Ultrasound transducer, ICE ultrasound probe and device generating multi-ultrasound section images

Abstract

The present disclosure provides an ultrasonic transducer, an ICE ultrasonic probe and a device for generating multiple ultrasonic cross-section images. The ultrasonic transducer comprises a control mechanism and an ultrasonic channel switching unit; the ultrasonic channel switching unit is composed of a sound-transmitting material layer and N different types of morphological change material layers; the N morphological change material layers and the sound-transmitting material layer are arranged in sequence, and the reflection surfaces with different inclination angles are formed between adjacent material layers; under different morphologies of the target morphological change material layer, the ultrasonic signal passes through the target reflection surface or the different transmission echo paths formed by reflection via the target reflection surface; the control mechanism is used for controlling each morphological change material to be in different morphologies at different time points, so that the ultrasonic signal at different time points detects the target tissue via different transmission echo paths to generate multiple ultrasonic cross-section images of the target tissue at different angles. The present disclosure can simultaneously display multiple ultrasonic cross-section images at different angles, significantly improving the comprehensiveness and efficiency of the examination.

Description

TECHNICAL FIELD

[0001] The present disclosure relates to the technical field of medical devices, in particular to an ultrasonic transducer, an ICE ultrasonic probe and an apparatus for generating multiple ultrasonic cross-section images. BACKGROUND

[0002] When performing intracardiac echocardiography (ICE) imaging, a conventional ICE probe usually needs to be frequently rotated to change the examination angle so as to obtain more comprehensive diagnostic information. However, this operation mode not only increases the skill requirement for the professional operation method of the doctor, but also increases the work burden of the doctor, and may cause discomfort or potential risks to the patient due to the frequent rotation of the catheter in the blood vessel heart. In addition, single-angle imaging often fails to capture the overall picture of the lesion, affecting the accuracy and efficiency of diagnosis. SUMMARY

[0003] The technical problem to be solved by the present disclosure is to overcome the defects of the conventional ICE probe that the imaging angle is single and cannot ensure comprehensive examination, and to provide an ultrasonic transducer, an ICE ultrasonic probe and an apparatus for generating multiple ultrasonic cross-section images.

[0004] The present disclosure solves the above technical problems by the following technical solutions:

[0005] According to a first aspect of the present disclosure, an ultrasonic transducer is provided, which 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.

[0006] The transducer array element is used for transmitting and receiving ultrasonic signals.

[0007] The sound-transmitting window is used for transmitting the ultrasonic signals.

[0008] The ultrasonic channel switching unit is composed of a sound-transmitting material layer and N different types of morphological change material layers.

[0009] Wherein, N is a positive integer, the N different types of morphological change material layers and the sound-transmitting material layer are arranged in sequence, and the reflection surfaces with different inclination angles are formed between adjacent material layers. Under different morphologies of the target morphological change material layer, the ultrasonic signals pass through the target reflection surface or different transmission echo paths formed by reflection of the target reflection surface.

[0010] The control mechanism is used for controlling each type of 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 via different transmission echo paths to generate multiple ultrasonic cross-section images of the target tissue at different angles.

[0011] Preferably, when N=1, the morphological change material layer comprises an electrorheological fluid layer; the ultrasonic transducer further comprises an electric field generating device electrically connected to the control mechanism;

[0012] The electric field generating device forms an electric field in the energized state, the electric field covering a first range where the electrorheological fluid layer is located, and the electrorheological fluid layer is converted from liquid to solid to form a first reflecting surface under the action of the electric field;

[0013] The control mechanism is used to control the energized state of the electric field generating device at different time points, and the ultrasonic signal detects the target tissue along a preset emission echo path at a non-energized state time point to generate a first ultrasonic cross-section image of the target tissue, and the ultrasonic signal detects the target tissue along a first emission echo path via the first reflecting surface at an energized state time point to generate a second ultrasonic cross-section image of the target tissue.

[0014] Preferably, when N=1, the morphological change material layer comprises a magnetic fluid layer; the ultrasonic transducer further comprises a magnetic field generating device electrically connected to the control mechanism;

[0015] The magnetic field generating device forms a magnetic field in the energized state, the magnetic field covering a second range where the magnetic fluid layer is located, and the magnetic fluid layer is converted from liquid to solid to form a second reflecting surface under the action of the magnetic field;

[0016] The control mechanism is used to control the energized state of the magnetic field generating device at different time points, and the ultrasonic signal detects the target tissue along a preset emission echo path at a non-energized state time point to generate a first ultrasonic cross-section image of the target tissue, and the ultrasonic signal detects the target tissue along a first emission echo path via the second reflecting surface at an energized state time point to generate a third ultrasonic cross-section image of the target tissue.

