Ultrasonic transducer, ICE ultrasonic probe and equipment for generating multiple ultrasonic section images

Abstract

The invention provides an ultrasonic transducer, an ICE ultrasonic probe for generating multiple ultrasonic section images and equipment. The ultrasonic transducer comprises a control mechanism and an ultrasonic channel switching unit, the ultrasonic channel switching unit is composed of an acoustic transmission material layer and N different types of morphological change material layers; the N morphological change material layers and the acoustic transmission material layer are arranged in sequence, reflecting surfaces with different inclination angles are formed between the adjacent material layers, and under different morphologies of the target morphological change material layer, an ultrasonic signal passes through a target reflecting surface or is reflected by the target reflecting surface to form different emission echo paths; the control mechanism is used for controlling each morphological change material to be in different morphologies at different time points, so that the ultrasonic signals at different time points detect the target tissue through different emission echo paths to generate a plurality of ultrasonic section images of the target tissue at different angles. According to the invention, a plurality of ultrasonic section images at different angles can be displayed at the same time, and the comprehensiveness and efficiency of inspection are remarkably improved.

Description

Technical Field

[0001] The present disclosure relates to the technical field of medical devices, and in particular to an ultrasonic transducer, an ICE ultrasonic probe and a device for generating multi-ultrasonic section images. Background Art

[0002] When performing intracardiac ultrasound imaging, traditional ICE (intracardiac ultrasound) probes usually need to frequently rotate the probe to change the inspection angle in order to obtain more comprehensive diagnostic information. However, this operation method not only increases the skill requirements for doctors' professional operation techniques, but also increases the workload of doctors, and may cause discomfort or potential risks to patients due to the frequent rotation of the catheter in the blood vessels and heart. In addition, imaging at a single angle often makes it difficult to capture the full picture of the lesion, affecting the accuracy and efficiency of diagnosis. Summary of the invention

[0003] The technical problem to be solved by the present disclosure is to overcome the defects in the prior art that the traditional ICE probe has a single imaging angle and cannot ensure the comprehensiveness of the inspection, and to provide an ultrasonic transducer, an ICE ultrasonic probe and a device for generating multi-ultrasonic section images.

[0004] The present invention solves the above technical problems through the following technical solutions:

[0005] According to a first aspect of the present disclosure, an ultrasonic transducer is provided, the ultrasonic transducer comprising a control mechanism, a housing, and a transducer array element, an ultrasonic channel switching unit, and a sound-transmitting window located in the housing;

[0006] The transducer array element is used to transmit and receive ultrasonic signals;

[0007] The acoustically transparent window is used to transmit the ultrasonic signal;

[0008] The ultrasonic channel switching unit is composed of a sound-transmitting material layer and N different types of morphologically variable material layers;

[0009] Wherein, N is a positive integer, N types of the morphology-changing material layers and the sound-transmitting material layers are arranged in sequence, and reflection surfaces with different inclination angles are formed between adjacent material layers, and under different forms of the target morphology-changing material layer, the ultrasonic signal passes through the target reflection surface or is reflected by the target reflection surface to form different transmission echo paths;

[0010] The control mechanism is used to control each of the morphologically changeable materials to be in different forms at different time points, so that the ultrasound signals at different time points detect the target tissue via different emission echo paths, so as to generate multiple ultrasound section images of the target tissue at different angles.

[0011] Preferably, when N=1, the morphology-changing material layer includes an electrorheological fluid layer; the ultrasonic transducer also includes an electric field generating device electrically connected to the control mechanism;

[0012] The electric field generating device forms an electric field when powered on, and the electric field covers a first range where the electrorheological fluid layer is located. Under the action of the electric field, the electrorheological fluid layer changes from a liquid state to a solid state to form a first reflection surface;

[0013] The control mechanism is used to control the power-on state of the electric field generating device at different time points. The ultrasonic signal detects the target tissue along a preset transmission echo path at a non-power-on time point to generate a first ultrasonic section image of the target tissue. The ultrasonic signal is reflected by the first reflection surface along the first transmission echo path at a power-on time point to detect the target tissue to generate a second ultrasonic section image of the target tissue.

[0014] Preferably, when N=1, the morphology-changing material layer includes a magnetic fluid layer; the ultrasonic transducer also includes a magnetic field generating device electrically connected to the control mechanism;

[0015] The magnetic field generating device forms a magnetic field when powered on, and the magnetic field covers the second range where the magnetic fluid layer is located. Under the action of the magnetic field, the magnetic fluid layer changes from a liquid state to a solid state to form a second reflection surface;

[0016] The control mechanism is used to control the power-on state of the magnetic field generating device at different time points. The ultrasonic signal detects the target tissue along a preset transmission echo path at a non-power-on time point to generate a first ultrasonic section image of the target tissue. The ultrasonic signal is reflected by the second reflection surface along the first transmission echo path at a power-on time point to detect the target tissue to generate a third ultrasonic section image of the target tissue.

