CN111407313A - Ultrasound transducer and ultrasound imaging device - Google Patents
Ultrasound transducer and ultrasound imaging device Download PDFInfo
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Abstract
本发明实施例公开了一种超声换能器和超声成像装置。所述超声换能器包括：背衬层、压电层、匹配层和结构层；所述背衬层，设置于所述超声换能器的底端；所述压电层，设置于所述背衬层的上方，与所述背衬层贴合；所述匹配层，设置于所述压电层的上方，与所述压电层贴合；所述结构层，设置于所述匹配层的上方，与所述匹配层贴合；其中，所述结构层包括至少一个环形凸起。以实现利用超声换能器在较近的距离范围内进行聚焦，提高超声图像的分辨率的技术效果。
The embodiment of the invention discloses an ultrasonic transducer and an ultrasonic imaging device. The ultrasonic transducer includes: a backing layer, a piezoelectric layer, a matching layer and a structural layer; the backing layer is arranged on the bottom end of the ultrasonic transducer; the piezoelectric layer is arranged on the The top of the backing layer is attached to the backing layer; the matching layer is arranged above the piezoelectric layer and attached to the piezoelectric layer; the structural layer is arranged on the matching layer The upper part is attached to the matching layer; wherein, the structural layer includes at least one annular protrusion. In order to realize the technical effect of using the ultrasonic transducer to focus in a relatively short distance range and improving the resolution of the ultrasonic image.
Description
Technical Field
The embodiment of the invention relates to the imaging technology, in particular to an ultrasonic transducer and an ultrasonic imaging device.
Background
Atherosclerosis is a cardiovascular disease with high mortality, and detection of atherosclerosis relies primarily on ultrasound transducers.
The existing ultrasonic transducer comprises a mechanical curved surface transducer and a planar transducer, wherein the mechanical curved surface transducer is an acoustic lens with a certain curvature manufactured at the front end of the ultrasonic transducer to detect the vascular wall and atheromatous plaque of lesion; the planar transducer is manufactured into an acoustic lens with a plane at the front end of the ultrasonic transducer, the planar transducer can generate a natural far field point in front of the transducer, the distance and the size of a focus are determined by the frequency and the size of the planar transducer, generally, the size of the planar transducer is larger as the focus distance is farther, but if the size of the planar ring energy device is larger, the planar transducer cannot enter a blood vessel, and thus the diseased blood vessel wall and atheromatous plaque cannot be detected.
Disclosure of Invention
The embodiment of the invention provides an ultrasonic transducer and an ultrasonic imaging device, which aim to realize the technical effects of focusing in a relatively short distance range by utilizing the ultrasonic transducer and improving the resolution of an ultrasonic image.
In a first aspect, an embodiment of the present invention provides an ultrasound transducer, including: a backing layer, a piezoelectric layer, a matching layer, and a structural layer; wherein,
the back lining layer is arranged at the bottom end of the ultrasonic transducer;
the piezoelectric layer is arranged above the back lining layer and is attached to the back lining layer;
the matching layer is arranged above the piezoelectric layer and is attached to the piezoelectric layer;
the structural layer is arranged above the matching layer and attached to the matching layer, and the structural layer comprises at least one annular protrusion.
Optionally, the structural layer includes two annular protrusions, and the two annular protrusions form a zigzag structure;
wherein one of the two annular protrusions has a size larger than that of the other annular protrusion, and the annular protrusion having the smaller size is located in a central region of the matching layer.
Optionally, the structural layer includes an annular protrusion and two strip-shaped protrusions;
wherein, the annular bulge is positioned in the central area of the matching layer, and the two strip-shaped bulges are positioned in the two opposite side areas of the matching layer.
Optionally, the width of the structural layer is determined based on fresnel diffraction theorem and the wavelength and focal length of the ultrasonic sound wave of the structural layer.
Optionally, the thickness of the structural layer is determined based on a wavelength of the ultrasonic sound wave, a first propagation speed of the ultrasonic sound wave in water, a second propagation speed of the ultrasonic sound wave in the structural layer, and a phase angle between the ultrasonic sound wave passing through the matching layer and the ultrasonic sound wave passing through the structural layer.
Optionally, the acoustic impedance of the structural layer is determined based on the material density of the material of the structural layer and the first propagation speed, and the acoustic impedance of the structural layer is between the acoustic impedance of the ultrasonic sound wave in water and the acoustic impedance of the ultrasonic sound wave in the matching layer.
