost consistent with the focal window of the initial focal position corresponding to the scanning point. The smaller the size of the equivalent focal window, the higher the corresponding scanning spatial resolution. This not only improves the image resolution at each scanning point, but also improves the resolution of the overall three-dimensional tomographic image.

[0061] For example, taking a single scanning point as an example, when adjusting the target position of the electron beam in the X-ray tube to move in the opposite direction of the focal point's travel direction, the distance the focal point of the X-ray tube moves in its travel direction can be determined based on the motion information of the focal point. Then, the target position of the electron beam in the X-ray tube is also adjusted to move by the same distance in the opposite direction of the focal point's travel direction, achieving motion countermeasure, thereby ensuring that the focal point position of the X-ray tube is always within the preset range of the initial focal point position. For example, when the focal point position moves downward by 1mm, the target position of the electron beam can be adjusted to move upward by 1mm. This ensures that the focal point position of the X-ray tube does not change or changes only slightly at that scanning point.

[0062] Step 206: Perform medical imaging scanning based on the X-ray tube after the focal position is adjusted.

[0063] For example, before rotating to each scanning point, the target position of the electron beam of the X-ray tube is adjusted to counteract the movement of the focal position, so that the focal position of the X-ray tube is always within the preset range of the initial focal position corresponding to each scanning point. Based on this, at each scanning point, after adjusting the target position of the electron beam of the X-ray tube, a line scan can be performed. That is, the X-ray signal emitted by the X-ray tube after the focal position is adjusted can be collected by the detector after passing through the scanned object, thereby obtaining the original scan data of the scanned object at that scanning point.

[0064] Medical imaging equipment can reconstruct images based on the raw scan data of each scan point, ultimately obtaining a tomographic image of the scanned object.

[0065] In the aforementioned medical imaging method, during rotational scanning, the medical imaging equipment can acquire the motion information of the X-ray tube during the rotational scanning process, and adjust the target position of the electron beam in the X-ray tube according to the motion information of the X-ray tube, so that the focal position of the X-ray tube is within the preset range of the initial focal position corresponding to each scanning point in the rotational scanning; and then perform medical imaging scanning based on the X-ray tube after the focal position is adjusted. In other words, the medical imaging method proposed in this application allows the medical imaging equipment to adjust the target position of the electron beam in the X-ray tube based on the motion information of the X-ray tube during rotational scanning. This creates a motion counteraction between the movement of the electron beam's target position and the movement of the X-ray tube's focal point, thereby compensating for the focal point's movement through the movement of the electron beam's target position. This ensures that at each scanning point, the focal point position of the X-ray tube remains within a preset range of the initial focal point position corresponding to the scanning point. Compared to the traditional method where the equivalent focal window continuously enlarges due to focal point movement, leading to a decrease in spatial resolution, the method proposed in this application can control the focal point position to remain unchanged or undergo only minor changes at each scanning point. That is, the size of the equivalent focal window remains unchanged or undergoes only minor changes, thereby improving the spatial resolution of the image scan and thus improving image quality.

[0066] In an exemplary embodiment, the adjustment of the electron beam's target position can be achieved by changing the direction of the electron beam. One implementation involves applying a bias voltage to a gate to adjust the electron beam's direction, wherein the gate can be positioned between the anode and cathode of the X-ray tube. Based on this, as... Figure 6 As shown, step 204 above may include steps 602 to 604. Wherein:

[0067] Step 602: Determine the target bias voltage based on the motion information of the X-ray tube.

[0068] The target bias voltage is the voltage applied to the grid in the X-ray tube. As shown in Figure 4(a), the X-ray tube includes a cathode filament and an anode target. A grid is positioned between the cathode filament and the anode target, at a predetermined distance from their central axes. When a certain bias voltage is applied to the grid, the direction of the electron beam emitted by the cathode filament is biased, thereby shifting the position of the electron beam hitting the anode target. It should be noted that the position of the grid can be related to the direction of the focal point movement. When the focal point moves to the left, the position of the grid should be such that applying a bias voltage to the grid can control the electron beam's target position to move to the right. This shift in the target position can compensate for the focal point's movement, thereby reducing the size of the equivalent focal window and improving spatial resolution.

[0069] For example, when a medical imaging device acquires the motion information of the X-ray tube, it can determine the target bias voltage corresponding to the motion information of the X-ray tube based on the correspondence between different motion information of the X-ray tube and different bias voltages. Alternatively, it can first determine the motion information of the focal point in the X-ray tube based on the motion information of the X-ray tube, and then determine the target bias voltage corresponding to the motion information of the focal point based on the correspondence between different motion information of the focal point and different bias voltages. Accordingly, this target bias voltage is also the bias voltage corresponding to the motion information of the X-ray tube.

[0070] Step 604: Apply a target bias voltage to the grid in the X-ray tube to bias the electron beam in the opposite direction of the focal point movement of the X-ray tube, so as to adjust the target position of the electron beam in the X-ray tube.