[0017] Preferably, when N=2, the morphology-changing material layer includes an electrorheological fluid layer and a magnetic fluid layer; the ultrasonic transducer also includes an electric field generating device and a magnetic field generating device electrically connected to the control mechanism;

[0018] The sound-transmitting material layer, the electrorheological fluid layer and the magnetic fluid layer are arranged in sequence along the emission direction of the ultrasonic signal, and a sound-transmitting diaphragm is provided between the magnetic fluid layer and the electrorheological fluid layer;

[0019] The sound-transmitting diaphragm is used to isolate the magnetic fluid layer and the electrorheological fluid layer;

[0020] The electric field generating device forms an electric field when powered on, and the electric field covers a third range where the electrorheological fluid layer is located. Under the action of the electric field, the electrorheological fluid layer changes from a liquid state to a solid state to form a third reflection surface;

[0021] The magnetic field generating device forms a magnetic field when powered on, and the magnetic field covers a fourth range where the magnetic fluid layer is located. Under the action of the magnetic field, the magnetic fluid layer changes from a liquid state to a solid state to form a fourth reflection surface;

[0022] The control mechanism is used to control the power-on status of the electric field generating device and the magnetic field generating device at different time points. The ultrasonic signal detects the target tissue along a preset transmission echo path at a time point when the magnetic field generating device and the electric field generating device are both not powered on, so as to generate a first ultrasonic section image of the target tissue. The ultrasonic signal is reflected via the third reflection surface along a third transmission echo path at a time point when the electric field generating device is powered on, so as to generate a fourth ultrasonic section image of the target tissue. The ultrasonic signal is transmitted via the fourth reflection surface along a fourth transmission echo path at a time point when the magnetic field generating device is powered on and the electric field generating device is not powered on, so as to generate a fifth ultrasonic section image of the target tissue.

[0023] Preferably, the electric field generating device comprises an electric field positive electrode and an electric field negative electrode;

[0024] The electric field positive electrode and the electric field negative electrode are arranged on the inner side wall of the shell.

[0025] Preferably, the electric field positive electrode and the electric field negative electrode are both conductive films;

[0026] and / or,

[0027] The negative electric field electrode covers the entire sound-transmitting window.

[0028] Preferably, the magnetic field generating device comprises an electromagnetic coil, and the electromagnetic coil is arranged at a preset position of the shell.

[0029] Preferably, the magnetic field generating device further comprises enhanced soft magnetic material;

[0030] The enhanced soft magnetic material is arranged at a relative position of the electromagnetic coil;

[0031] The enhanced soft magnetic material is used to enhance the magnetic field generated by the electromagnetic coil.

[0032] Preferably, the ultrasonic transducer further comprises a channel signal cable and an array element backing material;

[0033] The transducer array element and the control mechanism are connected to the ultrasound probe handle via the channel signal cable;

[0034] The array element backing material is used to fix the transducer array element.

[0035] According to a second aspect of the present disclosure, an ICE ultrasound probe for generating multiple ultrasound cross-section images is provided. The ICE ultrasound probe for generating multiple ultrasound cross-section images comprises the ultrasound transducer described in the first aspect of the present disclosure.

[0036] According to a third aspect of the present disclosure, an intracardiac ultrasound device is provided, wherein the intracardiac ultrasound device comprises the ICE ultrasound probe for generating multi-ultrasound section images as described in the second aspect of the present disclosure.

[0037] On the basis of being in accordance with the common sense in the art, the above-mentioned preferred conditions can be arbitrarily combined to obtain the preferred embodiments of the present disclosure.

[0038] The positive progressive effect of the present disclosure lies in: by introducing a control mechanism and a variety of morphologically changeable materials into the ultrasonic transducer of the ultrasonic probe, and designing the various morphologically changeable materials as reflective surfaces at a plurality of different angles, the control mechanism is used to control the states of the various morphologically changeable materials to realize reflection and imaging of ultrasonic signals in different directions, thereby realizing the simultaneous display of a plurality of ultrasonic section images at different angles, thereby significantly improving the comprehensiveness and efficiency of the examination, and because the ultrasonic probe can display a plurality of ultrasonic section images at the same time, the doctor does not need to frequently rotate the probe during the examination, thereby reducing the number of rotations and the impact on the patient, and also helping the doctor to have a more comprehensive understanding of the lesion condition, quickly and accurately find the lesion point at multiple angles, and improve the accuracy and reliability of the diagnosis. BRIEF DESCRIPTION OF THE DRAWINGS

[0039] Figure 1 is a first end view of the ultrasonic transducer in Example 1;

[0040] Figure 2 is a second end view of the ultrasonic transducer in Example 1;

[0041] Figure 3 is a third end view of the ultrasonic transducer in Example 1;

[0042] Figure 4 is a fourth end view of the ultrasonic transducer in Example 1;

[0043] Figure 5 This is a schematic diagram of the structure of the electric field generating device of the ultrasonic transducer in Example 1;

[0044] Figure 6 is a fifth end view of the ultrasonic transducer in Example 1;

[0045] Figure 7 It is a left side schematic diagram of the structure of the magnetic field generating device of the ultrasonic transducer in Example 1;

[0046] Figure 8 is a sixth end view of the ultrasonic transducer in Example 1;

[0047] Fig. 9 is a seventh end view of the ultrasonic transducer in Example 1;

[0048] Fig.10 is an eighth end view of the ultrasonic transducer in Example 1;

[0049] Fig.11 It is a schematic diagram of the right side structure of the electric field generating device and the magnetic field generating device of the ultrasonic transducer in Example 1;

[0050] Fig.12 Schematic diagram of the structure of an ICE ultrasound probe for generating multiple ultrasound cross-section images in Example 2. DETAILED DESCRIPTION

[0051] The present disclosure is further described below by way of examples, but the present disclosure is not limited to the scope of the examples.

[0052] Prefixes such as "first" and "second" are used in the embodiments of the present disclosure only to distinguish different description objects, and have no limiting effect on the position, order, priority, quantity or content of the described objects. The use of prefixes such as ordinal numbers to distinguish description objects in the embodiments of the present disclosure does not constitute a limitation on the described objects. For the statement of the described objects, please refer to the description in the context of the claims or embodiments, and no unnecessary limitation should be constituted due to the use of such prefixes. In addition, in the description of the present embodiment, unless otherwise specified, the meaning of "plurality" is two or more.