Optionally, the thickness of the piezoelectric layer is half of the wavelength of the ultrasonic wave of the piezoelectric layer, wherein the wavelength of the ultrasonic wave of the piezoelectric layer is obtained by dividing the sound velocity of the piezoelectric layer by the frequency of the ultrasonic transducer.
Optionally, the thickness of the matching layer is one quarter of the wavelength of the ultrasonic sound wave of the matching layer, where the wavelength of the ultrasonic sound wave of the matching layer is obtained by dividing the sound velocity of the matching layer by the frequency of the ultrasonic transducer.
Optionally, the annular protrusion is of a hollow or solid structure; the annular protrusion comprises at least one of a square protrusion, a circular protrusion, a triangular protrusion or a star-shaped protrusion.
In a second aspect, an embodiment of the present invention further provides an ultrasound imaging apparatus, including: a connector, a catheter and an ultrasound transducer according to any of the embodiments of the present invention; wherein,
the catheter is electrically connected with the ultrasonic transducer;
one end of the connector is electrically connected with the catheter, and the other end of the connector is electrically connected with the ultrasonic imaging system and the rotary withdrawing device respectively.
According to the technical scheme, the ultrasonic transducer is designed, the ultrasonic transducer comprises a back lining layer, a piezoelectric layer and a matching layer, a structural layer attached to the matching layer is arranged above the matching layer, ultrasonic waves generated by the ultrasonic transducer can be regulated and controlled through the structural layer, and the structural layer comprises at least one annular bulge, so that the focusing effect similar to that of a radian focusing transducer can be achieved, the wave beam at the focus position of the ultrasonic waves is narrowed, and the ultrasonic images with high imaging resolution and definition are obtained.
Drawings
Fig. 1 is a schematic structural diagram of an ultrasonic transducer in a first embodiment of the present invention;
fig. 2 is a schematic structural diagram of an ultrasonic transducer in a first embodiment of the present invention;
fig. 3 is another schematic structural diagram of an ultrasonic transducer in the first embodiment of the present invention;
FIG. 4 is a schematic diagram illustrating the determination of the width of a structural layer in a second embodiment of the present invention;
FIG. 5 is an analog schematic diagram of an ultrasound transducer utilizing an embodiment of the present invention in a second embodiment of the present invention;
fig. 6 is a schematic structural diagram of an ultrasonic imaging apparatus in a third embodiment of the present invention;
fig. 7 is a schematic cross-sectional structure diagram of an ultrasonic imaging apparatus in a third embodiment of the invention;
fig. 8 is a schematic diagram of the operation of an ultrasonic imaging apparatus in the third embodiment of the present invention.
Detailed Description
The present invention will be described in further detail with reference to the accompanying drawings and examples. It is to be understood that the specific embodiments described herein are merely illustrative of the invention and are not limiting of the invention. It should be further noted that, for the convenience of description, only some of the structures related to the present invention are shown in the drawings, not all of the structures.
Example one
Fig. 1 is a schematic structural diagram of an ultrasound transducer according to an embodiment of the present invention, and as shown in fig. 1, the ultrasound transducer 1 includes: backing layer 10, piezoelectric layer 11, matching layer 12 and structural layer 13; the backing layer 10 is arranged at the bottom end of the ultrasonic transducer; the piezoelectric layer 11 is arranged above the backing layer 10 and is attached to the backing layer 10; the matching layer 12 is arranged above the piezoelectric layer 11 and is attached to the piezoelectric layer 11; and the structural layer 13 is arranged above the matching layer 12 and is attached to the matching layer 12, and the structural layer 13 comprises at least one annular bulge.
As shown in fig. 1, the backing layer 10 can be located at the bottom end of the ultrasonic transducer 1 as a substrate, and the thickness and the number of layers can be set according to the user's needs, which is not limited herein. The structure of the backing layer 10 may be square as shown in fig. 1, or may be any other polygonal shape such as a circle, a triangle, or a star, which is not limited herein. Meanwhile, the structure of the backing layer 10 may be a solid structure or a hollow structure, which is not limited herein.
For example, the material of the piezoelectric layer can be piezoelectric ceramics, piezoelectric single crystal, piezoelectric composite material and other materials that can be used for the ultrasonic transducer fabrication.
