Ultrasound transducer, ice probe and four-dimensional imaging device for 4D imaging

Abstract

The present disclosure provides an ultrasonic transducer, an ICE probe and a four-dimensional imaging device for 4D imaging. The ultrasonic transducer for 4D imaging comprises a control assembly, a linear array and a reflection structure provided with a rotating reflection inclined surface connected with the control assembly and oppositely arranged; the linear array comprises a plurality of array element structures arranged in different preset directions and independently working; the control assembly is used to drive the rotating reflection inclined surface to rotate; the control assembly is also used to drive a target array element structure matched with a target azimuth of the rotating reflection inclined surface to emit and receive ultrasonic signals according to the target azimuth at different acquisition time instants, so as to generate a corresponding cross-sectional image at each acquisition time instant, and the cross-sectional images at different acquisition time instants are synthesized to obtain a four-dimensional dynamic ultrasonic image; wherein different array element structures correspond to different azimuth ranges of the rotating reflection inclined surface. The four-dimensional dynamic ultrasonic image generated by the present disclosure can meet the medical needs of accurate examination of heart cavities.

Description

Technical Field

[0001] This disclosure relates to the field of medical device technology, and in particular to an ultrasound transducer, an ICE (intracardiac ultrasound) probe, and a four-dimensional imaging device for 4D imaging. Background Technology

[0002] Since the mid-20th century, two-dimensional ultrasound (2D echo ultrasound imaging) technology has been widely used in clinical practice, particularly in gynecology and obstetrics, as an important tool for medical diagnosis. It utilizes the principle of ultrasound reflection to generate two-dimensional images based on the characteristics of the reflected waves, providing doctors with an effective means of observing the structure of the fetus and internal organs. However, with the rapid development of medical technology, two-dimensional ultrasound has gradually revealed its limitations. For example, the observation effect is limited by the amount of amniotic fluid and the fetal position, it cannot directly display dynamic changes, and it is difficult to meet the growing demand for precision medicine.

[0003] To this end, researchers have made unremitting efforts over decades, achieving a breakthrough from exploring two-dimensional planar images to three-dimensional stereoscopic imaging at the end of the 20th century. In the early 21st century, four-dimensional ultrasound (4D ultrasound echo imaging) technology, incorporating the time dimension, was also born. Each step embodies the innovation and leap forward in medical imaging technology. Four-dimensional ultrasound technology not only retains the stereoscopic imaging advantages of three-dimensional ultrasound, but also, by introducing the time dimension, enables real-time observation of the internal organs of the human body and the dynamic activities of the fetus, providing unprecedented visual experience and information for clinical diagnosis.

[0004] Intracardiac echocardiography (ICE) is a branch of echocardiography. Current ICE techniques suffer from limited field of view during surgery due to the small probe size (outer diameter only 3mm, internal usable space only 1-2.5mm), making it impossible to design complex transducer oscillation mechanisms. This limits ICE probe-based four-dimensional imaging to research purposes. In current clinical practice, only three-dimensional imaging can be achieved, requiring manual operation by the physician, which compromises accuracy and prevents the realization of four-dimensional imaging, thus failing to meet clinical needs.

[0005] Existing 3D ICE (Internal Cardiac Imaging) devices require manual operation by a doctor to control the catheter to rotate as uniformly as possible within the heart chambers, acquiring and storing cross-sectional images from various directions. After one rotation, an algorithm combines the stored N cross-sectional images to form a 360-degree 3D image. The time required for this process varies depending on the doctor's skill level, ranging from approximately 10 seconds to 3 minutes. However, the natural heartbeat is 60-120 times per second (for patients), and in special cases, the heart rate can even reach 140 beats per second. Therefore, during the doctor's rotation, the size of the heart and the image are constantly changing. This leads to errors in cross-sectional alignment, unclear images, and even contradictory pixels. Even with special algorithms to judge and discard, the synthesized image may still appear blurry or cropped. Therefore, this type of 3D ICE device has significant limitations in practical use.