[0071] It should be noted that the direction of movement of the focal point can also be called the direction of travel of the focal point.

[0072] For example, before the X-ray tube rotates to the next scanning point, such as a preset position before rotating to the next scanning point (assuming the next scanning point is 15°), the focus position can be corrected when rotating to 13° or 14°. When correcting the focus position, the target bias voltage applied to the X-ray tube gate can be determined based on the movement information of the X-ray tube focus, and the target bias voltage is applied to the X-ray tube gate when the X-ray tube rotates to 13° or 14°. When the target bias voltage is applied to the gate in the X-ray tube, the direction of the electron beam will be biased under the interference of the target bias voltage. In this example, it is desirable that the electron beam can be biased in the opposite direction to the movement of the X-ray tube focus, so that the movement of the electron beam can counteract the movement of the focus, so that after adjusting the target position of the electron beam, the movement of the focus can be compensated, thereby ensuring that the focus position does not change.

[0073] For example, refer to Figure 7As shown, taking a horizontal position for the cathode filament and anode target, assuming that at a certain scanning point, from the start to the end of the scan, the focal position of the X-ray tube moves downward at a constant speed, a certain bias voltage can be applied to the gate located below the midpoint between the cathode filament and the anode target. This allows the electron beam to be biased upward, thus allowing the electron beam's target position on the anode target surface to move upward, counteracting the downward movement of the focal position. This ensures that the focal position at that scanning point remains unchanged, that is, that the equivalent focal window at that scanning point is consistent with the focal window corresponding to the initial focal position at that scanning point. Alternatively, assuming that at a certain scanning point, from the start to the end of the scan, the focal position of the X-ray tube moves upward, a certain bias voltage can be applied to the gate located above the midpoint between the cathode filament and the anode target. This allows the electron beam to be biased downward, thus allowing the electron beam's target position on the anode target surface to move downward, counteracting the upward movement of the focal position. This ensures that the focal position at that scanning point remains unchanged, that is, that the equivalent focal window at that scanning point is consistent with the focal window corresponding to the initial focal position at that scanning point. The magnitude of the bias voltage is related to the motion information of the X-ray tube, that is, to the motion information of the focal point in the X-ray tube.

[0074] In this embodiment, the medical imaging equipment determines the target bias voltage of the gate in the X-ray tube based on the movement information of the X-ray tube, and applies the target bias voltage to the gate in the X-ray tube, so that the electron beam is biased in the opposite direction of the movement direction of the focal point of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube. In this way, the target position of the electron beam can move in the opposite direction of the movement direction of the focal point to ensure that the focal position at each scanning point does not change significantly, and avoids the increase of the equivalent focal window at each scanning point. By using this method, the spatial resolution of image scanning can be improved, thereby improving image quality.

[0075] In an exemplary embodiment, the motion information of the X-ray tube may include the motion speed of the X-ray tube's focal point and the motion time of the focal point, wherein the motion speed of the focal point may be the rotational speed of the X-ray tube, and the motion time of the focal point may be the scanning duration from the start to the end of the scan at the scanning point; such as Figure 8 As shown, step 602 above may include steps 802 to 804. Wherein:

[0076] Step 802: Determine the target movement distance of the focus during the rotational scanning process based on the movement speed and movement time of the focus.

[0077] The motion speed and motion time of the focal point can be the motion speed and motion time of the focal point when scanning at each scanning point.

[0078] For example, before the X-ray tube rotates to each scanning point, the medical imaging device can determine the target movement distance of the focal position after movement at the scanning point relative to the initial focal position of the scanning point, based on the movement speed and movement time of the focal point corresponding to that scanning point.

[0079] Step 804: Determine the target bias voltage corresponding to the target moving distance based on the preset correspondence between the moving distance and the bias voltage.

[0080] For example, the preset correspondence between the moving distance and the bias voltage can be a conversion relationship between the moving distance and the bias voltage. This correspondence can also include the correspondence between different moving distances and different bias voltages. For example, the moving distance and the bias voltage can be positively correlated, that is, the larger the moving distance, the larger the corresponding bias voltage, which means the larger the offset voltage applied to the gate, and the greater the bias of the electron beam emitted by the X-ray tube. This ensures that the bias of the electron beam and the movement of the X-ray tube focal point counteract each other, so that the focal position of the X-ray tube remains unchanged during the imaging scanning process at the scanning point (i.e., during the exposure process), thereby avoiding the degradation of image quality and improving the imaging resolution.

[0081] When a medical imaging device determines the target movement distance of the focal point at a scanning point based on its movement speed and time, it can determine a target bias voltage corresponding to that target movement distance according to a preset correspondence. This target bias voltage causes the electron beam's target position to shift in the opposite direction of the focal point's movement by that target movement distance, thereby creating a motion counteracting the focal point's movement and ultimately keeping the focal point position at the scanning point within a preset range of the initial focal point position at that scanning point.