Alternatively, the structure of the piezoelectric layer 11 may also be square as shown in fig. 1, and may also be any other polygonal shape such as a circle, a triangle, or a star, which is not limited herein. Meanwhile, the structure of the piezoelectric layer 11 may be a solid structure or a hollow structure, which is not limited herein. The number of layers of the piezoelectric layer 11 can be set according to the user's requirement, and is not limited herein.
Illustratively, the plane where the piezoelectric layer 11 and the backing layer 10 are attached may be square as shown in fig. 1, and may also be any other polygonal shape such as a circle, a triangle, or a star, which is not limited herein.
In the embodiment of the present invention, optionally, the number of the matching layers 12 may be one layer, two layers, or multiple layers, and the specific number of the matching layers may be set according to the user requirement, which is not limited herein. The matching layer 12 may have a square shape as shown in fig. 1, or may have any other polygonal shape such as a circle, a triangle, or a star shape, which is not limited herein. Meanwhile, the structure of the matching layer 12 may be a solid structure or a hollow structure, which is not limited herein.
For example, the plane where the piezoelectric layer 11 and the matching layer 12 are attached may be square as shown in fig. 1, and may also be any other polygonal shape such as a circle, a triangle, or a star, which is not limited herein.
Similarly, the number of structural layers 13 may be one layer, two layers, or more than two layers. It can be understood that the more the number of structural layers is, the more flexible the regulation performance of the ultrasonic sound wave is. However, the number of layers of the structural layer 13 may be determined according to the size limit of the ultrasonic transducer and the manufacturing process of the structural layer in consideration of the technical limit in implementation.
Alternatively, the structure of the structural layer 13 may also be square as shown in fig. 1, and may also be in the shape of any other polygon such as a circle, a triangle, or a star, which is not limited herein. Meanwhile, the structure of the structural layer 13 may be a solid structure or a hollow structure, which is not limited herein. For example, the plane where the matching layer 12 and the structural layer 13 are attached may be square as shown in fig. 1, and may also be any other polygonal shape such as a circle, a triangle, or a star, which is not limited herein.
It should be noted that the joint surfaces between the backing layer 10, the piezoelectric layer 11, the matching layer 12, and the structural layer 13 may be the same shape as shown in fig. 1, or may be different shapes from each other, which is not limited herein, and meanwhile, the backing layer 10, the piezoelectric layer 11, the matching layer 12, and the structural layer 13 may also be all solid structures, or all hollow structures, or one or more of them may be a solid structure, or another plurality or one of them may be a hollow structure, which is not limited herein.
Similarly, the plane where the piezoelectric layer 11 and the backing layer 10 are attached, the plane where the piezoelectric layer 11 and the matching layer 12 are attached, and the plane where the matching layer 12 and the structural layer 13 are attached may be the same shape as shown in fig. 1, or may be different shapes, and are not limited herein.
At least one annular protrusion in the structural layer 13, the number of the annular protrusions may be one, two or more, and is not limited herein.
The annular bulge can regulate and control the ultrasonic sound waves, can achieve a focusing effect similar to that of the radian focusing transducer, and enables the wave beams at the ultrasonic sound wave focus position to be narrowed, so that the ultrasonic image with high imaging resolution and high definition is obtained.
Optionally, the structural layer 13 includes two annular protrusions, and the two annular protrusions form a zigzag structure; wherein one of the two annular protrusions has a size larger than that of the other annular protrusion, and the annular protrusion having the smaller size is located in a central region of the matching layer.
Illustratively, a schematic structural diagram of the ultrasonic transducer described with reference to fig. 2, wherein a in fig. 2 is a front view of the ultrasonic transducer, the diagram b in fig. 2 is a top view of the ultrasound transducer, the diagram c in fig. 2 is a side view of the ultrasound transducer, as shown in fig. 2, the structural layer 13 has two annular protrusions 131 and 132, the size of the annular protrusion 131 is different from that of the annular protrusion 132, the size of the annular protrusion 131 is smaller, the size of the annular protrusion 132 is larger, the annular protrusion 131 and the annular protrusion 132 can form a zigzag structure, i.e., the centers of the annular protrusion 131 and the annular protrusion 132 coincide, the annular protrusion 131 having a smaller size is positioned inside the annular protrusion 132 having a larger size, the annular protrusion 131 having a smaller size is positioned in a central region of the matching layer 12, for example, it may be that the centers of the annular projection 131 and the annular projection 132 are located at the center position of the matching layer 12. Thus, the annular protrusion 131 and the annular protrusion 132 in the structural layer 13 can regulate and control the ultrasonic sound wave, and can achieve a focusing effect similar to that of a radian focusing transducer, so that the wave beam at the focus position of the ultrasonic sound wave becomes narrow, and an ultrasonic image with high imaging resolution and high definition is obtained.