[0017] Preferably, when N=2, the morphological change material layer comprises an electrorheological fluid layer and a magnetic fluid layer; the ultrasonic transducer further comprises an electric field generating device and a magnetic field generating device electrically connected to the control mechanism;

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

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

[0020] The electric field generating device forms an electric field in the energized state, the electric field covering a third range where the electrorheological fluid layer is located, and the electrorheological fluid layer is converted from liquid to solid to form a third reflecting surface under the action of the electric field;

[0021] The magnetic field generating device forms a magnetic field in the energized state, the magnetic field covers the fourth range where the magnetic fluid layer is located, and the magnetic fluid layer is converted from liquid to solid to form a fourth reflecting surface under the action of the magnetic field;

[0022] The control mechanism is used to control the energized state 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 emission echo path at a time point when neither the electric field generating device nor the magnetic field generating device is energized, to generate a first ultrasonic cross-section image of the target tissue, the ultrasonic signal detects the target tissue along a third emission echo path via the third reflecting surface at a time point when the electric field generating device is energized, to generate a fourth ultrasonic cross-section image of the target tissue, and the ultrasonic signal detects the target tissue along a fourth emission echo path via the fourth reflecting surface at a time point when the magnetic field generating device is energized and the electric field generating device is not energized, to generate a fifth ultrasonic cross-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 electric field negative electrode covers the entire acoustic 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 a reinforced soft magnetic material.

[0030] The reinforced soft magnetic material is arranged at a position opposite to the electromagnetic coil;

[0031] The reinforced 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 back material.

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

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

[0035] According to a second aspect of the present disclosure, there is provided an ICE ultrasonic probe for generating multiple ultrasonic section images, the ICE ultrasonic probe comprising the ultrasonic transducer according to the first aspect of the present disclosure.

[0036] According to a third aspect of the present disclosure, there is provided an intracardiac echocardiography device, the intracardiac echocardiography device comprising the ICE ultrasonic probe for generating multiple ultrasonic section images according to the second aspect of the present disclosure.

[0037] On the basis of common general knowledge in the art, the above-mentioned preferred conditions can be combined in any manner, thereby obtaining various preferred embodiments of the present disclosure.

[0038] The positive progress effect of the present disclosure is that: by introducing a control mechanism and multiple shape-changing materials into the ultrasonic transducer of the ultrasonic probe, and designing the multiple shape-changing materials as multiple reflection surfaces with different angles, the state of the multiple shape-changing materials is controlled by the control mechanism to realize the reflection and imaging of ultrasonic signals in different directions, thereby realizing the simultaneous display of multiple ultrasonic section images with different angles, significantly improving the comprehensiveness and efficiency of the examination, and since the ultrasonic probe can simultaneously display multiple ultrasonic section images, 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 more comprehensively understand the lesion condition, quickly and accurately find the lesion point under multiple angles, and improve the accuracy and reliability of the diagnosis. BRIEF DESCRIPTION OF DRAWINGS

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

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

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

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

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

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

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

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

[0047] Figure 9 Figure 7 is a seventh end view of the ultrasound transducer of Example 1;

[0048] Figure 10 Figure 8 is an eighth end view of the ultrasound transducer of Example 1;

[0049] Figure 11 Figure 9 is a right side view of the electric field generating device and the magnetic field generating device structure of the ultrasound transducer of Example 1;

[0050] Figure 12 Figure 10 is a schematic diagram of the ICE ultrasound probe structure for generating multi-ultrasound cross-section images of Example 2. DETAILED DESCRIPTION

[0051] The present disclosure is further illustrated by the following examples, but is not limited to the examples described.

[0052] In the embodiments of the present disclosure, the prefix words such as "first", "second" are merely used 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 ordinal words such as ordinal words in the embodiments of the present disclosure does not constitute a limitation on the described objects, and the description of the described objects should be referred to the description of the context in the claims or embodiments, and should not constitute an unnecessary limitation because of the use of such prefix words. In addition, in the description of the embodiments, unless otherwise specified, the meaning of "a plurality of" is two or more.

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

[0054] Example 1

[0055] In a specific embodiment of the present disclosure, an ultrasound transducer 100 is provided, as shown in the figure, which comprises a control mechanism (not shown in the figure), a shell 1, and a transducer array element 2, an ultrasound channel switching unit 3, and a sound transmission window 4 in the shell 1. Figure 1

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

[0057] The sound transmission window 4 is used to transmit ultrasonic signals.