[0082] In this embodiment, the medical imaging device first determines the target movement distance of the focal point during the rotational scanning process based on the movement speed and movement time of the focal point. Then, based on the preset correspondence between the movement distance and the bias voltage, it determines the target bias voltage corresponding to the target movement distance. By applying the target bias voltage to the gate of the X-ray tube, the direction of the electron beam can be biased in the opposite direction of the focal point movement. That is, the movement of the electron beam's target position counteracts the movement of the focal point position, ultimately ensuring that the focal point position remains unchanged during the scanning process of each scanning point, thereby improving spatial resolution and thus improving image quality.

[0083] In one exemplary embodiment, the target position of the electron beam is adjusted by changing the direction of the electron beam. In another implementation, the direction of the electron beam can also be adjusted by a magnetic bias coil, which can be positioned between the anode and cathode of the X-ray tube. Based on this, as... Figure 9As shown, step 204 above may include steps 902 to 904. Wherein:

[0084] Step 902: Determine the target bias current based on the motion information of the X-ray tube.

[0085] The target bias current can be the current applied to the magnetic bias coil in the X-ray tube. Similar to the gate setup described above, a magnetic bias coil can be placed between the cathode filament and the anode target of the X-ray tube. By applying different magnitudes of bias current to the magnetic bias coil, the bias direction of the electron beam can be changed, causing the electron beam's target position to shift by different distances.

[0086] For example, the medical imaging device can pre-acquire a first correspondence between different motion information of the X-ray tube and different bias currents of the magnetic bias coil, or a second correspondence between different offset distances of the electron beam's target position (i.e., the movement distance of the focal point in the X-ray tube) and different bias currents of the magnetic bias coil; then, before the X-ray tube moves to each scanning point, the target bias current applied to the magnetic bias coil can be determined based on the motion information of the X-ray tube at the scanning point and the first correspondence; or, the movement distance of the focal point can be determined based on the motion information of the X-ray tube at the scanning point, wherein the movement distance of the focal point is the offset distance of the electron beam's target position, and then, the target bias current applied to the magnetic bias coil can be determined based on the offset distance of the electron beam's target position and the second correspondence.

[0087] It should be noted that the moving distance and the bias current can also be positively correlated, that is, the greater the moving distance, the greater the corresponding bias current.

[0088] Step 904: Apply a target bias current to the magnetic bias coil of the X-ray tube to bias the electron beam in the opposite direction to the movement direction of the focal point of the X-ray tube, so as to adjust the target position of the electron beam in the X-ray tube.

[0089] For example, before the X-ray tube moves to the scanning point, a target bias current corresponding to the scanning point can be applied to the magnetic bias coil of the X-ray tube, thereby causing the electron beam to be biased in the opposite direction of the movement direction of the focal point of the X-ray tube, so as to adjust the target position of the electron beam in the X-ray tube; the target position of the biased electron beam forms a motion counteraction with the movement of the focal point in the rotational scanning, so that the focal point formed at the scanning point is always at the initial focal position corresponding to the scanning point.

[0090] In this embodiment, by setting a magnetic bias coil in the X-ray tube and applying a target bias current that matches the motion information of the X-ray tube to the magnetic bias coil, the electron beam of the X-ray tube is biased to a certain extent under the influence of the magnetic bias coil. This ensures that at each scanning point, the focal position of the X-ray tube is always at the initial focal position corresponding to each scanning point, avoiding the problem of reduced spatial resolution caused by the increase in the size of the equivalent focal window during rotational scanning, improving the spatial resolution of rotational scanning, and thus improving the image quality of three-dimensional tomographic imaging.

[0091] In an exemplary embodiment, the medical imaging device may determine a corresponding target bias voltage based on the motion information of the focal spot at each scanning point before rotating to each scanning point, or before performing imaging scanning at each scanning point. This target bias voltage is then applied to the gate of the X-ray tube, adjusting the focal spot position to the initial focal spot position before scanning at that point. Under the adjusted focal spot position, the device acquires raw scanning data at that scanning point using a detector. Exemplarily, the medical imaging device may also restore the electron beam's target position during non-scanning periods of rotational scanning, such as the period between completing a scan at a scanning point and moving to the next scanning point. After restoring the electron beam's target position, the focal spot position of the X-ray tube changes with the movement of the X-ray tube.

[0092] In other words, after data acquisition at a certain scanning point is completed, the target bias voltage applied to the gate can be canceled, thereby restoring the initial projection direction of the electron beam, i.e., restoring the target position of the electron beam. It should be noted that during the rotational scanning process, when the projection direction of the electron beam remains unchanged, the focal position formed by the electron beam on the anode target surface will shift. Therefore, when no bias voltage is applied to the gate, the target position of the electron beam will change with the rotation of the X-ray tube.