[0006] To achieve a 4D effect on ICE devices, existing technologies employ an ultra-high precision matrix method. This involves cutting 32*64=2048 array elements from the 2.5*10mm size of the ICE probe, then connecting over 4,000 lines within a space of less than 1mm via extremely fine wiring to the catheter cable. A self-designed chip select chip controls the activation time of each array element, thus forming a 4D functional ICE probe in dual-phase array mode. While this process achieves a 4D effect, it requires precise size control. Each array element is only 50*140 micrometers in size; if even one element is damaged during cutting, the entire transducer matrix is ​​rendered unusable. Furthermore, the need to route insulated ground and signal lines within this size while preventing crosstalk, coupled with the development and production costs of the high-voltage chip select chip, results in each disposable catheter probe costing tens of thousands of US dollars. This makes the price of each probe catheter far beyond the reach of ordinary patients. Therefore, such products have not been used in actual clinical practice and remain only in the research field.

[0007] Looking back at current conventional catheter-based endovascular ultrasound products, some designs use an external electric device to rotate the probe at a uniform speed, such as IVUS (intravascular ultrasound). In IVUS, a rotary transformer transmits the current and echo signals from the rotating single element to a stationary circuit board, where they are processed by an FPGA to obtain the ultrasound image. However, since ICE probes are multi-element transmitters and receivers, such as 64, 96, or 128 elements, achieving element rotation would require hundreds of leads to rotate simultaneously. To prevent these leads from breaking during rotation, hundreds of rotary transformers would be needed on a single axis to transmit the current from the rotating part to the stationary circuit board. This is impractical. Even with the smallest rotary transformer currently available, the axis alone would need to be 1-2 meters long, while the reasonable total length of the doctor's operating handle is only 20 centimeters, and the rotating axis is only about 5 centimeters long. Clearly, this design approach is not feasible for ICE probes.

[0008] Another method uses a rotating inclined plane at a constant angle to reflect focused ultrasound waves for scanning. For example, patent application CN201910610675.0 describes a system and method for intravascular ultrasound diagnosis. This patent achieves a 360-degree cross-section effect after the array elements move and rotate while the array elements are stationary through inclined plane reflection. However, since ICE (Intravascular Electron Microarray) uses multiple array elements to simultaneously emit multiple beams and receive echoes, and then calculates the spatial focusing of single or multiple points in the time dimension to form a phased array image, while the aforementioned patent is for imaging of a single array element beam, if the imaging method of the aforementioned patent is applied to four-dimensional imaging of ICE, distortion due to the disorder of the beam arrangement at different angles will result in a "high-dimensional saddle surface effect". Summary of the Invention

[0009] The technical problem to be solved by this disclosure is to overcome the shortcomings of existing ICE probes in clinical practice, which cannot achieve four-dimensional dynamic imaging to meet clinical needs, and to provide an ultrasound transducer, ICE probe and four-dimensional imaging device for 4D imaging.

[0010] This disclosure solves the above-mentioned technical problems through the following technical solution:

[0011] According to a first aspect of this disclosure, an ultrasonic transducer for 4D imaging is provided, the ultrasonic transducer including a control component, a linear array connected to and disposed opposite to the control component, and a reflective structure;

[0012] The linear array includes multiple Hall elements fixedly arranged at multiple different positions, and several array element structures arranged in different preset directions and operating independently. Each array element structure consists of several polarized array elements arranged in a straight line. The array element structure is used to transmit and receive ultrasonic signals.

[0013] The reflective structure is provided with a rotating reflective ramp and a magnetic element that rotates with the rotating reflective ramp;

[0014] The control component is used to send a first control command to the reflective structure to drive the rotating reflective ramp to rotate;

[0015] The control component is also used to send a second control command to the Hall element to drive the Hall element to detect the magnetic strength information of the magnetic element;

[0016] The control component is also used to determine the target orientation of the rotating reflective ramp based on the magnetic intensity information detected by each Hall element at different acquisition times, send a third control command to a target array element structure that matches the target orientation, drive the target array element structure to emit the ultrasonic signal, and receive the ultrasonic signal reflected by the rotating reflective ramp along a preset reflection path at the target orientation to generate a cross-sectional image corresponding to each acquisition time, and synthesize the cross-sectional images at different acquisition times to obtain a four-dimensional dynamic ultrasonic image;

[0017] The different array element structures correspond to different azimuth ranges of the rotating reflective inclined plane.

[0018] Preferably, the linear array is square, and the linear array includes four array element structures;

[0019] The four array elements are arranged in a cross shape.

[0020] Preferably, two Hall elements are disposed on each side of the linear array, and the two Hall elements are symmetrically arranged.