[0058] The ultrasound channel switching unit 3 is composed of a sound transmission material layer 31 and N different types of morphological change material layers 32.

[0059] ​Wherein, N is a positive integer, N kinds of morphological change material layers 32 and the sound transmission material layer 31 are arranged in sequence, the reflection surfaces with different inclination angles are formed between adjacent material layers, and different transmission echo paths are formed by the target reflection surface or the reflection of the target reflection surface under different morphologies of the target morphological change material layer 32.

[0060] The control mechanism is used to control each kind of morphological change material to be in different morphologies at different time points, so that the ultrasonic signal at different time points detects the target tissue through different transmission echo paths 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, and the transducer array element 2 in the ultrasonic transducer 100 is used to transmit and receive ultrasonic signals, usually with 64 channels, 128 channels or 256 channels, which can be selected according to the size of the heart cavity to avoid affecting the bending in the heart cavity due to the size being too large.

[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 section images of the target tissue at different angles. The ultrasonic channel switching unit 3 introduces the sound transmission material layer 31 and N kinds of morphological change material layers 32 between the sound transmission window 4 and the inner wall of the shell 1, and the sound transmission material layer 31 and N kinds of morphological change material layers 32 are arranged in sequence along the transmission direction of the ultrasonic signal, wherein N kinds of morphological change material layers 32 can realize the transformation between liquid and solid under certain conditions, such as electrorheological fluid, magnetic fluid, composite material, etc. Each kind of morphological change material layer 32 is separated from each other (such as using a sound transmission diaphragm) to form reflection surfaces 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 penetrate the morphological change material, and when the morphological change material is in a solid state, the ultrasonic signal is reflected by the reflection surface of the morphological change material layer 32 which is transformed into a solid state. It should be noted that the inclination 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 transmission material layer 31 is used to couple the transmission and echo ultrasonic signals of the transducer array element 2. The sound transmission window 4 is the channel for transmitting and echoing ultrasonic signals, usually using an arc-shaped sound window, and the sound transmission material layer 31 and the sound transmission window 4 can transmit the ultrasonic waves emitted by the transducer array element 2 and the echoes of the detected target tissue to each other. The sound transmission material layer 31 and N kinds of morphological change material layers 32 are wrapped inside the shell 1 and the sound transmission window 4 to isolate the physical transmission of blood and protect the electrical insulation of all materials and circuits inside.

[0064] The control mechanism controls the N kinds of morphological change material layers 32 to transform between liquid and solid state under corresponding specific conditions in sequence and continuously, so as to obtain N real-time ultrasonic section images of different angles, which are stored and displayed by the host computer, and then displayed simultaneously on the same screen.

[0065] The embodiment can simultaneously display multiple ultrasonic section images of different angles by introducing the control mechanism and multiple morphological change materials into the ultrasonic transducer 100 of the ultrasonic probe, significantly improving the comprehensiveness and efficiency of the examination. Since the ultrasonic probe can simultaneously display multiple ultrasonic section images, 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, helping the doctor to more comprehensively understand the lesion condition, reducing the strict requirements on the professional skill level of the doctor, quickly and accurately finding the lesion point under multiple angles, and improving the accuracy and reliability of the diagnosis.

[0066] It should be noted that, Figure 1 The number of morphological change materials is illustrative, and the number of morphological change materials can be set according to actual needs, and should not be limited to a maximum of three morphological change materials.

[0067] In one embodiment, as shown in Figures 1-11 The ultrasonic transducer 100 further includes a channel signal cable 5 and an array element back material 6.

[0068] The transducer array element 2 and the control mechanism are connected to the handle of the ultrasonic probe through the channel signal cable 5.

[0069] The array element back 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 back material 6. The transducer array element 2 and the control mechanism are connected to the handle of the ultrasonic probe through the channel signal cable 5 to realize on-off control of the transducer array element 2 and the control mechanism. The array element back material 6 is used to fix the transducer array element 2. The array element back material 6 is combined with the transducer array element 2 and fixed to the corresponding position of the shell 1 by a fixing material.

[0071] In one embodiment, when N = 1, as shown in Figure 2 The morphological change material layer includes an electrorheological fluid layer 321. The ultrasonic transducer 100 further includes an electric field generating device 10 electrically connected to the control mechanism.

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

[0073] The control mechanism is used to control the energization state of the electric field generating device 10 at different time points. The ultrasonic signal detects the target tissue along the preset emission echo path at the time point when the energization state is not activated, so as to generate a first ultrasonic cross-sectional image of the target tissue. The ultrasonic signal detects the target tissue along the first emission echo path via the reflection of the first reflective surface at the time point when the energization state is activated, so as to generate a second ultrasonic cross-sectional image of the target tissue.