[0093] For example, before rotating to the current scanning point, the medical imaging device can first restore the initial projection direction of the electron beam, that is, cancel the target bias voltage applied to the gate; then, based on the movement speed and movement time of the focal point corresponding to the current scanning point, calculate the target movement distance of the focal point corresponding to the current scanning point, and determine the target bias voltage corresponding to the target movement distance; then, apply the target bias voltage corresponding to the target movement distance at the current scanning point to the gate, so that after the electron beam is biased in the opposite direction of the movement direction of the focal point, the target position of the electron beam moves the target movement distance in the opposite direction of the movement direction of the focal point, so that the focal position of the X-ray tube at the current scanning point is within a preset range of the initial focal position corresponding to the current scanning point; furthermore, after adjusting the bias direction of the electron beam, control the detector to start collecting the original scanning data passing through the scanning object at the current scanning point.

[0094] In other words, before rotating to each scanning point, the initial target position of the electron beam can be restored first. Then, the target bias voltage corresponding to the motion information of the focal point at the scanning point is determined and applied to the gate. This can improve the countermeasure accuracy at each scanning point, so that the focal position of the X-ray tube at each scanning point falls on the initial focal position corresponding to each scanning point, improve the spatial resolution of the entire rotational scan, and thus improve the quality of the reconstructed image.

[0095] In one exemplary embodiment, the medical imaging device may be a medical imaging device that performs limited-angle tomographic scanning, including but not limited to mammography X-ray imaging devices, dual-energy or multi-energy digital three-dimensional mammography tomography devices, mammography X-ray and ultrasound fusion imaging devices, digital X-ray imaging devices, etc.

[0096] For example, the technique described above, which controls the focal point to move in the opposite direction of the travel direction during rotational scanning by using a gate or magnetic bias coil, thereby reducing the equivalent focal window (or equivalent focal size) and improving spatial resolution, can be called a flying focal technique. In this embodiment, the flying focal technique can be applied to a medical imaging device performing limited-angle tomography. The medical imaging device may include an X-ray tube employing this flying focal technique. The device controller of the medical imaging device can collect the motion information of the X-ray tube during rotational scanning and send the motion information of the X-ray tube to the X-ray tube controller, so that the X-ray tube controller can adjust the bias voltage or magnetic bias line of the gate in the X-ray tube according to the motion information of the X-ray tube. The bias current of the coil is adjusted and controlled to first remove the bias voltage applied to the gate or the bias current of the magnetic bias coil at each scanning point. Then, based on the movement information of the X-ray tube at the scanning point, the target bias voltage of the gate or the target bias current of the magnetic bias coil is determined. Subsequently, the target bias voltage corresponding to the scanning point is applied to the gate, or the target bias current corresponding to the scanning point is applied to the magnetic bias coil. This allows the direction of the electron beam to be biased under the influence of the gate or the magnetic bias coil, thereby causing the target position of the electron beam to move in the opposite direction of the focal point's travel direction. This achieves motion counteraction against the focal point movement, reduces the equivalent focal point size at the scanning point, and improves the scanning spatial resolution of the scanning point.

[0097] Using this femtofocus technology can not only improve spatial resolution but also shorten the acquisition time of tomographic scans, indirectly reduce motion artifacts caused by patient movement, and further improve image quality.

[0098] For example, for dual-energy or multi-energy digital breast tomography (DBT) scanning, there are currently problems such as motion artifacts caused by the long scanning time of dual-energy subtraction DBT and low spatial resolution caused by the large equivalent focal size. Based on this, the flying focal technique proposed in the embodiments of this application can be integrated with dual-energy or multi-energy DBT scanning technology, which can greatly improve the acquisition and subtraction image effect of dual-energy or multi-energy DBT.

[0099] In addition, taking dual-energy DBT scanning as an example, when performing rotational scanning, high-energy scanning and low-energy scanning need to be performed separately. For example, high-energy rotational scanning can be performed first, and after completing the high-energy scanning at the preset scanning angle, low-energy rotational scanning can be performed. Alternatively, low-energy rotational scanning can be performed first, followed by high-energy rotational scanning. Or, high-energy scanning and low-energy scanning can be performed separately when rotating to each scanning point, thereby obtaining the high-energy scanning image and low-energy scanning image corresponding to each scanning point. Then, image subtraction can be performed on the high-energy scanning image and low-energy scanning image of each scanning point to obtain the subtracted image of each scanning point.

[0100] In dual-energy DBT scanning equipment, the introduction of flying focal spot technology not only improves spatial resolution but also ensures consistency between high-energy and low-energy spatial resolution. Typically, at the same scanning point, the equivalent focal window size for high-energy scanning differs from that for low-energy scanning. This results in different spatial resolutions for the high-energy and low-energy scan images at that point, affecting the quality of the resulting subtraction image. Related technologies address this by adjusting the ratio of X-ray quantity (mA) and exposure time (seconds) generated by the X-ray tube, ensuring that the high-energy and low-energy exposure times (seconds) are the same. This ensures that the equivalent focal window sizes for high-energy and low-energy scanning are identical, achieving consistency between high-energy and low-energy spatial resolution. When the resolutions of the two images are consistent, the quality of the subtraction image can be improved.