The annular protrusion 131 and the annular protrusion 132 may be identical or different in shape. As an alternative embodiment of the present invention, both the annular protrusion 131 and the annular protrusion 132 may have a square shape. Further, the annular protrusion 131 may have a solid square block structure, and the annular protrusion 132 may have a hollow square block structure.
It should be noted that fig. 2 only shows the structural layer including two annular protrusions, but the structural layer is not limited to include only two annular structures, for example, the annular protrusion 131 may be a hollow square structure, and at least one hollow or solid annular protrusion may be disposed inside the annular protrusion 131. Of course, an annular projection structure may also be provided between the annular projection 131 and the annular projection 132.
In the embodiment of the present invention, the structural layer 13 further includes strip-shaped protrusions, and in order to make the focusing position of the ultrasonic transducer correspond to the central position of the ultrasonic transducer as much as possible, the number of the strip-shaped protrusions may be set to be even, and the strip-shaped protrusions are symmetrically arranged above the matching layer 12. For example, when the matching layer has a square shape, the stripe-shaped protrusions may be respectively provided at edge regions of opposite sides of the matching layer 12.
Optionally, the structural layer 13 includes an annular protrusion and two strip-shaped protrusions; wherein, the annular bulge is positioned in the central area of the matching layer, and the two strip-shaped bulges are positioned in the two opposite side areas of the matching layer.
Illustratively, referring to fig. 3, another structural schematic diagram of the ultrasonic transducer, a in fig. 3 is a front view of the ultrasonic transducer, b in fig. 3 is a top view of the ultrasonic transducer, c in fig. 3 is a side view of the ultrasonic transducer, as shown in fig. 3, the structural layer 13 includes an annular protrusion 134 and two strip-shaped protrusions 135, the annular protrusion 134 is located in a central region of the matching layer 12, for example, the center of the annular protrusion 134 is located in the central position of the matching layer 12, the two strip-shaped protrusions 135 are located in two opposite side regions of the matching layer, for example, as shown in fig. 3, the two strip-shaped protrusions 135 are located in two opposite left and right side regions of the matching layer, and of course, may also be located in two opposite upper and lower side regions of the matching layer, such that one annular protrusion 134 and two strip-shaped protrusions 135 in the structural layer 13 can modulate ultrasonic sound waves, the focusing effect similar to that of the radian focusing transducer can be achieved, the wave beam at the ultrasonic sound wave focus position is narrowed, and therefore the ultrasonic image with high imaging resolution and definition can be obtained.
It should be noted that fig. 3 only shows the case where the structural layer includes one annular protrusion and two strip-shaped protrusions, but the structural layer is not limited to include only one annular protrusion and two strip-shaped protrusion structures, for example, one annular protrusion 134 may be a hollow square block structure, and at least one hollow or solid annular protrusion may be disposed inside the annular protrusion 134. Of course, it is also possible to provide an annular projection structure or a bar-shaped projection structure between the annular projection 134 and the two bar-shaped projections 135.
It will be understood that fig. 2 and 3 illustrate two possible configurations of the structural layer 13, and that in practical applications, the configuration of fig. 2 or 3 may be used, where fig. 2 and 3 illustrate that the protrusions of fig. 2 and 3 are interchangeable with the planar portions of the matching layer, and that the protrusions of fig. 3 are protrusions of the planar portions of the matching layer of fig. 2, and the annular protrusions 131 and 132 of fig. 2 are recessed to form the configuration of fig. 3.
Optionally, the annular protrusion is of a hollow or solid structure. Illustratively, the annular protrusion may include at least one of a square protrusion, a circular protrusion, a triangular protrusion, or a star-shaped protrusion, which may be set by a user according to a requirement, but is not limited thereto.