[0074] Specifically, if it is necessary to display two ultrasonic cross-sectional images simultaneously in different directions, only one type of morphologically changing material is needed, such as an electrorheological fluid. This electrorheological fluid can change between liquid and solid states under the influence of an electric field. When an electric field is applied, the electrorheological fluid becomes solid and reflects ultrasonic waves; when the electric field is removed, it becomes liquid again, allowing ultrasonic signals to pass through.

[0075] An electric field generating device 10 electrically connected to the control mechanism is installed, and an electrorheological fluid layer 321 is introduced between the acoustic window 4 and the inner wall of the outer shell. The side of the electrorheological fluid layer 321 adjacent to the acoustic material layer 31 is designed with a certain tilt angle. Since the ultrasonic signal emitted by the transducer array element 2 is vertically upward (i.e., in the Y-axis direction), when the electrorheological fluid layer 321 is solid, the ultrasonic signal is reflected by the reflective surface and detects the target tissue along the first emission echo path.

[0076] Therefore, as Figure 3 As shown, when the electric field generating device 10 is not energized, the electrorheological fluid is not affected by the electric field, and the ultrasonic signal γ can freely pass through the acoustic window 4 and be emitted and echoed along the preset emission echo path (i.e., the Y-axis direction) to detect the target tissue. The imaging position of the reflective surface of the target tissue is also in the Y-axis direction. For example... Figure 4 As shown, when the electric field generating device 10 is energized to generate an electric field, the electrorheological fluid transforms into a solid, forming a first reflective surface that reflects the ultrasonic signal γ. This allows the ultrasonic signal γ to be reflected along the first emission echo path to form a second ultrasonic cross-sectional image. Taking an angle of 45 degrees between the first reflective surface and the transducer element 2 as an example, the ultrasonic signal γ, after being reflected by the first reflective surface, transforms into an emission and echo along the X-axis to detect the target tissue. The imaging position of the target tissue's reflective surface is also in the X-axis direction. Therefore, by continuously switching the energizing state of the electric field generating device 10, for example, switching 60 cycles per second (i.e., 120 unidirectional switches), the ICE probe can simultaneously present two ultrasonic cross-sectional images in both the X and Y axes, achieving simultaneous imaging from multiple angles.

[0077] Among them, such as Figures 2-5As shown, the electric field generating device 10 includes an electric field positive pole 101 and an electric field negative pole 102; the electric field positive pole 101 and the electric field negative pole 102 are arranged on the inner side wall of the shell 1. In order to avoid affecting the propagation of the ultrasonic signal, the electric field positive pole 101 and the electric field negative pole 102 are both conductive films, and the thickness is as small as possible, for example, 1 μm, at this time, the influence on the ultrasonic signal propagation is very small, the electric field positive pole 101 film and the electric field negative pole 102 film are plated on the inner wall of the shell 1, and the electric field positive pole 101 film and the electric field negative pole 102 film are connected to the channel signal cable 5 through the lead, that is, the control of the electric field generating device 10 can be realized.

[0078] As a preferred embodiment, the electric field negative pole 102 covers the entire acoustic window 4, ensuring that all ultrasonic signals behave consistently under the action of the electric field to obtain high-quality ultrasonic section images.

[0079] The specific embodiment uses the electrorheological fluid layer 321 and the electric field generating device 10 to realize the function of simultaneously displaying two ultrasonic section images, significantly expands the examination range of the ICE intracardiac ultrasound, reduces the number of rotations, reduces the impact on the patient, and improves the efficiency and accuracy of diagnosis.

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

[0081] The magnetic field generating device 20 forms a magnetic field in the energized state, and the magnetic field covers the second range where the magnetic fluid layer 322 is located, and the magnetic fluid layer 322 is converted from a liquid state to a solid state to form a second reflection surface under the action of the magnetic field;

[0082] The control mechanism is used to control the energized state of the magnetic field generating device 20 at different time points, and the ultrasonic signal detects the target tissue along the preset emission echo path at the non-energized state time point to generate a first ultrasonic section image of the target tissue, and the ultrasonic signal detects the target tissue along the first emission echo path via the second reflection surface at the energized state time point to generate a third ultrasonic section image of the target tissue.