[0101] However, while this technique can ensure that the resolution of high-energy scanned images and low-energy scanned images at the same scan point is consistent, it still cannot avoid focus shift at the scan point. That is, the equivalent focal window at the scan point will still increase, resulting in a decrease in spatial resolution. However, by using the flying focus technique in this application, whether it is high-energy scanning or low-energy scanning, it can ensure that the size of the equivalent focal window at the scan point is consistent with the size of the focal window at the initial focal position corresponding to the scan point. This not only improves the spatial resolution, but also achieves consistency between high-energy and low-energy spatial resolution. This is because the high-energy equivalent focal window is the focal window at the initial focal position, and the low-energy equivalent focal window is also the focal window at the initial focal position. That is, the size of the high-energy window and the low-energy window are the same, and the resulting image resolution is naturally the same.

[0102] For example, for breast examinations, mammography can be fused with breast ultrasound imaging, or dual-energy or multi-energy DBT can be fused with breast ultrasound imaging, leveraging the inherent complementary advantages of ultrasound and X-ray diagnosis. This fusion device can also incorporate femtofocus technology to improve spatial resolution and thus image quality.

[0103] Breast ultrasound imaging works by scanning the breast with an ultrasound beam and processing the reflected signals to obtain an acoustic image of the breast. Three-dimensional ultrasound imaging, on the other hand, reconstructs a three-dimensional ultrasound image from a two-dimensional tomographic image of the breast through motion control, thus obtaining images in the coronal, sagittal, and transverse planes. In the differential diagnosis of breast masses, three-dimensional ultrasound imaging compensates for the limitations of two-dimensional ultrasound, providing more diagnostically significant coronal two-dimensional images. While mammography is the gold standard for early detection of breast hyperplasia, nodules, calcifications, and cancer, breast ultrasound imaging is superior in detecting structural lesions and glandular blood flow. Internationally, the most reliable clinical method for early diagnosis of breast cancer is to use both X-ray and ultrasound examinations, comparing the results to determine if a biopsy is necessary for confirmation. The main advantage of X-ray imaging is that it can identify details of lesions such as microcalcifications and detect potential breast lesions at an earlier stage. The disadvantage is that it requires greater pressure on the breast and it is difficult to see the complete image structure of the lesion tissue. Ultrasound imaging can clearly show the complete image structure of the lesion tissue, but it is more difficult to detect details of lesions such as microcalcifications.

[0104] To address this, this application also proposes a fusion imaging device for mammography combining X-ray and ultrasound. This fusion imaging device, during volumetric ultrasound examination, can perform array scanning of flexible ultrasound patch probes or motion-controlled scanning of a portion of the patch probes to complete volumetric ultrasound scanning and imaging. For example, the flexible ultrasound patch probe can be positioned between a compression plate and a substrate, adaptively adapting to the shape of the compressed breast based on the degree of compression exerted by the compression plate, thereby improving the ultrasound imaging effect on the compressed breast.

[0105] It should be noted that for this fusion imaging device, ultrasound examination can be performed first, followed by X-ray examination, or vice versa. Furthermore, during X-ray examination, the ultrasound probe can be moved out of the X-ray examination area to avoid interference with the X-ray examination and affecting the X-ray imaging quality.

[0106] For example, for a fusion imaging device, when different modal reconstructed images are acquired, image subtraction, registration, fusion and other processing operations can be performed on the different modal reconstructed images to obtain a fused reconstructed image after fusion processing, so as to carry out comprehensive processing and analysis of breast lesions in the future.

[0107] This application's embodiments, based on this novel flyfocal X-ray tube and combined with the clinical advantages of dual-energy or multi-energy mammography, constitute an advanced imaging system. This system achieves both the significantly improved spatial resolution of DBT (deep-focus transcranial Doppler) due to the use of flyfocal technology and rapid dual-energy or multi-energy tomographic imaging using this flyfocal X-ray tube. This technology can greatly improve the image resolution and detection rate of patient-specific lesions. Furthermore, by integrating ultrasound examination into the mammography system and performing inter-device fusion, a multimodal fusion device is formed. This fusion system possesses both high spatial resolution tomographic multi-energy subtraction imaging and fused ultrasound imaging, representing the future technological direction of mammography.

[0108] It should be understood that although the steps in the flowcharts of the embodiments described above are shown sequentially according to the arrows, these steps are not necessarily executed in the order indicated by the arrows. Unless explicitly stated herein, there is no strict order restriction on the execution of these steps, and they can be executed in other orders. Moreover, at least some steps in the flowcharts of the embodiments described above may include multiple steps or multiple stages. These steps or stages are not necessarily completed at the same time, but can be executed at different times. The execution order of these steps or stages is not necessarily sequential, but can be performed alternately or in turn with other steps or at least some of the steps or stages of other steps.

[0109] Based on the same inventive concept, this application also provides a medical imaging apparatus for implementing the medical imaging method described above. The solution provided by this apparatus is similar to the implementation described in the above method; therefore, the specific limitations in one or more medical imaging apparatus embodiments provided below can be found in the limitations of the medical imaging method described above, and will not be repeated here.