[0053] In the embodiments of the present disclosure, the collection, storage, use, processing, transmission, provision and disclosure of user personal information involved are in compliance with the provisions of relevant laws and regulations and do not violate public order and good morals.

[0054] Example 1

[0055] In a specific embodiment of the present disclosure, an ultrasonic transducer 100 is provided. Figure 1 As shown, the ultrasonic transducer 100 includes a control mechanism (not shown in the figure), a housing 1, and a transducer array element 2, an ultrasonic channel switching unit 3, and a sound-transmitting window 4 located in the housing 1;

[0056] The transducer array element 2 is used to transmit and receive ultrasonic signals;

[0057] The sound-transmitting window 4 is used to transmit ultrasonic signals;

[0058] The ultrasound channel switching unit 3 is composed of a sound-transmitting material layer 31 and N different types of morphology-changing material layers 32;

[0059] Wherein, N is a positive integer, N types of morphologically variable material layers 32 and sound-transmitting material layers 31 are arranged in sequence, and reflection surfaces with different inclination angles are formed between adjacent material layers. Under different morphologies of the target morphologically variable material layer 32, the ultrasonic signal passes through the target reflection surface or is reflected by the target reflection surface to form different emission echo paths;

[0060] The control mechanism is used to control each morphologically variable material to be in different forms at different time points, so that the ultrasonic signals at different time points detect the target tissue via different emission echo paths, so as to generate multiple ultrasonic section images of the target tissue at different angles.

[0061] Specifically, the ultrasonic transducer 100 is the core part of the ICE probe. The transducer array element 2 in the ultrasonic transducer 100 is used to transmit and receive ultrasonic signals, usually using 64 channels, 128 channels or 256 channels, which can be selected according to the size of the heart cavity to avoid excessive size affecting the curvature of the heart cavity.

[0062] The ultrasonic channel switching unit 3 can detect the target tissue from different angles by changing the transmission echo path of the ultrasonic signal to generate multiple ultrasonic cross-sectional images of the target tissue at different angles. The ultrasonic channel switching unit 3 is formed by introducing a sound-transmitting material layer 31 and N different morphological change material layers 32 between the sound-transmitting window 4 and the inner wall of the shell 1, and the sound-transmitting material layer 31 and the N morphological change material layers 32 are arranged in sequence along the transmission direction of the ultrasonic signal, wherein the N morphological change material layers 32 are all capable of realizing the transformation between liquid and solid under specific conditions, for example, electrorheological fluid, magnetic fluid, composite material, etc., each morphological change material layer 32 is separated from each other (such as using a sound-transmitting diaphragm) to form a reflection surface with different inclination angles, and the control conditions of different morphological change material layers 32 do not affect each other, when the morphological change material layer 32 is in a liquid state, the ultrasonic signal can pass through the morphological change material, and when the morphological change material is in a solid state, the ultrasonic signal is reflected through the reflection surface of the morphological change material layer 32 transformed into a solid state. It should be noted that the tilt angle can be set according to actual needs. For example, the angle between the reflection surface and the transducer array element 2 can be 30 degrees, 45 degrees, 60 degrees, etc.

[0063] The sound-transmitting material layer 31 is used to couple the ultrasonic signal emitted by the transducer array element 2 and the echo. The sound-transmitting window 4 is a channel for the ultrasonic signal to be emitted and echoed, and usually adopts an arc-shaped acoustic window. The sound-transmitting material layer 31 and the sound-transmitting window 4 can mutually transmit the ultrasonic wave emitted by the transducer array element 2 and the echo of the target tissue to be detected. The sound-transmitting material layer 31 and the N types of morphologically variable material layers 32 are wrapped together by the shell 1 and the sound-transmitting window 4 inside to isolate the physical penetration of blood and protect the electrical insulation of all internal materials and circuits.

[0064] The control mechanism can obtain N real-time ultrasonic cross-sectional images at different angles by sequentially and continuously controlling N morphologically changing material layers 32 to transform between liquid and solid under corresponding specific conditions. After being stored and displayed by the host, N ultrasonic cross-sectional images at different angles can be displayed simultaneously on the same screen.

[0065] This specific embodiment introduces a control mechanism and a variety of morphologically changeable materials into the ultrasonic transducer 100 of the ultrasonic probe, which can simultaneously display multiple ultrasonic cross-sectional images at different angles, thereby significantly improving the comprehensiveness and efficiency of the examination. In addition, since the ultrasonic probe can display multiple ultrasonic cross-sectional images at the same time, the doctor does not need to frequently rotate the probe during the examination, thereby reducing the number of rotations and the impact on the patient. It also helps the doctor to have a more comprehensive understanding of the lesion condition, reduces the strict requirements on the doctor's professional skill level, and quickly and accurately finds the lesion point at multiple angles, thereby improving the accuracy and reliability of diagnosis.

[0066] It should be noted that Figure 1 Three morphology-changing materials are used as an illustration, and the specific number of morphology-changing materials can be set according to actual needs and should not be limited to a maximum of three morphology-changing materials.

[0067] In a specific embodiment, Figure 1-11 As shown, the ultrasonic transducer 100 further includes a channel signal cable 5 and an array element backing material 6;

[0068] The transducer array element 2 and the control mechanism are connected to the ultrasound probe handle via a channel signal cable 5;

[0069] The array element backing material 6 is used to fix the transducer array element 2 .