[0021] Preferably, the line connecting each Hall element to the center point of the linear array forms a predetermined angle with the adjacent array element structure.

[0022] Preferably, the ultrasonic transducer further includes a motor;

[0023] The reflective structure is connected to the rotor in the motor;

[0024] The motor is used to receive the first control command and drive the rotor to rotate, thereby causing the rotating reflective inclined plane in the reflective structure to rotate.

[0025] Preferably, the motor is further configured to receive the first control command and drive the rotor to rotate clockwise, thereby causing the rotating reflective inclined plane to rotate clockwise;

[0026] Preferably, the motor is further configured to receive the first control command and drive the rotor to rotate counterclockwise, thereby causing the rotating reflective inclined plane to rotate counterclockwise.

[0027] Preferably, the magnetic element includes a magnet.

[0028] According to a second aspect of this disclosure, an ICE probe for 4D imaging is provided, the ICE probe including a controller and an ultrasonic transducer for 4D imaging as described in the first aspect of this disclosure;

[0029] The controller is used to drive the control components of the ultrasonic transducer to acquire cross-sectional images at different acquisition times.

[0030] According to a third aspect of this disclosure, an ICE four-dimensional imaging device is provided, the ICE four-dimensional imaging device including a processor, a display communicatively connected to the processor, and an ICE probe for 4D imaging as described in the second aspect of this disclosure;

[0031] The processor is used to receive the cross-sectional images acquired by the ICE probe at different acquisition times, and to synthesize several cross-sectional images obtained by rotating the rotating reflective inclined plane once to obtain a stereoscopic image;

[0032] The processor is also configured to send the stereoscopic image obtained by each rotation of the rotating reflective ramp to the display.

[0033] The display is used to sequentially display the stereoscopic images according to the acquisition time to form a four-dimensional dynamic ultrasound image.

[0034] Based on common knowledge in the field, the above-mentioned preferred conditions can be combined arbitrarily to obtain various preferred embodiments of this disclosure.

[0035] The positive and progressive effects of this disclosure are as follows: by combining array element structures set in different directions and operating independently with rotating reflective inclined planes, the ultrasound waves emitted by the array element structures continuously pick up cross-sectional images around the catheter as the rotor rotates continuously. By combining multiple cross-sectional images picked up in each rotation, a ring-shaped three-dimensional ultrasound image for that rotation is obtained. As the rotor rotates rapidly and continuously, the three-dimensional ultrasound images for each rotation are presented sequentially according to time, forming a four-dimensional dynamic ultrasound image of the heart's interior that changes with the heartbeat, thereby meeting the medical needs for precise examination of the heart chambers. Attached Figure Description

[0036] Figure 1 This is a schematic diagram of the ultrasonic transducer structure for 4D imaging in Embodiment 1 of this disclosure;

[0037] Figure 2 This is a schematic diagram of the linear array structure in Embodiment 1 of this disclosure;

[0038] Figure 3This is a schematic diagram of the rotation state of the rotating reflective inclined plane in Embodiment 1 of this disclosure;

[0039] Figure 4 This is a schematic diagram of the cross-sectional imaging of the rotating reflective inclined plane in the a-position of Embodiment 1 of this disclosure;

[0040] Figure 5 This is a schematic diagram of the cross-sectional imaging of the rotating reflective inclined plane in the b-direction of Embodiment 1 of this disclosure;

[0041] Figure 6 This is a schematic diagram of the cross-sectional imaging of the rotating reflective inclined plane in the c-position of Embodiment 1 of this disclosure;

[0042] Figure 7 This is a schematic diagram of the cross-sectional imaging of the rotating reflective inclined plane in the d-position of Embodiment 1 of this disclosure;

[0043] Figure 8 This is a schematic diagram of the cross-sectional imaging of the rotating reflective inclined plane in the e-direction of Embodiment 1 of this disclosure;

[0044] Figure 9 This is a schematic diagram of the cross-sectional imaging of the rotating reflective inclined plane in the f-direction of Embodiment 1 of this disclosure;

[0045] Figure 10 This is a schematic diagram of the cross-sectional imaging of the rotating reflective inclined plane in the g-position of Embodiment 1 of this disclosure;

[0046] Figure 11 This is a schematic diagram of the cross-sectional imaging of the rotating reflective inclined plane in the h-position of Embodiment 1 of this disclosure;

[0047] Figure 12 This is a schematic diagram of the ICE probe structure for 4D imaging in Embodiment 2 of this disclosure. Detailed Implementation

[0048] The present disclosure is further illustrated below by way of embodiments, but the present disclosure is not limited to the scope of the embodiments described herein.