[0083] Specifically, if it is necessary to simultaneously display two ultrasonic section images in different directions, a magnetic fluid can also be used. 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 setting up a magnetic field generating device 20 electrically connected to the control mechanism, and introducing a magnetofluid layer 322 between the sound-transparent window 4 and the inner wall of the outer shell, the side of the magnetofluid layer 322 adjacent to the sound-transparent material layer 31 is designed at a certain tilt angle. When the electrorheological fluid layer 321 is solid, the ultrasonic signal is reflected by the reflective surface and detected along the second emission echo path to detect the target tissue.

[0085] Therefore, when the magnetic field generating device 20 is not powered on, the magnetofluid is unaffected by the magnetic field, and the ultrasonic signal can freely pass through the acoustic window 4 and be emitted and echoed along the preset emission echo path (i.e., the Y-axis direction) to detect the target tissue. The imaging position of the reflective surface of the target tissue is also in the Y-axis direction. When the magnetic field generating device 20 is powered on and generates a magnetic field, the magnetofluid transforms into a solid, forming a second reflective surface that reflects the ultrasonic signal. This allows the ultrasonic signal to be reflected along the second emission echo path to form a third ultrasonic cross-sectional image. Thus, by continuously switching the power-on state of the magnetic field generating device 20, the control mechanism can simultaneously present two ultrasonic cross-sectional images in both the Y-axis and the second emission echo path directions, achieving simultaneous imaging from multiple angles. For example, if the angle between the second reflective surface and the transducer element 2 is 45 degrees, then the direction of the second emission echo path is the X-axis direction.

[0086] Among them, such as Figure 7 As shown, the magnetic field generating device 20 includes an electromagnetic coil 201, which is located at a predetermined position in the housing 1. The electromagnetic coil 201 is connected to the channel signal cable 5 via a lead wire to connect to the handle of the ultrasonic probe. For example, the electromagnetic coil 201 is located on the inner wall of the housing 1 facing the magnetofluid layer 322, so that the magnetic field generated by the electromagnetic coil 201 can cover the magnetofluid layer 322 and control the morphological changes of the magnetofluid layer 322.

[0087] In one specific implementation, such as Figure 7 As shown, the magnetic field generating device 20 also includes a reinforcing soft magnetic material 202;

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

[0089] The 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 a reinforcing soft magnetic material 202 disposed at a position opposite to the electromagnetic coil 201 to assist in enhancing the magnetic field generated by the electromagnetic coil 201. When current is applied to the electromagnetic coil 201, a magnetic path is formed between the generated magnetic field and the reinforcing soft magnetic material 202. The addition of the reinforcing soft magnetic material 202 can enhance and make the magnetic field experienced by the magnetofluid between the two more uniform, thereby reducing the driving current while satisfying the morphological changes of the magnetofluid.

[0091] The embodiment realizes the function of displaying two ultrasonic section images simultaneously by using the magnetic fluid layer 322 and the magnetic field generating device 20, significantly expands the examination range of the ICE intracardiac ultrasound, reduces the number of rotations, reduces the influence on the patient, and improves the efficiency and accuracy of diagnosis.

[0092] In one embodiment, when N = 2, as shown in Figures 8-11 the morphing material layer 32 includes the electrorheological fluid layer 321 and the magnetic fluid layer 322; the ultrasonic transducer 100 further includes the electric field generating device 10 and the magnetic field generating device 20 electrically connected with the control mechanism;

[0093] The acoustic transmission material layer 31, the electrorheological fluid layer 321 and the magnetic fluid layer 322 are sequentially arranged along the transmission direction of the ultrasonic signal, and the magnetic fluid layer 322 and the electrorheological fluid layer 321 are provided with an acoustic transmission diaphragm;

[0094] The acoustic transmission 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 in the energized state, the electric field covers the third range where the electrorheological fluid layer 321 is located, and the electrorheological fluid layer 321 is converted from liquid to solid to form a third reflecting surface under the action of the electric field;

[0096] The magnetic field generating device 20 forms a magnetic field in the energized state, the magnetic field covers the fourth range where the magnetic fluid layer 322 is located, and the magnetic fluid layer 322 is converted from liquid to solid to form a fourth reflecting surface under the action of the magnetic field;