[0070] Specifically, the ultrasonic transducer 100 further includes a channel signal cable 5 and an array element backing material 6. The transducer array element 2 and the control mechanism are connected to the channel signal cable 5 through a lead wire to be connected to the handle of the ultrasonic probe to realize switch control of the transducer array element 2 and the control mechanism. The array element backing material 6 is used to fix the transducer array element 2. The array element backing material 6 is combined with the transducer array element 2 and fixed to the corresponding position of the housing 1 through a fixing material.

[0071] In a specific implementation, when N=1, Figure 2 As shown, the morphology-changing material layer includes an electrorheological fluid layer 321; the ultrasonic transducer 100 also includes an electric field generating device 10 electrically connected to the control mechanism;

[0072] The electric field generating device 10 forms an electric field when powered on, and the electric field covers the first range where the electrorheological fluid layer 321 is located. Under the action of the electric field, the electrorheological fluid layer 321 changes from a liquid state to a solid state to form a first reflection surface.

[0073] The control mechanism is used to control the power-on state of the electric field generating device 10 at different time points. The ultrasonic signal detects the target tissue along a preset transmission echo path at the non-power-on state time point to generate a first ultrasonic section image of the target tissue. The ultrasonic signal is reflected by the first reflection surface along the first transmission echo path at the power-on state time point to detect the target tissue to generate a second ultrasonic section image of the target tissue.

[0074] Specifically, if two ultrasonic cross-sectional images need to be displayed simultaneously in different directions, only one morphologically changeable material is needed, such as electrorheological fluid. The electrorheological fluid can change between liquid and solid under the action of an electric field. When the electric field is applied, the electrorheological fluid becomes solid and reflects ultrasonic waves. When the electric field is removed, it changes back to liquid and allows ultrasonic signals to penetrate.

[0075] By providing an electric field generating device 10 electrically connected to the control mechanism, and introducing an electrorheological fluid layer 321 between the sound-transmitting window 4 and the inner wall of the housing, a surface of the electrorheological fluid layer 321 adjacent to the sound-transmitting material layer 31 is designed to be inclined at a certain angle. Since the direction of the ultrasonic signal emitted by the transducer array element 2 is vertically upward (i.e., the Y-axis direction), when the electrorheological fluid layer 321 is solid, the ultrasonic signal is reflected by the reflection surface along the first emission echo path to detect the target tissue.

[0076] Therefore, if Figure 3 As shown, when the electric field generating device 10 is not powered, the electrorheological fluid is not affected by the electric field, and the ultrasonic signal γ can freely pass through the acoustic window 4 along the preset transmission echo path (i.e., the Y-axis direction) to transmit and echo the target tissue, and the imaging position of the reflection surface of the target tissue is also in the Y-axis direction. Figure 4 As shown, when the electric field generating device 10 is powered on to generate an electric field, the electrorheological fluid is transformed into a solid to form a first reflection surface to reflect the ultrasonic signal γ, so that the ultrasonic signal γ is reflected by the first reflection surface along the first transmission echo path to form a second ultrasonic section image. Taking the angle between the first reflection surface and the transducer array element 2 as 45 degrees as an example, the ultrasonic signal γ is transformed into a transmission and echo detection target tissue along the X-axis direction after being reflected by the first reflection surface, and the imaging position of the reflection surface of the target tissue is also in the X-axis direction. Therefore, the control mechanism continuously switches the power-on state of the electric field generating device 10, for example, switching 60 cycles per second (i.e., switching 120 times in one direction), so that the ICE probe can simultaneously present two ultrasonic section images in the X-axis and Y-axis directions, thereby realizing simultaneous imaging at multiple angles.

[0077] Among them, Figure 2-5As shown, the electric field generating device 10 includes an electric field positive electrode 101 and an electric field negative electrode 102; the electric field positive electrode 101 and the electric field negative electrode 102 are arranged on the inner wall of the housing 1. In order to avoid affecting the propagation of the ultrasonic signal, the electric field positive electrode 101 and the electric field negative electrode 102 are both conductive films, and the smaller the thickness, the better, for example, 1μm, at this time, the effect on the propagation of the ultrasonic signal is very small, the electric field positive electrode 101 film and the electric field negative electrode 102 film are plated on the inner wall of the housing 1, and the electric field positive electrode 101 film and the electric field negative electrode 102 film are connected to the channel signal cable 5 through the lead wire, so as to realize the control of the electric field generating device 10.

[0078] As a preferred implementation, the electric field cathode 102 covers the entire acoustic window 4, ensuring that all ultrasound signals behave in a consistent manner under the action of the electric field, so as to obtain high-quality ultrasound cross-sectional images.

[0079] This specific embodiment utilizes the electrorheological fluid layer 321 and the electric field generating device 10 to realize the function of simultaneously displaying two ultrasonic cross-sectional images, significantly expanding the examination range of ICE intracardiac ultrasound, reducing the number of rotations, reducing the impact on patients, and improving the efficiency and accuracy of diagnosis.

[0080] In another specific embodiment, when N=1, Figure 6 As shown, the morphology-changing material layer 32 includes a magnetic fluid layer 322; the ultrasonic transducer 100 also includes a magnetic field generating device 20 electrically connected to the control mechanism;

[0081] The magnetic field generating device 20 forms a magnetic field when powered on, and the magnetic field covers the second range where the magnetic fluid layer 322 is located. Under the action of the magnetic field, the magnetic fluid layer 322 changes from a liquid state to a solid state to form a second reflection surface.