[0049] The prefixes such as "first" and "second" used in this disclosure are merely for distinguishing different descriptive objects and do not limit the position, order, priority, quantity, or content of the described objects. The use of ordinal numbers and other prefixes used to distinguish descriptive objects in this disclosure does not constitute a limitation on the described objects. The description of the described objects is given in the claims or the context of the embodiments, and should not be construed as an unnecessary limitation. Furthermore, in the description of this embodiment, unless otherwise stated, "multiple" means two or more.

[0050] Example 1

[0051] In one specific embodiment of this disclosure, an ultrasonic transducer 100 for 4D imaging is provided, such as... Figure 1-2 As shown, the ultrasonic transducer 100 includes a control component (not shown in the figure), a linear array 1 connected to the control component and disposed opposite to it, and a reflective structure 2.

[0052] The linear array 1 includes multiple Hall elements fixedly arranged at multiple different positions, and several array element structures set in different preset directions and operating independently. Each array element structure consists of several polarized array elements arranged in a straight line. The array element structure is used to transmit and receive ultrasonic signals.

[0053] The reflective structure 2 is provided with a rotating reflective inclined plane and a magnetic element 21 that rotates with the rotating reflective inclined plane;

[0054] The control component is used to send a first control command to the reflective structure 2 to drive the rotating reflective ramp to rotate;

[0055] The control component is also used to send a second control command to the Hall element to drive the Hall element to detect the magnetic strength information of the magnetic element 21;

[0056] The control component is also used to determine the target orientation of the rotating reflective ramp based on the magnetic intensity information detected by each Hall element at different acquisition times, send a third control command to a target array element structure that matches the target orientation, drive the target array element structure to emit ultrasonic signals, and receive the ultrasonic signals reflected by the rotating reflective ramp along a preset reflection path at the target orientation to generate a cross-sectional image corresponding to each acquisition time. The cross-sectional images at different acquisition times are synthesized to obtain a four-dimensional dynamic ultrasonic image.

[0057] Different array element structures correspond to different azimuth ranges of the rotating reflective slope.

[0058] Specifically, a polarization process is used to fabricate an array element structure in linear array 1, consisting of multiple polarized array elements arranged in a straight line, with each array element structure communicating with a control component (e.g., an FPGA host) via a cable to receive control commands from the control component and initiate operation. For example, for a circular linear array 1, multiple array elements located on the same diameter can be polarized to obtain array element structures; different diameters correspond to different array element structures, thus obtaining multiple array element structures. Similarly, for a square linear array 1, the array elements on the central horizontal line, central vertical line, and two diagonals can be polarized to obtain four different array element structures. The array element material can be piezoelectric ceramic. Each array element structure can independently transmit and receive ultrasonic signals under the drive of the control component, while unpolarized array elements do not have the function of transmitting or receiving ultrasonic signals.

[0059] The reflective structure 2 is positioned relative to the linear array 1. The reflective structure 2 has a rotating reflective ramp at a constant angle. The ultrasonic signal... The signal is emitted after being reflected by the rotating reflective ramp, and the echo signal reflected back by the human tissue is reflected back to the linear array 1 by the rotating reflective ramp. Different array element structures in the linear array 1 correspond to rotating reflective ramps with different azimuth ranges.

[0060] To enable the control components to identify the orientation of the rotating reflective ramp, Hall elements can be fixedly installed at different positions around the linear array 1. The number of Hall elements can be set according to actual needs. At the same time, a magnetic element 21 is installed on the reflective structure 2, and the Hall elements can detect the magnetic element 21 within a certain distance.

[0061] When the rotating reflective ramp rotates to different orientations, the Hall element located within a certain distance can detect the magnetic element 21. The Hall element sends the orientation information to the control component, which can then determine the target orientation of the rotating reflective ramp based on the position of the Hall element, thereby determining the target array element structure for transmitting and receiving ultrasonic signals.