[0110] In one exemplary embodiment, such as Figure 10 As shown, a medical imaging device is provided, including: an acquisition module 1002, an adjustment module 1004, and an imaging module 1006, wherein:

[0111] The acquisition module 1002 is used to acquire the motion information of the X-ray tube during the rotational scanning process of the medical imaging equipment.

[0112] The adjustment module 1004 is used to adjust the target position of the electron beam in the X-ray tube according to the motion information of the X-ray tube, so that the focal position of the X-ray tube is within the preset range of the initial focal position corresponding to each scanning point during rotational scanning.

[0113] Imaging module 1006 is used for medical imaging scanning based on the X-ray tube after the focal position is adjusted.

[0114] In one embodiment, the adjustment module 1004 includes:

[0115] The first determining unit is used to determine the target bias voltage based on the motion information of the X-ray tube.

[0116] The first adjustment unit is used to apply a target bias voltage to the grid in the X-ray tube, so that the electron beam is biased in the opposite direction to the movement direction of the focal point of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube.

[0117] In one embodiment, the motion information of the X-ray tube includes the motion speed and motion time of the focal point of the X-ray tube. The first determining unit is used to determine the target moving distance of the focal point during the rotational scanning process based on the motion speed and motion time of the focal point; and to determine the target bias voltage corresponding to the target moving distance based on the preset correspondence between the moving distance and the bias voltage.

[0118] In one embodiment, the adjustment module 1004 further includes:

[0119] The second determining unit is used to determine the target bias current based on the motion information of the X-ray tube.

[0120] The second adjustment unit is used to apply a target bias current to the magnetic bias coil of the X-ray tube, so that the electron beam is biased in the opposite direction of the movement direction of the focal point of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube.

[0121] In one embodiment, the device further includes:

[0122] The recovery module is used to restore the electron beam's target position during non-scanning periods of the rotational scan.

[0123] In one embodiment, the medical imaging device is a medical imaging device that performs limited-angle tomography scans.

[0124] In one embodiment, the medical imaging equipment includes a mammography X-ray imaging device, a dual-energy or multi-energy digital three-dimensional tomography imaging device for the breast, a fusion imaging device for breast X-ray and ultrasound, and a digital X-ray imaging device.

[0125] The modules in the aforementioned medical imaging device can be implemented entirely or partially through software, hardware, or a combination thereof. These modules can be embedded in or independent of the processor in a computer device, or stored in the memory of a computer device as software, so that the processor can call and execute the operations corresponding to each module.

[0126] In one exemplary embodiment, a computer device is provided, which may be a medical imaging device, and its internal structure diagram may be as follows: Figure 11 As shown, the computer device includes a processor, memory, input / output interfaces, and a communication interface. The processor, memory, and input / output interfaces are connected via a system bus, and the communication interface is also connected to the system bus via the input / output interfaces. The processor provides computational and control capabilities. The memory includes non-volatile storage media and internal memory. The non-volatile storage media stores the operating system and computer programs. The internal memory provides an environment for the operation of the operating system and computer programs stored in the non-volatile storage media. The input / output interfaces are used for exchanging information between the processor and external devices. The communication interface is used for wired or wireless communication with external terminals or servers; wireless communication can be achieved through Wi-Fi, mobile cellular networks, NFC (Near Field Communication), or other technologies. When the computer program is executed by the processor, it implements a medical imaging method.

[0127] Those skilled in the art will understand that Figure 11 The structure shown is merely a block diagram of a portion of the structure related to the present application and does not constitute a limitation on the computer device to which the present application is applied. Specific computer devices may include more or fewer components than those shown in the figure, or combine certain components, or have different component arrangements.

[0128] In one exemplary embodiment, a computer device is provided, including a memory and a processor, wherein the memory stores a computer program, and the processor executes the computer program to perform the following steps:

[0129] Acquire information about the movement of the X-ray tube during rotational scanning in medical imaging equipment;

[0130] The target position of the electron beam in the X-ray tube is adjusted according to the motion information of the X-ray tube, so that the focal position of the X-ray tube is within the preset range of the initial focal position corresponding to each scanning point during the rotational scanning.

[0131] Medical imaging scans are performed using an X-ray tube with the focal position adjusted.

[0132] In one embodiment, the processor, when executing a computer program, also performs the following steps:

[0133] Determine the target bias voltage based on the motion information of the X-ray tube;

[0134] A target bias voltage is applied to the grid in the X-ray tube to bias the electron beam in the opposite direction to the movement direction of the focal point of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube.

[0135] In one embodiment, the motion information of the X-ray tube includes the velocity and time of motion of the focal point of the X-ray tube, and the processor, when executing the computer program, also performs the following steps:

[0136] The target movement distance during the rotational scanning process is determined based on the focal point's movement speed and movement time.