[0082] The control mechanism is used to control the power-on state of the magnetic field generating device 20 at different time points. The ultrasonic signal detects the target tissue along a preset transmission echo path at the non-power-on time point to generate a first ultrasonic section image of the target tissue. The ultrasonic signal is reflected by the second reflection surface along the first transmission echo path at the power-on time point to detect the target tissue to generate a third ultrasonic section image of the target tissue.

[0083] Specifically, if two ultrasonic cross-sectional images need to be displayed simultaneously in different directions, a magnetic fluid can also be used to achieve this, wherein the magnetic fluid is in a liquid state without the action of a magnetic field and can transmit ultrasonic signals, and is in a solid state under the action of a magnetic field and can reflect ultrasonic signals.

[0084] By providing a magnetic field generating device 20 electrically connected to the control mechanism, and introducing a magnetic fluid layer 322 between the sound-transmitting window 4 and the inner wall of the housing, a surface of the magnetic fluid layer 322 adjacent to the sound-transmitting material layer 31 is designed to be inclined at a certain angle. When the electrorheological fluid layer 321 is solid, the ultrasonic signal is reflected by the reflection surface and detects the target tissue along the second transmission echo path.

[0085] Therefore, when the magnetic field generating device 20 is not powered on, the magnetic fluid is not affected by the magnetic field, and the ultrasonic signal can freely pass through the sound-transmitting window 4 along the preset transmission echo path (i.e., the Y-axis direction) to transmit and echo the target tissue, and the imaging position of the reflection surface of the target tissue is also in the Y-axis direction. When the magnetic field generating device 20 is powered on to generate a magnetic field, the magnetic fluid is transformed into a solid to form a second reflection surface to reflect the ultrasonic signal, so that the ultrasonic signal is reflected by the second reflection surface along the second transmission echo path to form a third ultrasonic section image. Therefore, by continuously switching the power-on state of the magnetic field generating device 20, the control mechanism can simultaneously present two ultrasonic section images in the Y-axis and the second transmission echo path directions, thereby realizing simultaneous imaging at multiple angles. For example, if the angle between the second reflection surface and the transducer array element 2 is 45 degrees, then the direction of the second transmission echo path is the X-axis direction.

[0086] Among them, Figure 7 As shown, the magnetic field generating device 20 includes an electromagnetic coil 201, which is disposed at a preset position of the housing 1. The electromagnetic coil 201 is connected to the channel signal cable 5 through a lead wire to be connected to the handle of the ultrasound probe. For example, the electromagnetic coil 201 is disposed on the inner wall of the housing 1 facing the magnetic fluid layer 322, so that the magnetic field generated by the electromagnetic coil 201 can cover the magnetic fluid layer 322 and control the morphological change of the magnetic fluid layer 322.

[0087] In a specific embodiment, Figure 7 As shown, the magnetic field generating device 20 further includes a reinforced soft magnetic material 202;

[0088] The reinforced soft magnetic material 202 is arranged at a relative position to the electromagnetic coil 201;

[0089] The reinforced soft magnetic material 202 is used to enhance the magnetic field generated by the electromagnetic coil 201 .

[0090] Specifically, the magnetic field generating device 20 also includes an enhanced soft magnetic material 202 disposed at a position relative to the electromagnetic coil 201, which is used to assist in enhancing the magnetic field generated by the electromagnetic coil 201. When the electromagnetic coil 201 is connected to a current, a magnetic path is formed between the generated magnetic field and the enhanced soft magnetic material 202. The addition of the enhanced soft magnetic material 202 can enhance the magnetic field received by the magnetic fluid between the two and make it more uniform, so as to reduce the driving current while satisfying the change in the morphology of the magnetic fluid.

[0091] This specific embodiment utilizes the magnetic fluid layer 322 and the magnetic field generating device 20 to realize the function of simultaneously displaying two ultrasonic cross-sectional images, significantly expanding the examination range of ICE intracardiac ultrasound, reducing the number of rotations, reducing the impact on patients, and improving the efficiency and accuracy of diagnosis.

[0092] In a specific implementation, when N=2, Figure 8-11 As shown, the morphology-changing material layer 32 includes an electrorheological fluid layer 321 and a magnetic fluid layer 322; the ultrasonic transducer 100 also includes an electric field generating device 10 and a magnetic field generating device 20 electrically connected to the control mechanism;

[0093] The sound-transmitting material layer 31, the electrorheological fluid layer 321 and the magnetic fluid layer 322 are arranged in sequence along the transmission direction of the ultrasonic signal, and a sound-transmitting diaphragm is provided between the magnetic fluid layer 322 and the electrorheological fluid layer 321;

[0094] The sound-transmitting diaphragm is used to isolate the magnetic fluid layer 322 and the electrorheological fluid layer 321;

[0095] The electric field generating device 10 forms an electric field when powered on, and the electric field covers the third range where the electrorheological fluid layer 321 is located. Under the action of the electric field, the electrorheological fluid layer 321 changes from a liquid state to a solid state to form a third reflection surface.

[0096] The magnetic field generating device 20 forms a magnetic field when powered on, and the magnetic field covers the fourth range where the magnetic fluid layer 322 is located. Under the action of the magnetic field, the magnetic fluid layer 322 changes from a liquid state to a solid state to form a fourth reflection surface.