[0097] The control mechanism is used to control the energized state of the electric field generating device 10 and the magnetic field generating device 20 at different time points, and in the state that neither the magnetic field generating device 20 nor the electric field generating device 10 is energized, 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 a preset transmission echo path to generate a first ultrasonic section image of the target tissue; in the state that the electric field generating device 10 is energized, i.e. the electric field positive pole 101 and the electric field negative pole 102 form an electric field covering the electrorheological fluid layer 321 in the energized state, the electrorheological fluid layer 321 is converted from liquid to solid to form a third reflecting surface under the action of the electric field, and the ultrasonic signal is reflected by the third reflecting surface to detect the target tissue along a third transmission echo path to generate a fourth ultrasonic section image of the target tissue; in the state that the magnetic field generating device 20 is energized and the electric field generating device 10 is not energized, the magnetic field generating device 20 forms a magnetic field covering the magnetic fluid layer 322, the magnetic fluid layer 322 is converted from liquid to solid to form a fourth reflecting surface under the action of the magnetic field, and the ultrasonic signal is transmitted along a fourth transmission echo path to detect the target tissue to generate a fifth ultrasonic section image of the target tissue.

[0098] Specifically, considering that the same kind of morphing material will interfere with each other because of the same kind of condition, for example, the ultrasonic 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 controlled to generate an electric field to control the first electrorheological fluid layer to change to 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 will greatly affect the transmission of the ultrasonic signal, so as to be unable to image as required.

[0099] Therefore, when three ultrasonic section images need to be displayed in different directions at the same time, a magnetic fluid and an electrorheological fluid can be selected respectively, and a magnetic field generating device 20 and an electric field generating device 10 are correspondingly provided, and the ultrasonic signal transmission direction of the ultrasonic material layer 31, the electrorheological fluid layer 321 and the magnetic fluid layer 322 is sequentially arranged. Among them, the electrorheological fluid layer 321 and the magnetic fluid layer 322 are separated by the ultrasonic diaphragm to avoid mixing, and since the ultrasonic material layer 31 itself is a solid, it is not necessary to be repeatedly separated, the third reflection surface is formed between the electrorheological fluid layer 321 and the ultrasonic material, and the fourth reflection surface is formed between the magnetic fluid layer 322 and the electrorheological fluid layer 321, and the angle of the third reflection surface and the fourth reflection surface is different. Of course, the positions of the electrorheological fluid layer 321 and the magnetic fluid layer 322 can also be exchanged, which is not limited in the embodiment.

[0100] As shown in Figure 8 , 11 , when the magnetic field generating device 20 and the electric field generating device 10 are both without current, the ICE probe works in the conventional mode, and the transmission direction of the ultrasonic signal γ is the Y-axis direction, and the echo imaging is also along the Y-axis to form the first ultrasonic section image of the target tissue.

[0101] As shown in Figure 9 , 11 , when the electric field positive pole 101 and the electric field negative pole 102 are applied with current, the electrorheological fluid layer 321 changes to a solid state to form a third reflection surface, and the ultrasonic signal γ is reflected along the third transmission echo path to detect the target tissue, and the echo imaging is also along the third transmission echo path to form the fourth ultrasonic section image of the target tissue. 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] As shown in Figures 10-11As shown, when the magnetic field generating device 20 is powered on and the electric field generating device 10 is not powered on, the magnetic fluid layer 322 turns into a solid state to form a fourth reflecting surface, the ultrasonic signal γ passes through the electro-rheological fluid layer 321, is reflected by the fourth reflecting surface, and detects the target tissue along a fourth transmission echo path, and the echo imaging also forms a fifth ultrasonic section image of the examined tissue along the fourth transmission echo path.

[0103] For example, when the angle between the third reflecting surface and the transducer element 2 is 30 degrees and the angle between the fourth reflecting surface and the transducer element 2 is 60 degrees, when the magnetic field generating device 20 is powered on and the electric field generating device 10 is not powered on, the ultrasonic signal is reflected at the fourth reflecting surface, according to the reflection law, the incident angle and the reflection angle are the same, and the reflected direction is 120 degrees with respect to the Y axis, and the echo imaging also forms a reflecting 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 reflecting surface, according to the reflection law, the reflected direction is 60 degrees with respect to the Y axis, and the echo imaging also forms a reflecting surface image of the examined tissue at this angle.

[0104] Therefore, 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 section images at different angles can be obtained. After storage and display by the host computer, three ultrasonic section images at different angles can be displayed simultaneously on the same screen.

[0105] The specific embodiment can simultaneously display multiple ultrasonic section images at different angles through the synergistic effect of the electromagnetic coil 201 and the electro-rheological fluid, significantly improving the comprehensiveness and efficiency of the examination. Since multiple ultrasonic section 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 the doctor to more comprehensively understand the lesion condition and improves the accuracy and reliability of the diagnosis.