[0137] Based on the preset correspondence between the moving distance and the bias voltage, the target bias voltage corresponding to the target moving distance is determined.

[0138] In one embodiment, the processor, when executing a computer program, also performs the following steps:

[0139] Determine the target bias current based on the motion information of the X-ray tube;

[0140] A target bias current is applied to the magnetic bias coil of the X-ray tube to bias the electron beam in the opposite direction of the focal point movement of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube.

[0141] In one embodiment, the processor, when executing a computer program, also performs the following steps:

[0142] During the non-scanning period of the rotational scan, the target position of the electron beam is restored.

[0143] In one embodiment, the medical imaging device is a medical imaging device that performs limited-angle tomography scans.

[0144] In one embodiment, the medical imaging equipment includes a mammography X-ray imaging device, a dual-energy or multi-energy digital three-dimensional tomography imaging device for the breast, a fusion imaging device for breast X-ray and ultrasound, and a digital X-ray imaging device.

[0145] In one embodiment, a computer-readable storage medium is provided having a computer program stored thereon, the computer program performing the following steps when executed by a processor:

[0146] Acquire information about the movement of the X-ray tube during rotational scanning in medical imaging equipment;

[0147] The target position of the electron beam in the X-ray tube is adjusted according to the motion information of the X-ray tube, so that the focal position of the X-ray tube is within the preset range of the initial focal position corresponding to each scanning point during the rotational scanning.

[0148] Medical imaging scans are performed using an X-ray tube with the focal position adjusted.

[0149] In one embodiment, when the computer program is executed by a processor, it also performs the following steps:

[0150] Determine the target bias voltage based on the motion information of the X-ray tube;

[0151] A target bias voltage is applied to the grid in the X-ray tube to bias the electron beam in the opposite direction to the movement direction of the focal point of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube.

[0152] In one embodiment, the motion information of the X-ray tube includes the velocity and time of motion of the focal point of the X-ray tube, and the computer program, when executed by the processor, also performs the following steps:

[0153] The target movement distance during the rotational scanning process is determined based on the focal point's movement speed and movement time.

[0154] Based on the preset correspondence between the moving distance and the bias voltage, the target bias voltage corresponding to the target moving distance is determined.

[0155] In one embodiment, when the computer program is executed by a processor, it also performs the following steps:

[0156] Determine the target bias current based on the motion information of the X-ray tube;

[0157] A target bias current is applied to the magnetic bias coil of the X-ray tube to bias the electron beam in the opposite direction of the focal point movement of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube.

[0158] In one embodiment, when the computer program is executed by a processor, it also performs the following steps:

[0159] During the non-scanning period of the rotational scan, the target position of the electron beam is restored.

[0160] In one embodiment, the medical imaging device is a medical imaging device that performs limited-angle tomography scans.

[0161] In one embodiment, the medical imaging equipment includes a mammography X-ray imaging device, a dual-energy or multi-energy digital three-dimensional tomography imaging device for the breast, a fusion imaging device for breast X-ray and ultrasound, and a digital X-ray imaging device.

[0162] In one embodiment, a computer program product is provided, including a computer program that, when executed by a processor, performs the following steps:

[0163] Acquire information about the movement of the X-ray tube during rotational scanning in medical imaging equipment;

[0164] The target position of the electron beam in the X-ray tube is adjusted according to the motion information of the X-ray tube, so that the focal position of the X-ray tube is within the preset range of the initial focal position corresponding to each scanning point during the rotational scanning.

[0165] Medical imaging scans are performed using an X-ray tube with the focal position adjusted.

[0166] In one embodiment, when the computer program is executed by a processor, it also performs the following steps:

[0167] Determine the target bias voltage based on the motion information of the X-ray tube;

[0168] A target bias voltage is applied to the grid in the X-ray tube to bias the electron beam in the opposite direction to the movement direction of the focal point of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube.

[0169] In one embodiment, the motion information of the X-ray tube includes the velocity and time of motion of the focal point of the X-ray tube, and the computer program, when executed by the processor, also performs the following steps:

[0170] The target movement distance during the rotational scanning process is determined based on the focal point's movement speed and movement time.

[0171] Based on the preset correspondence between the moving distance and the bias voltage, the target bias voltage corresponding to the target moving distance is determined.

[0172] In one embodiment, when the computer program is executed by a processor, it also performs the following steps:

[0173] Determine the target bias current based on the motion information of the X-ray tube;

[0174] A target bias current is applied to the magnetic bias coil of the X-ray tube to bias the electron beam in the opposite direction of the focal point movement of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube.

[0175] In one embodiment, when the computer program is executed by a processor, it also performs the following steps:

[0176] During the non-scanning period of the rotational scan, the target position of the electron beam is restored.

[0177] In one embodiment, the medical imaging device is a medical imaging device that performs limited-angle tomography scans.

[0178] In one embodiment, the medical imaging equipment includes a mammography X-ray imaging device, a dual-energy or multi-energy digital three-dimensional tomography imaging device for the breast, a fusion imaging device for breast X-ray and ultrasound, and a digital X-ray imaging device.