[0062] When four-dimensional dynamic ultrasound imaging is required, the control component drives the rotating reflective ramp to rotate uniformly at a certain speed, and drives the Hall element to detect the magnetic intensity information of the magnetic element 21 to determine the target orientation of the rotating reflective ramp at different times. The control component determines the matching target array structure based on the orientation range of the rotating reflective ramp, and controls the target array structure to transmit and receive ultrasound signals. The ultrasound signal is reflected by the rotating reflective ramp and then transmitted. The echo signal reflected back by human tissue is also reflected by the rotating reflective ramp and received by the target array structure, thus obtaining a cross-sectional image of the heart cavity. Because the rotating reflective ramp rotates continuously, the ultrasound signal emitted by the target array structure is reflected by the rotating reflective ramp at different angles at different acquisition times, thus obtaining multiple cross-sectional images of the heart cavity at different angles within the corresponding orientation range.

[0063] When the target orientation of the rotating reflective ramp exceeds the orientation range corresponding to the current target array element structure, the control component controls another matching target array element structure to transmit and receive ultrasound signals, continue to acquire cross-sectional images of the heart cavity at different angles, and control the current target array element structure to stop transmitting ultrasound signals to avoid signal interference causing distortion of the "high-dimensional saddle surface effect" and ensure the accuracy of four-dimensional dynamic ultrasound imaging.

[0064] After the rotating reflection inclined plane rotates one week, multiple cross-sectional images collected can be synthesized through an algorithm to obtain a four-sided annular three-dimensional ultrasound image. Presenting the four-sided annular three-dimensional ultrasound images obtained every time it rotates one week in chronological order can obtain a four-dimensional dynamic ultrasound image.

[0065] In this specific embodiment, by arranging the array structures that work independently in different directions and cooperating with the rotating reflection inclined plane, the ultrasonic waves emitted by the array structures continuously pick up cross-sectional images around the catheter under the continuous rotation of the rotor. By combining multiple cross-sectional images picked up every time it rotates one week, a three-dimensional annular ultrasound image for this week is obtained. As the rotor rotates rapidly and continuously, the three-dimensional ultrasound images for each week are presented in sequence according to time, forming a four-dimensional dynamic ultrasound image that环视四周 of the heart and changes with the heartbeat, thus meeting the medical needs of precise examination of the heart cavity.

[0066] In a specific embodiment, as Figure 1-2 shown, the linear array 1 is square, and the linear array 1 includes four array structures;

[0067] The four array structures are arranged in a cross shape.

[0068] Specifically, taking the 19*19 linear array 1 as an example, four array structures of "cross-shaped" L1, L2, L3, and L4 are fabricated in the linear array 1 by using a polarization process, with a total of 73 polarized array elements. Among them, the polarized array elements correspond to the gray parts in the figure, and the unpolarized array elements correspond to the white parts in the figure.

[0069] Since the damage to the probe caused by the cutting of the unpolarized part has no impact, this "cross-shaped" array element process design reduces the scrap ratio after the array element is damaged by cutting. In theory, the scrap rate ratio = array element / cutting matrix = 73 / 361 ≈ 0.20 = 20%, that is, the scrap rate drops to one-fifth of the original. However, in actual production, because the cutting of the array element is in a manual control mode or a program control mode, when setting the manual or program control parameters, a micro-inclination method is adopted, that is, when cutting, one side of the cutting tool can be intentionally protected, and the risk is transferred to the other side. The polarized array elements are intentionally controlled and protected, and the useless array elements on the adjacent other side do not need to be cared about. Therefore, the damage rate of the polarized array elements during actual operation will be much lower than 20%. According to the conventional cutting method, in actual statistics, the scrap ratio is controlled to be less than 5% of the 4D array elements of the matrix, greatly improving the yield rate in production operations and equivalently reducing the material cost.

[0070] In a specific embodiment, as Figure 1-2 shown, two Hall elements are arranged on each side of the linear array 1, and the two Hall elements are symmetrically arranged. Preferably, the connection line between the center point of each Hall element and the linear array 1 forms a preset angle with the adjacent array structure.