[0097] The control mechanism is used to control the power-on state of the electric field generating device 10 and the magnetic field generating device 20 at different time points. At the time point when the magnetic field generating device 20 and the electric field generating device 10 are not powered on, the electrorheological fluid layer 321 and the magnetic fluid layer 322 are both in liquid state, and the ultrasonic signal can pass through the electrorheological fluid layer 321 and the magnetic fluid layer 322 to detect the target tissue along the preset transmission echo path to generate a first ultrasonic section image of the target tissue; at the time point when the electric field generating device 10 is powered on, that is, the electric field positive electrode 101 and the electric field negative electrode 102 form an electric field covering the electrorheological fluid layer 321 in the powered state, and the electrorheological fluid Under the action of the electric field, layer 321 changes from liquid to solid to form a third reflection surface, and the ultrasonic signal is reflected via the third reflection surface along the third transmission echo path to detect the target tissue, so as to generate a fourth ultrasonic section image of the target tissue; when the magnetic field generating device 20 is powered on and the electric field generating device 10 is not powered on, the magnetic field generating device 20 forms a magnetic field covering the magnetic fluid layer 322, and the magnetic fluid layer 322 changes from liquid to solid under the action of the magnetic field to form a fourth reflection surface, and the ultrasonic signal is transmitted via the fourth reflection surface along the fourth transmission echo path to detect the target tissue, so as to generate a fifth ultrasonic section image of the target tissue.

[0098] Specifically, considering that the same morphological change material will crosstalk with each other because it is affected by the same condition, for example, the ultrasound channel switching unit 3 includes a first electrorheological fluid layer and a second electrorheological fluid layer, and the first electrorheological fluid layer and the second electrorheological fluid layer are correspondingly provided with a first electric field generating device and a second electric field generating device. When the first electric field generating device is energized to generate an electric field to control the first electrorheological fluid layer to change into a solid state, the second electrorheological fluid layer will also be affected by the electric field and cannot be in a pure liquid state, which has a great influence on the transmission of the ultrasound signal, so that imaging cannot be performed as required.

[0099] Therefore, when it is necessary to display three ultrasonic cross-sectional images simultaneously in different directions, magnetic fluid and electrorheological fluid can be selected respectively, and a magnetic field generating device 20 and an electric field generating device 10 are provided correspondingly, and the sound-transmitting material layer 31, the electrorheological fluid layer 321 and the magnetic fluid layer 322 are arranged in sequence along the transmission direction of the ultrasonic signal. Among them, the electrorheological fluid layer 321 and the magnetic fluid layer 322 are separated by a sound-transmitting diaphragm to avoid mixing, and since the sound-transmitting material layer 31 itself is solid, there is no need to separate them repeatedly, and a third reflection surface is formed between the electrorheological fluid layer 321 and the sound-transmitting material, and a fourth reflection surface is formed between the magnetic fluid layer 322 and the electrorheological fluid layer 321, and the angles of the third reflection surface and the fourth reflection surface are different. Of course, the positions of the electrorheological fluid layer 321 and the magnetic fluid layer 322 can also be swapped, and this embodiment does not limit this.

[0100] like Figure 8 , 11 As shown, when no current is applied to the magnetic field generating device 20 and the electric field generating device 10, the ICE probe works in the normal mode, the emission direction of the ultrasonic signal γ is the Y-axis direction, and the echo imaging also forms the first ultrasonic section image of the target tissue under examination along the Y-axis.

[0101] like Fig. 9 , 11 As shown, when current is applied to the electric field positive electrode 101 and the electric field negative electrode 102, the electrorheological fluid layer 321 changes to a solid state to form a third reflection surface, and the ultrasonic signal γ is reflected by the third reflection surface along the third transmission echo path to detect the target tissue, and the echo imaging also forms a fourth ultrasonic section image of the examined tissue along the third transmission echo path. It should be noted that when the electrorheological fluid layer 321 changes to a solid state, the ultrasonic signal γ cannot pass through the electrorheological fluid layer 321 to reach the magnetic fluid layer 322. Therefore, whether the magnetic fluid layer 322 is in a liquid state does not affect the transmission echo path of the ultrasonic signal γ.

[0102] like Figure 10-11As shown, when current is applied to the magnetic field generating device 20 and current is not applied to the electric field generating device 10, the magnetic fluid layer 322 is transformed into a solid state to form a fourth reflection surface, and the ultrasonic signal γ passes through the electrorheological fluid layer 321 and is reflected by the fourth reflection surface along the fourth transmission echo path to detect the target tissue, and the echo imaging also forms a fifth ultrasonic section image of the examined tissue along the fourth transmission echo path.

[0103] Taking the angle between the third reflection surface and the transducer array element 2 as 30 degrees, and the angle between the fourth reflection surface and the transducer array element 2 as 60 degrees as an example, when the magnetic field generating device 20 is powered on and the electric field generating device 10 is powered off, the ultrasonic signal is reflected at the fourth reflection surface. According to the law of reflection, the incident angle is the same as the reflection angle, and the reflected direction is 120 degrees from the Y axis. The echo imaging also forms the reflection surface image of the examined tissue at this angle. When the electric field generating device 10 is powered on, the ultrasonic signal is reflected at the third reflection surface. According to the law of reflection, the reflected direction is 60 degrees from the Y axis. The echo imaging also forms the reflection surface image of the examined tissue at this angle.

[0104] Thus, by sequentially and continuously controlling the power on of the magnetic field generating device 20 and the electric field generating device 10, three real-time ultrasonic cross-sectional images at different angles can be obtained. After being stored and displayed by the host, three ultrasonic cross-sectional images at different angles can be displayed simultaneously on the same screen.

[0105] This specific embodiment can display multiple ultrasonic cross-sectional images at different angles simultaneously through the synergistic effect of the electromagnetic coil 201 and the electrorheological fluid, which significantly improves the comprehensiveness and efficiency of the examination. Since multiple ultrasonic cross-sectional images can be displayed simultaneously, the doctor does not need to frequently rotate the probe during the examination, thereby reducing the number of rotations and the impact on the patient. Multi-angle imaging helps doctors understand the lesion more comprehensively and improves the accuracy and reliability of diagnosis.