[0179] It should be noted that the data involved in this application (including but not limited to data used for analysis, data stored, data displayed, etc.) are information and data that have been fully authorized by all parties, and the collection, use and processing of the relevant data must comply with relevant regulations.

[0180] Those skilled in the art will understand that all or part of the processes in the above embodiments can be implemented by a computer program instructing related hardware. The computer program can be stored in a non-volatile computer-readable storage medium. When executed, the computer program can include the processes of the embodiments described above. Any references to memory, databases, or other media used in the embodiments provided in this application can include at least one of non-volatile and volatile memory. Non-volatile memory can include read-only memory (ROM), magnetic tape, floppy disk, flash memory, optical memory, high-density embedded non-volatile memory, resistive random access memory (ReRAM), magnetic random access memory (MRAM), ferroelectric random access memory (FRAM), phase change memory (PCM), graphene memory, etc. Volatile memory can include random access memory (RAM) or external cache memory, etc. By way of illustration and not limitation, RAM can take many forms, such as Static Random Access Memory (SRAM) or Dynamic Random Access Memory (DRAM). The databases involved in the embodiments provided in this application may include at least one type of relational database and non-relational database. Non-relational databases may include, but are not limited to, blockchain-based distributed databases. The processors involved in the embodiments provided in this application may be general-purpose processors, central processing units, graphics processing units, digital signal processors, programmable logic devices, quantum computing-based data processing logic devices, etc., and are not limited to these.

[0181] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

[0182] The embodiments described above are merely illustrative of several implementation methods of this application, and while the descriptions are specific and detailed, they should not be construed as limiting the scope of this application. It should be noted that those skilled in the art can make various modifications and improvements without departing from the concept of this application, and these all fall within the protection scope of this application. Therefore, the protection scope of this application should be determined by the appended claims.

Claims

1. A medical imaging method, characterized by, The method includes: Acquire information about the movement of the X-ray tube during rotational scanning in medical imaging equipment; The target position of the electron beam in the X-ray tube is adjusted according to the motion information of the X-ray tube, so that the focal position of the X-ray tube is within the preset range of the initial focal position corresponding to each scanning point of the rotational scan. Medical imaging scans are performed using the X-ray tube after the focal position is adjusted.

2. The method according to claim 1, characterized in that, The step of adjusting the target position of the electron beam in the X-ray tube based on the motion information of the X-ray tube includes: The target bias voltage is determined based on the motion information of the X-ray tube; The target bias voltage is applied to the gate in the X-ray tube to bias the electron beam in the opposite direction to the movement direction of the focal point of the X-ray tube, so as to adjust the target position of the electron beam in the X-ray tube.

3. The method according to claim 2, characterized in that, The motion information of the X-ray tube includes the motion velocity and motion time of the focal spot of the X-ray tube. Determining the target bias voltage based on the motion information of the X-ray tube includes: The target movement distance of the focus during the rotational scanning process is determined based on the movement speed and movement time of the focus. Based on the preset correspondence between the moving distance and the bias voltage, the target bias voltage corresponding to the target moving distance is determined.

4. The method according to claim 1, characterized in that, The step of adjusting the target position of the electron beam in the X-ray tube based on the motion information of the X-ray tube includes: The target bias current is determined based on the motion information of the X-ray tube; The target bias current is applied to the magnetic bias coil of the X-ray tube, so that the electron beam is biased in the opposite direction to the movement direction of the focal point of the X-ray tube, thereby adjusting the target position of the electron beam in the X-ray tube.

5. The method according to any one of claims 1-4, characterized in that, The method further includes: During the non-scanning period of the rotational scan, the target position of the electron beam is restored.

6. The method according to any one of claims 1-4, characterized in that, The medical imaging equipment mentioned is a medical imaging equipment that performs limited-angle tomographic scanning.

7. The method according to claim 6, characterized in that, The medical imaging equipment includes mammography X-ray imaging equipment, dual-energy or multi-energy digital three-dimensional mammography equipment, mammography X-ray and ultrasound fusion imaging equipment, and digital X-ray imaging equipment.

8. A medical imaging device, characterized in that, The device includes: The acquisition module is used to acquire the motion information of the X-ray tube during the rotational scanning process of the medical imaging equipment; The adjustment module is used to adjust the target position of the electron beam in the X-ray tube according to the motion information of the X-ray tube, so that the focal position of the X-ray tube is within a preset range of the initial focal position at each scanning point of the rotational scan; An imaging module is used to perform medical imaging scans based on the X-ray tube after the focal position has been adjusted.

9. A computer device comprising a memory and a processor, wherein the memory stores a computer program, characterized in that, When the processor executes the computer program, it implements the steps of the method according to any one of claims 1 to 7.

10. A computer-readable storage medium having a computer program stored thereon, characterized in that, When the computer program is executed by a processor, it implements the steps of the method according to any one of claims 1 to 7.

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