[0071] Specifically, eight Hall elements A, B, C, D, E, F, G, and H are designed around the "rice-shaped" linear array 1. Two Hall elements are designed on each side of the quadrilateral. The angle between the line connecting the position of each Hall element to the center point of the linear array 1 and the adjacent array element structure is 22.5 degrees. For example, the angle between Hall element C and array element structure L2 is 22.5 degrees, and the angle between array element structure L2 and Hall element D is also 22.5 degrees. The angle between C and D is 45 degrees. Similarly, the angles between Hall element C and array element structure L1, and between Hall element D and array element structure L3 are also 22.5 degrees, and so on. Thus, the four array element structures divide the linear array 1 into eight different angles, each of which matches a different azimuth range of the rotating reflection inclined plane. By dividing the 360 degrees of a circle into eight 45-degree fan-shaped ranges, with the center of the linear array as the center of the acoustic resonance point, extending 22.5 degrees to both sides respectively, the action angle of each single linear array is narrow, effectively controlling the distortion of the high-dimensional saddle surface effect.

[0072] A magnetic element is embedded at the lower end of the back side of the reflection structure 2. Preferably, the magnetic element is a magnet, which is used to generate an electromagnetic field. When the rotating reflection inclined plane rotates, the magnetic intensities detected by Hall elements at different positions are different. Therefore, the azimuth of the rotating reflection inclined plane can be determined according to the magnetic intensity information detected by Hall elements A, B, C, D, E, F, G, and H, and then the matching target array element structure can be determined according to this azimuth.

[0073] In a specific example, as Figure 3 shown, a - h in the figure respectively represent eight states of the rotating reflection inclined plane when rotating clockwise. When the rotating reflection inclined plane is in the a azimuth, the magnetic intensities detected by Hall element E and Hall element F are the same. The control component can determine that the position of the magnet is between Hall element E and Hall element F according to the magnetic intensity information sent by Hall element E and Hall element F. The matching target array element structure is L4. Therefore, the control component drives the array element structure L4 to transmit and receive ultrasonic signals, and the tissue section diagram obtained by acquisition is as Figure 4As shown, multiple cross-sections at different angles are acquired as the rotating reflective ramp moves clockwise. When the rotating reflective ramp is in position b, the magnetic element is directly above the Hall element F. At this time, the magnetic intensity detected by the Hall element F is the strongest. The Hall elements E and G are equidistant from the magnetic element and detect the same magnetic intensity information. However, the magnetic intensity detected by the Hall element E is decreasing, while the magnetic intensity detected by the Hall element G is increasing. Therefore, based on the magnetic intensity information sent by the Hall elements E, F, and G, the control component can determine that the rotating reflective ramp is sweeping over the Hall element F. At this time, the control component initiates the array element structure switching, switching array element structure L4 to array element structure L1, driving array element structure L4 to stop transmitting and receiving ultrasonic signals, and simultaneously driving array element structure L1 to start transmitting and receiving ultrasonic signals. The acquired blocking cross-section is shown in the figure. Figure 5 As shown, multiple cross-sections at different angles are acquired as the rotating reflective ramp continues to move clockwise. Similarly, the cross-section images acquired by rotating the rotating reflective ramp clockwise from position a to position h are in the following order. Figure 4-11 As shown, the process returns to the cross-sectional view corresponding to position a and begins the next cycle of cross-sectional image acquisition, which will not be elaborated further here.

[0074] With the continuous rotation of the rotating reflective ramp, multiple cross-sectional images of the heart chambers are continuously captured. The cross-sectional images of each rotation are combined to obtain the four-dimensional three-dimensional ultrasound image of that rotation. As the rotating reflective ramp rotates rapidly and at different speeds, the four-dimensional three-dimensional ultrasound images obtained from each rotation are presented sequentially according to time, thus obtaining a four-dimensional dynamic ultrasound image of the heart changing with the heartbeat.

[0075] In one specific implementation, such as Figure 1 As shown, the ultrasonic transducer 100 also includes a motor 3;

[0076] The reflector structure 2 is connected to the rotor in the motor 3;

[0077] Motor 3 is used to receive the first control command and drive the rotor to rotate, thereby driving the rotating reflective inclined plane in the reflective structure 2 to rotate.

[0078] Specifically, the ultrasonic transducer 100 includes a motor 3, which is mounted inside the conduit. The motor 3 is tightly bonded and fixed to the inner wall of the conduit and connected to the control component via a lead wire (e.g., a flat thin-film wire with a thickness of 30 micrometers). The rotor diameter on the motor 3 is smaller than the diameter of the motor 3 itself, allowing it to rotate freely within the conduit. The rotor can rotate clockwise or counterclockwise under the drive of the motor 3, thereby rotating the rotating reflective ramp on the reflective structure 2. The lead wire of the motor 3 is close to the inner wall of the conduit to avoid affecting the rotor's rotation.