[0106] This embodiment introduces a control mechanism and a variety of morphologically changeable materials into the ultrasonic transducer 100 of the ultrasonic probe, and designs the various morphologically changeable materials as reflective surfaces at a plurality of different angles. The control mechanism is used to control the states of the various morphologically changeable materials to achieve reflection and imaging of ultrasonic signals in different directions, thereby achieving simultaneous display of a plurality of ultrasonic section images at different angles, thereby significantly improving the comprehensiveness and efficiency of the examination. Furthermore, since the ultrasonic probe can display a plurality of ultrasonic section images at the same time, the doctor does not need to frequently rotate the probe during the examination, thereby reducing the number of rotations and the impact on the patient. This also helps the doctor to have a more comprehensive understanding of the lesion condition, quickly and accurately find the lesion point at multiple angles, and improve the accuracy and reliability of the diagnosis.

[0107] Example 2

[0108] In a specific embodiment of the present disclosure, an ICE ultrasound probe 200 for generating multiple ultrasound cross-section images is provided. The ICE ultrasound probe 200 for generating multiple ultrasound cross-section images includes the ultrasound transducer 100 described in any of the above embodiments.

[0109] Specifically, Fig.12 As shown, the ICE ultrasound probe 200 for generating multiple ultrasound cross-section images includes a cable 7, a handle 8, a locking wheel 9, a universal steering wheel 11, a catheter 12, and an ultrasonic transducer 100 in the catheter 12. The cable 7 is connected to the host, and includes an ultrasound transceiver channel cable 7 and a control mechanism cable 7, which are used to transmit ultrasound signals and control signals. The handle 8 is for the doctor to hold during the examination, which is convenient for operation. The locking wheel 9 is used to lock the probe steering angle adjusted by the universal steering wheel 11 to ensure the stability of the probe during the examination.

[0110] It should be noted that when the ultrasonic transducer 100 is placed in the internal ultrasonic probe 200, the catheter 12 can be used as the shell 1 of the ultrasonic transducer 100, or the ultrasonic transducer 100 including the shell 1 can be placed in the catheter, which is not limited in this specific embodiment.

[0111] This embodiment introduces a control mechanism and multiple morphologically changeable materials into the ultrasonic transducer of the ultrasonic probe, and designs the multiple morphologically changeable materials as reflective surfaces at multiple different angles. The control mechanism is used to control the states of the multiple morphologically changeable materials to achieve reflection and imaging of ultrasonic signals in different directions, thereby achieving simultaneous display of multiple ultrasonic section images at different angles, which significantly improves the comprehensiveness and efficiency of the examination. Moreover, since the ultrasonic probe can display multiple ultrasonic section images at the same time, the doctor does not need to frequently rotate the probe during the examination, thereby reducing the number of rotations and the impact on the patient. It also helps the doctor to have a more comprehensive understanding of the lesion condition, quickly and accurately find the lesion point at multiple angles, and improve the accuracy and reliability of the diagnosis.

[0112] Example 3

[0113] In a specific embodiment of the present disclosure, an intracardiac ultrasound device is provided, and the intracardiac ultrasound device includes the ICE ultrasound probe 200 for generating multi-ultrasound cross-section images as described in any of the above embodiments.

[0114] Specifically, the intracardiac ultrasound device includes a host, and an ICE ultrasound probe 200 connected to the host for generating multiple ultrasound slice images. The doctor adjusts the position and angle of the ICE ultrasound probe 200 for generating multiple ultrasound slice images through the handle 8 and the locking wheel 9, and uses the universal steering wheel 11 to perform fine bending operations on the probe. The host receives and processes ultrasound signals from the ultrasound transducer 100 through the cable 7, and displays multiple ultrasound slice images in different directions, which helps the doctor to have a more comprehensive understanding of the situation in the cardiac cavity and quickly and accurately find the lesion point.

[0115] This embodiment introduces a control mechanism and multiple morphologically changeable materials into the ultrasonic transducer of the ultrasonic probe, and designs the multiple morphologically changeable materials as reflective surfaces at multiple different angles. The control mechanism is used to control the states of the multiple morphologically changeable materials to achieve reflection and imaging of ultrasonic signals in different directions, thereby achieving simultaneous display of multiple ultrasonic section images at different angles, which significantly improves the comprehensiveness and efficiency of the examination. Moreover, since the ultrasonic probe can display multiple ultrasonic section images at the same time, the doctor does not need to frequently rotate the probe during the examination, thereby reducing the number of rotations and the impact on the patient. It also helps the doctor to have a more comprehensive understanding of the lesion condition, quickly and accurately find the lesion point at multiple angles, and improve the accuracy and reliability of the diagnosis.

[0116] Although the specific embodiments of the present disclosure are described above, those skilled in the art should understand that this is only an example, and the protection scope of the present disclosure is defined by the appended claims. Those skilled in the art may make various changes or modifications to these embodiments without departing from the principles and essence of the present disclosure, but these changes and modifications all fall within the protection scope of the present disclosure.