The design of the annular bulge mainly takes the Fresnel diffraction principle into consideration, because the light source or the sound wave can be diffracted under the condition that the distance between the light source or the sound wave and the obstacle is limited, the Fresnel diffraction is generated by the small holes, the slits and the like, therefore, when the annular bulge is designed, the annular bulge can be designed into at least one closed square bulge, triangular bulge or star-shaped bulge and the like, the slits can be formed among the at least one square bulge, the triangular bulge or the star-shaped bulge and the like, the ultrasonic sound wave can be diffracted, or the annular bulge can be designed into the circular bulge, the circular bulge forms the small holes and the ultrasonic sound wave can be diffracted, the ultrasonic sound wave can be regulated and controlled by utilizing the Fresnel diffraction theorem formula (Fresnel half-wave band method), and the focusing effect similar to that of the radian focusing transducer can be achieved, the technical effect of improving the resolution of the ultrasonic image. According to the technical scheme, the ultrasonic transducer is designed, the ultrasonic transducer comprises a back lining layer, a piezoelectric layer and a matching layer, a structural layer attached to the matching layer is arranged above the matching layer, ultrasonic waves generated by the ultrasonic transducer can be regulated and controlled through the structural layer, and the structural layer comprises at least one annular bulge, so that the focusing effect similar to that of a radian focusing transducer can be achieved, the wave beam at the focus position of the ultrasonic waves is narrowed, and the ultrasonic images with high imaging resolution and definition are obtained.
Example two
On the basis of the technical solutions of the above embodiments, optionally, the width of the structural layer 13 is determined based on the fresnel diffraction theorem and the wavelength and the focal length of the ultrasonic sound wave of the structural layer 13.
Illustratively, the wavelength of the ultrasonic sound wave is related to the material used for the structural layer 13 and the frequency of the ultrasonic sound wave emitted by the ultrasonic transducer, based on the formula: λ ═ c/f, where λ is the wavelength of the ultrasonic wave, c is the sound velocity of the ultrasonic wave, and f is the frequency of the ultrasonic wave emitted by the ultrasonic transducer, in practical application, the frequency of the ultrasonic wave emitted by the ultrasonic transducer is generally 20-100MHz, and the material used for the structural layer 13 may be a resin material, an acrylic material, a rubber material, an organosilicon material, or a photoresist material with similar acoustic parameters. The focal distance is related to practical application, for example, intravascular ultrasound mainly detects objects in a 1mm-3mm area of the front end of the ultrasonic transducer, and since the blood vessel wall is approximately in the 1mm-3mm area of the front end of the ultrasonic transducer, the focal distance can be set to 2mm in general.
Illustratively, taking the structure of the ultrasonic transducer shown in fig. 2 as an example, referring to the width determination diagram of the structural layer shown in fig. 4, according to the fresnel diffraction theorem, when the structural layer of the ultrasonic transducer satisfies the following formula, the ultrasonic transducer can focus the ultrasonic sound wave at a preset position (for example, at a focal length of 2 mm), form a focal point,
Wi(i＝1)＝Ri，Wi(i＞1)＝Ri-Rj(j ═ i-1), where RnIndicates the width of the nth fresnel zone (i.e., the raised regions D1 and D2 in fig. 4); λ represents the wavelength of the ultrasonic sound wave emitted by the ultrasonic transducer; f denotes the focal length of the ultrasonic sound wave; wi(i ═ 1) represents half of the side length of the central annular projection (i.e. half of D1 in fig. 4); wi(i > 1) indicates the widths of the other annular protrusions (i.e., W1 and W2 in FIG. 4) except for the central annular protrusion; riRepresents one half of the side length, R, of the i-th annular projectionjRepresenting half the side length of the jth annular projection.
Illustratively, based on the above fresnel diffraction theorem equation, the widths of the annular protrusions and the slits between the annular protrusions in fig. 4 can be determined based on the following equation:
wherein λ is the wavelength of the ultrasonic sound wave, and F is the focal length of the ultrasonic sound wave.
Based on the above calculation method, the width of the structural layer can be determined, so that the annular bulge of the structural layer can be designed based on the determined width of the structural layer, the ultrasonic sound wave can be regulated and controlled through the annular bulge, a focusing effect similar to that of the radian focusing transducer can be achieved, the wave beam at the focus position of the ultrasonic sound wave is narrowed, and the ultrasonic image with high imaging resolution and high definition can be obtained.
Optionally, the thickness of the structural layer 13 is determined based on the wavelength of the ultrasonic sound wave, the first propagation velocity of the ultrasonic sound wave in water, the second propagation velocity of the ultrasonic sound wave in the structural layer 13, and the phase angle between the ultrasonic sound wave passing through the matching layer 12 and the ultrasonic sound wave passing through the structural layer 13.