[0079] In a specific example, such as Figure 1 As shown, the ultrasonic transducer 100 also includes an array element substrate 4, which is used to fix the position of the linear array 1 in the conduit. The cables of the polarization array element are combined with the leads of the Hall element and the leads of the motor 3 to form a cable bundle 5 that is connected to the control component.

[0080] In one feasible approach, since the rotating reflective slope rotates 360 degrees to form a circle, with the 180-degree semicircle being a mirror image of another 180-degree semicircle, the same array element structure can be used in the current orientation and in the orientation 180 degrees later. The four array element structures arranged at 90 degrees to each other can actually be used alternately as eight array element structures arranged at 45 degrees to each other.

[0081] This specific embodiment combines array element structures arranged in different directions and operating independently with a rotating reflective inclined plane. This allows the ultrasound waves emitted by the array element structures to continuously pick up cross-sectional images around the catheter as the rotor rotates continuously. By combining multiple cross-sectional images picked up in each rotation, a ring-shaped three-dimensional ultrasound image for that rotation is obtained. As the rotor rotates rapidly and continuously, the three-dimensional ultrasound images for each rotation are presented sequentially according to time, forming a four-dimensional dynamic ultrasound image of the heart's interior that changes with the heartbeat, thus meeting the medical needs for precise examination of the heart chambers.

[0082] Example 2

[0083] In one specific embodiment of this disclosure, an ICE probe 200 for 4D imaging is provided, such as... Figure 12 As shown, the ICE probe 200 includes a controller (not shown) and an ultrasonic transducer 100 for 4D imaging as described in any of the above embodiments.

[0084] The controller is used to drive the control components of the ultrasonic transducer 100 to acquire cross-sectional images at different acquisition times.

[0085] Specifically, the ultrasound transducer 100 for 4D imaging is placed at a preset position on the catheter 6 of the ICE probe 200. The control component and the ultrasound transducer 100 are led to the handle 7 via the catheter 6. The doctor operates the control controller through the handle 7 to drive the control component of the ultrasound transducer 100 to work, so as to acquire multiple cross-sectional images around the heart chamber. The cross-sectional images are sent to the ICE 4D imaging device via the communication cable 8 connected to the ICE 4D imaging device to form a 4D dynamic ultrasound image.

[0086] This specific embodiment combines array element structures arranged in different directions and operating independently with a rotating reflective inclined plane. This allows the ultrasound waves emitted by the array element structures to continuously pick up cross-sectional images around the catheter as the rotor rotates continuously. By combining multiple cross-sectional images picked up in each rotation, a ring-shaped three-dimensional ultrasound image for that rotation is obtained. As the rotor rotates rapidly and continuously, the three-dimensional ultrasound images for each rotation are presented sequentially according to time, forming a four-dimensional dynamic ultrasound image of the heart's interior that changes with the heartbeat, thus meeting the medical needs for precise examination of the heart chambers.

[0087] Example 3

[0088] In one specific embodiment of this disclosure, an ICE four-dimensional imaging device is provided. The ICE four-dimensional imaging device includes a processor, a display communicatively connected to the processor, and an ICE probe 200 for 4D imaging as described in any of the above embodiments.

[0089] The processor is used to receive cross-sectional images acquired by the ICE probe 200 at different acquisition times, and to synthesize several cross-sectional images obtained by rotating the rotating reflective inclined plane once to obtain a stereoscopic image;

[0090] The processor is also used to send the stereoscopic image obtained after each rotation of the rotating reflective ramp to the display.

[0091] The display is used to sequentially show stereoscopic images according to the acquisition time to form a four-dimensional dynamic ultrasound image.

[0092] Specifically, by connecting the ICE probe 200 for 4D imaging to the processor of the ICE four-dimensional imaging device, multiple cross-sectional images of the pericardial cavity are continuously acquired and transmitted to the processor for synthesis processing of multiple cross-sectional images for each rotation, resulting in stereoscopic images at different times. These images are then sent to the display according to time to form a four-dimensional dynamic ultrasound image.