Claims

1. An ultrasonic transducer, characterized in that: The ultrasonic transducer comprises a control mechanism, a shell, and a transducer array element, an ultrasonic channel switching unit, and a sound-transmitting window located in the shell; The transducer array element is used to transmit and receive ultrasonic signals; The acoustically transparent window is used to transmit the ultrasonic signal; The ultrasonic channel switching unit is composed of a sound-transmitting material layer and N different types of morphologically variable material layers; Wherein, N is a positive integer, N types of the morphology-changing material layers and the sound-transmitting material layers are arranged in sequence, and reflection surfaces with different inclination angles are formed between adjacent material layers, and under different forms of the target morphology-changing material layer, the ultrasonic signal passes through the target reflection surface or is reflected by the target reflection surface to form different transmission echo paths; The control mechanism is used to control each of the morphologically changeable materials to be in different forms at different time points, so that the ultrasound signals at different time points detect the target tissue via different emission echo paths, so as to generate multiple ultrasound section images of the target tissue at different angles.

2. The ultrasonic transducer according to claim 1, characterized in that: When N=1, the morphology-changing material layer includes an electrorheological fluid layer; the ultrasonic transducer also includes an electric field generating device electrically connected to the control mechanism; The electric field generating device forms an electric field when powered on, and the electric field covers a first range where the electrorheological fluid layer is located. Under the action of the electric field, the electrorheological fluid layer changes from a liquid state to a solid state to form a first reflection surface; The control mechanism is used to control the power-on state of the electric field generating device at different time points. The ultrasonic signal detects the target tissue along a preset transmission echo path at a non-power-on time point to generate a first ultrasonic section image of the target tissue. The ultrasonic signal is reflected by the first reflection surface along the first transmission echo path at a power-on time point to detect the target tissue to generate a second ultrasonic section image of the target tissue.

3. The ultrasonic transducer according to claim 1, characterized in that: When N=1, the morphology-changing material layer includes a magnetic fluid layer; the ultrasonic transducer also includes a magnetic field generating device electrically connected to the control mechanism; The magnetic field generating device forms a magnetic field when powered on, and the magnetic field covers the second range where the magnetic fluid layer is located. Under the action of the magnetic field, the magnetic fluid layer changes from a liquid state to a solid state to form a second reflection surface; The control mechanism is used to control the power-on state of the magnetic field generating device at different time points. The ultrasonic signal detects the target tissue along a preset transmission echo path at a non-power-on time point to generate a first ultrasonic section image of the target tissue. The ultrasonic signal is reflected by the second reflection surface along the first transmission echo path at a power-on time point to detect the target tissue to generate a third ultrasonic section image of the target tissue.

4. The ultrasonic transducer according to claim 1, characterized in that: When N=2, the morphology-changing material layer includes an electrorheological fluid layer and a magnetic fluid layer; the ultrasonic transducer also includes an electric field generating device and a magnetic field generating device electrically connected to the control mechanism; The sound-transmitting material layer, the electrorheological fluid layer and the magnetic fluid layer are arranged in sequence along the transmission direction of the ultrasonic signal, and a sound-transmitting diaphragm is provided between the magnetic fluid layer and the electrorheological fluid layer; The sound-transmitting diaphragm is used to isolate the magnetic fluid layer and the electrorheological fluid layer; The electric field generating device forms an electric field when powered on, and the electric field covers a third range where the electrorheological fluid layer is located. Under the action of the electric field, the electrorheological fluid layer changes from a liquid state to a solid state to form a third reflection surface; The magnetic field generating device forms a magnetic field when powered on, and the magnetic field covers a fourth range where the magnetic fluid layer is located. Under the action of the magnetic field, the magnetic fluid layer changes from a liquid state to a solid state to form a fourth reflection surface; The control mechanism is used to control the power-on status of the electric field generating device and the magnetic field generating device at different time points. The ultrasonic signal detects the target tissue along a preset transmission echo path at a time point when the magnetic field generating device and the electric field generating device are both not powered on, so as to generate a first ultrasonic section image of the target tissue. The ultrasonic signal is reflected via the third reflection surface along a third transmission echo path at a time point when the electric field generating device is powered on, so as to generate a fourth ultrasonic section image of the target tissue. The ultrasonic signal is transmitted via the fourth reflection surface along a fourth transmission echo path at a time point when the magnetic field generating device is powered on and the electric field generating device is not powered on, so as to generate a fifth ultrasonic section image of the target tissue.

5. The ultrasonic transducer according to claim 2 or 4, characterized in that: The electric field generating device comprises an electric field positive electrode and an electric field negative electrode; The electric field positive electrode and the electric field negative electrode are arranged on the inner side wall of the shell.

6. The ultrasonic transducer according to claim 5, characterized in that: The electric field positive electrode and the electric field negative electrode are both conductive films; and / or, The negative electric field electrode covers the entire sound-transmitting window.

7. The ultrasonic transducer according to claim 3 or 4, characterized in that: The magnetic field generating device comprises an electromagnetic coil, and the electromagnetic coil is arranged at a preset position of the shell.

8. The ultrasonic transducer according to claim 7, characterized in that: The magnetic field generating device also includes enhanced soft magnetic material; The enhanced soft magnetic material is arranged at a relative position of the electromagnetic coil; The enhanced soft magnetic material is used to enhance the magnetic field generated by the electromagnetic coil.

9. The ultrasonic transducer according to any one of claims 1 to 4, characterized in that: The ultrasonic transducer also includes a channel signal cable and an array element backing material; The transducer array element and the control mechanism are connected to the ultrasound probe handle via the channel signal cable; The array element backing material is used to fix the transducer array element.

10. An ICE ultrasound probe for generating multiple ultrasound slice images, characterized in that: The ICE ultrasound probe for generating a multi-ultrasound slice image comprises the ultrasound transducer according to any one of claims 1 to 9.

11. An intracardiac ultrasound device, characterized in that: The intracardiac ultrasound device comprises the ICE ultrasound probe for generating multi-ultrasound slice images as claimed in claim 10.

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