[0106] The embodiment introduces a control mechanism and multiple shape-changing materials into the ultrasonic transducer 100 of the ultrasonic probe, designs the multiple shape-changing materials as multiple reflecting surfaces at different angles, controls the state of the multiple shape-changing materials by the control mechanism to realize the reflection and imaging of the ultrasonic signal in different directions, and then simultaneously displays multiple ultrasonic section images at different angles, significantly improving the comprehensiveness and efficiency of the examination. Since the ultrasonic probe can simultaneously display multiple ultrasonic section images, 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 also helps the doctor to more comprehensively understand the lesion condition, quickly and accurately find the lesion point, and improve the accuracy and reliability of the diagnosis.

[0107] Embodiment 2

[0108] In an embodiment of the present disclosure, an ICE ultrasound probe 200 for generating multiple ultrasound section images is provided, and the ICE ultrasound probe 200 for generating multiple ultrasound section images comprises the ultrasound transducer 100 according to any one of the above embodiments.

[0109] Specifically, as shown in the figure, the ICE ultrasound probe 200 for generating multiple ultrasound section images comprises a cable 7, a handle 8, a locking wheel 9, a universal steering wheel 11, a catheter 12, and the ultrasound transducer 100 in the catheter 12. The cable 7 is connected to a host computer, including an ultrasound transceiver channel cable 7 and a control mechanism cable 7, for transmitting ultrasound signals and control signals. The handle 8 is held by the doctor during examination, facilitating operation. The locking wheel 9 is used to lock the steering angle of the probe adjusted by the universal steering wheel 11, ensuring the stability of the probe during the examination. Figure 12

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

[0111] In the present embodiment, the control mechanism and the multiple shape-changing materials are introduced into the ultrasound transducer of the ultrasound probe, and the multiple shape-changing materials are designed as multiple reflection surfaces with different angles. The state of the multiple shape-changing materials is controlled by the control mechanism to realize the reflection and imaging of the ultrasound signals in different directions, thereby realizing the simultaneous display of multiple ultrasound section images with different angles, significantly improving the comprehensiveness and efficiency of the examination. Since the ultrasound probe can simultaneously display multiple ultrasound section images, 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 more comprehensively understand the lesion condition, quickly and accurately find the lesion point under multiple angles, and improve the accuracy and reliability of the diagnosis.

[0112] Embodiment 3

[0113] In an embodiment of the present disclosure, an intracardiac ultrasound device is provided, and the intracardiac ultrasound device comprises the ICE ultrasound probe 200 for generating multiple ultrasound section images according to any one of the above embodiments.

[0114] Specifically, the intracardiac ultrasound device comprises a host computer, and the ICE ultrasound probe 200 for generating multiple ultrasound section images connected to the host computer. The doctor adjusts the position and angle of the ICE ultrasound probe 200 for generating multiple ultrasound section images through the handle 8 and the locking wheel 9, and performs fine bending operation on the probe by using the universal steering wheel 11. The host computer receives and processes the ultrasound signals from the ultrasound transducer 100 through the cable 7, displays multiple ultrasound section images with different directions, and helps the doctor to more comprehensively understand the situation inside the heart chamber and quickly and accurately find the lesion point.​

[0115] The embodiment introduces a control mechanism and a plurality of morphological change materials into the ultrasonic transducer of the ultrasonic probe, and designs the plurality of morphological change materials as reflection surfaces of a plurality of different angles, controls the state of the plurality of morphological change materials by the control mechanism, so as to realize the reflection and imaging of the ultrasonic signal in different directions, and then realize the simultaneous display of a plurality of ultrasonic section images of different angles, which significantly improves the comprehensiveness and efficiency of the examination, and since the ultrasonic probe can simultaneously display a plurality of ultrasonic section images, the doctor does not need to frequently rotate the probe during the examination, thereby reducing the rotation times and the influence on the patient, and also helping the doctor to more comprehensively understand the lesion condition, quickly and accurately find the lesion point under 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 illustration, and the protection scope of the present 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 the present disclosure, and 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 includes a control mechanism, a housing, and transducer array elements, an ultrasonic channel switching unit, and a sound-transmitting window located within the housing. The transducer array element is used to transmit and receive ultrasonic signals; The acoustic window is used to transmit the ultrasonic signal; The ultrasonic channel switching unit is composed of a sound-permeable material layer and N different types of morphologically changing material layers; The morphologically changing material layer enables the transformation between liquid and solid states under different conditions; Where N is a positive integer, N types of morphological change material layers and sound-transmitting material layers are arranged sequentially, and reflective surfaces with different tilt angles are formed between adjacent material layers. Under different morphological changes of the target morphological change material layer, the ultrasonic signal passes through the target reflective surface or is reflected by the target reflective surface to form different emission echo paths. The control mechanism is used to control each of the morphologically changing materials to be in different morphologies at different time points, so that the ultrasonic signals at different time points detect the target tissue via different emission echo paths, thereby generating multiple ultrasonic cross-sectional images of the target tissue at different angles.