[0093] This specific embodiment combines array element structures arranged in different directions and operating independently with a rotating reflective inclined plane. This allows the ultrasound waves emitted by the array element structures to continuously pick up cross-sectional images around the catheter as the rotor rotates continuously. By combining multiple cross-sectional images picked up in each rotation, a ring-shaped three-dimensional ultrasound image for that rotation is obtained. As the rotor rotates rapidly and continuously, the three-dimensional ultrasound images for each rotation are presented sequentially according to time, forming a four-dimensional dynamic ultrasound image of the heart's interior that changes with the heartbeat, thus meeting the medical needs for precise examination of the heart chambers.

[0094] While specific embodiments of this disclosure have been described above, those skilled in the art should understand that these are merely illustrative examples, and the scope of protection of this disclosure is defined by the appended claims. Those skilled in the art can make various changes or modifications to these embodiments without departing from the principles and essence of this disclosure, but all such changes and modifications fall within the scope of protection of this disclosure.

Claims

1. An ultrasonic transducer for 4D imaging, characterized in that, The ultrasonic transducer includes a control component, a linear array and a reflective structure connected to and disposed opposite to the control component; The linear array includes multiple Hall elements fixedly arranged at multiple different positions, and several array element structures arranged in different preset directions and operating independently. Each array element structure consists of several polarized array elements arranged in a straight line. The array element structure is used to transmit and receive ultrasonic signals. The reflective structure is provided with a rotating reflective ramp and a magnetic element that rotates with the rotating reflective ramp; The control component is used to send a first control command to the reflective structure to drive the rotating reflective inclined plane to rotate; the control component is also used to send a second control command to the Hall element to drive the Hall element to detect the magnetic intensity information of the magnetic element; The control component is also used to determine the target orientation of the rotating reflective ramp based on the magnetic intensity information detected by each Hall element at different acquisition times, send a third control command to a target array element structure that matches the target orientation, drive the target array element structure to emit the ultrasonic signal, and receive the ultrasonic signal reflected by the rotating reflective ramp along a preset reflection path at the target orientation to generate a cross-sectional image corresponding to each acquisition time, and synthesize the cross-sectional images at different acquisition times to obtain a four-dimensional dynamic ultrasonic image; The different array element structures correspond to different azimuth ranges of the rotating reflective inclined plane.

2. The ultrasonic transducer according to claim 1, characterized in that, The linear array is square, and the linear array includes four array element structures; The four array elements are arranged in a cross shape.

3. The ultrasonic transducer according to claim 2, characterized in that, Two Hall elements are arranged on each side of the linear array, and the two Hall elements are arranged symmetrically.

4. The ultrasonic transducer according to claim 3, characterized in that, The line connecting each Hall element to the center point of the linear array forms a predetermined angle with the adjacent array element structure.

5. The ultrasonic transducer according to claim 1, characterized in that, The ultrasonic transducer also includes a motor; The reflective structure is connected to the rotor in the motor; The motor is used to receive the first control command and drive the rotor to rotate, thereby causing the rotating reflective inclined plane in the reflective structure to rotate.

6. The ultrasonic transducer according to claim 5, characterized in that, The motor is also used to receive the first control command and drive the rotor to rotate clockwise, so as to drive the rotating reflective inclined plane to rotate clockwise.

7. The ultrasonic transducer according to claim 5, characterized in that, The motor is also used to receive the first control command and drive the rotor to rotate counterclockwise, so as to drive the rotating reflective inclined plane to rotate counterclockwise.

8. The ultrasonic transducer according to any one of claims 1 to 7, characterized in that, The magnetic element includes a magnet.

9. An ICE probe for 4D imaging, characterized in that, The ICE probe includes a controller and an ultrasonic transducer for 4D imaging as described in any one of claims 1 to 8; The controller is used to drive the control components of the ultrasonic transducer to acquire cross-sectional images at different acquisition times.

10. An ICE four-dimensional imaging device, characterized in that, The ICE 4D imaging device includes a processor, a display communicatively connected to the processor, and an ICE probe for 4D imaging as described in claim 9; The processor is used to receive the cross-sectional images acquired by the ICE probe at different acquisition times, and to synthesize several cross-sectional images obtained by rotating the rotating reflective inclined plane once to obtain a stereoscopic image; The processor is also used to send the stereoscopic image obtained by each rotation of the rotating reflective ramp to the display. The display is used to sequentially display the stereoscopic images according to the acquisition time to form a four-dimensional dynamic ultrasound image.

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