2. The ultrasonic transducer according to claim 1, characterized in that, When N=1, the morphologically 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 generates an electric field when energized, and the electric field covers a first area where the electrorheological liquid layer is located. Under the action of the electric field, the electrorheological liquid layer changes from a liquid state to a solid state to form a first reflective surface. The control mechanism is used to control the energization state of the electric field generating device at different time points. The ultrasonic signal detects the target tissue along a preset emission echo path at the time point when the device is not energized, so as to generate a first ultrasonic cross-sectional image of the target tissue. The ultrasonic signal detects the target tissue along a first emission echo path after being reflected by the first reflective surface at the time point when the device is energized, so as to generate a second ultrasonic cross-sectional image of the target tissue.

3. The ultrasonic transducer according to claim 1, characterized in that, When N=1, the morphologically changing material layer includes a magnetofluid layer; the ultrasonic transducer also includes a magnetic field generating device electrically connected to the control mechanism; The magnetic field generating device generates a magnetic field when energized, and the magnetic field covers the second area where the magnetofluid layer is located. Under the action of the magnetic field, the magnetofluid layer changes from a liquid state to a solid state to form a second reflective 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 emission echo path at the time point when the power is off, so as to generate a first ultrasonic cross-sectional image of the target tissue. The ultrasonic signal is reflected by the second reflective surface along the first emission echo path at the time point when the power is on, so as to generate a third ultrasonic cross-sectional image of the target tissue.

4. The ultrasonic transducer according to claim 1, characterized in that, When N=2, the morphologically changing material layer includes an electrorheological fluid layer and a magnetofluid 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-permeable material layer, the electrorheological fluid layer, and the magnetofluid layer are arranged sequentially along the emission direction of the ultrasonic signal, and a sound-permeable membrane is provided between the magnetofluid layer and the electrorheological fluid layer. The acoustically permeable membrane is used to isolate the magnetofluid layer and the electrorheological fluid layer; The electric field generating device generates an electric field when energized, and the electric field covers the third area where the electrorheological liquid layer is located. Under the action of the electric field, the electrorheological liquid layer changes from a liquid state to a solid state to form a third reflective surface. The magnetic field generating device generates a magnetic field when energized, and the magnetic field covers the fourth region where the magnetofluid layer is located. Under the action of the magnetic field, the magnetofluid layer changes from a liquid state to a solid state to form a fourth reflective surface. The control mechanism is used to control the energizing state 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 emission echo path at a time point when both the magnetic field generating device and the electric field generating device are not energized, so as to generate a first ultrasonic cross-sectional image of the target tissue. The ultrasonic signal is reflected by the third reflective surface and detected along a third emission echo path at a time point when the electric field generating device is energized, so as to generate a fourth ultrasonic cross-sectional image of the target tissue. The ultrasonic signal is emitted by the fourth reflective surface and detected along a fourth emission echo path at a time point when the magnetic field generating device is energized and the electric field generating device is not energized, so as to generate a fifth ultrasonic cross-sectional image of the target tissue.

5. The ultrasonic transducer according to claim 2 or 4, characterized in that, The electric field generating device includes a positive electric field electrode and a negative electric field electrode; The positive and negative electrodes of the electric field are located on the inner sidewall of the shell.

6. The ultrasonic transducer according to claim 5, characterized in that, Both the positive and negative electrodes of the electric field are conductive thin films. And / or, The negative electrode of the electric field covers the entire acoustic window.

7. The ultrasonic transducer according to claim 3 or 4, characterized in that, The magnetic field generating device includes an electromagnetic coil, which is located at a predetermined position on the housing.

8. The ultrasonic transducer according to claim 7, characterized in that, The magnetic field generating device also includes reinforcing soft magnetic materials; The reinforcing soft magnetic material is disposed at a position relative to the electromagnetic coil; The reinforcing 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 and the control mechanism are connected to the ultrasonic 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 multi-ultrasound cross-sectional images, characterized in that, The ICE ultrasound probe that generates multi-ultrasound cross-sectional images includes an ultrasound transducer as described in any one of claims 1 to 9.

11. An intracardiac ultrasound device, characterized in that, The intracardiac ultrasound device includes the ICE ultrasound probe as described in claim 10, which generates multi-ultrasound cross-sectional images.

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