For example, the first propagation speed may be a propagation speed of ultrasonic sound waves in water; the second propagation velocity may be a propagation velocity of the ultrasonic sound wave in the structural layer; based on the wavelength of the ultrasonic sound wave, the first propagation velocity of the ultrasonic sound wave in water, the second propagation velocity of the ultrasonic sound wave in the structural layer 13, and the phase angle between the ultrasonic sound wave passing through the matching layer 12 and the ultrasonic sound wave passing through the structural layer 13, the thickness of the structural layer can be determined by the following formula:
wherein, c0Is the first propagation velocity of the ultrasonic sound wave, c1Is the second propagation velocity of the ultrasonic sound wave, h is the thickness of the structural layer,
is the phase angle between the ultrasonic sound wave passing through the matching layer and the ultrasonic sound wave passing through the structural layer.
It should be noted that ultrasound is used for ultrasoundThe structural layer of the energy device can realize phase regulation and control of ultrasonic sound waves, the ultrasonic sound waves passing through the matching layer are regulated ultrasonic sound waves, the ultrasonic sound waves passing through the structural layer are ultrasonic sound waves which are not regulated, and in actual application, the structural layer realizes that the waveform of the ultrasonic sound waves is delayed by one quarter of a period, namely when the structural layer is used as a power source, the structural layer can realize phase regulation and control of the ultrasonic sound waves, the ultrasonic sound waves passing through the matching layer
And the structural layer can regulate and control the focusing effect of the ultrasonic sound waves to be optimal.
Through foretell calculation mode, confirm the thickness of structural layer, can design the annular bulge of structural layer like this based on the thickness of the structural layer of confirming, regulate and control the ultrasonic sound wave through the annular bulge, can reach the focusing effect similar with radian focus transducer for the wave beam at ultrasonic sound wave focus position narrows, thereby obtains the ultrasonic image of high imaging resolution and definition.
Optionally, the acoustic impedance of the structural layer 13 is determined based on the material density of the material of the structural layer 13 and the first propagation speed, and the acoustic impedance of the structural layer 13 is between the acoustic impedance of the ultrasonic sound wave in water and the acoustic impedance of the ultrasonic sound wave in the matching layer 12.
Illustratively, the acoustic impedance of the structural layer 13 is based on the material density of the structural layer material and the first propagation velocity, and may be determined according to the following equation: where Z is the acoustic impedance of the structural layer, ρ is the material density of the material used in the structural layer, and c is the first propagation velocity, i.e., the propagation velocity of the ultrasonic sound wave in water. The acoustic impedance of the structural layer 13 is between the acoustic impedance of the ultrasonic sound wave in water and the acoustic impedance of the ultrasonic sound wave in the matching layer 12, and may be ZWater (W)＜ZStructural layer＜ZMatching layer. Therefore, the annular bulge on the structural layer can be designed according to the acoustic impedance of the structural layer, the ultrasonic sound wave is regulated and controlled through the annular bulge, the focusing effect similar to that of the radian focusing transducer can be achieved, the wave beam at the focus position of the ultrasonic sound wave is narrowed, and the ultrasonic image with high imaging resolution and high definition is obtained. Optionally, the thickness of the piezoelectric layer 11 is half of the wavelength of the ultrasonic sound wave of the piezoelectric layer 11Wherein the wavelength of the ultrasonic acoustic wave of the piezoelectric layer 11 is obtained by dividing the sound velocity of the piezoelectric layer 11 by the frequency of the ultrasonic transducer.
Illustratively, the wavelength of the ultrasonic sound wave of the piezoelectric layer 11 is obtained by dividing the sound velocity of the piezoelectric layer 11 by the frequency of the ultrasonic transducer. Specifically, the acoustic velocity of the piezoelectric layer 11 may be divided by the frequency of the ultrasonic transducer to obtain the wavelength of the ultrasonic wave of the piezoelectric layer 11, and then a half of the wavelength of the ultrasonic wave may be used as the thickness of the piezoelectric layer 11.
Optionally, the thickness of the matching layer 12 is one quarter of the wavelength of the ultrasonic sound wave of the matching layer 12, wherein the wavelength of the ultrasonic sound wave of the matching layer 12 is obtained by dividing the sound velocity of the matching layer 12 by the frequency of the ultrasonic transducer.
Illustratively, the wavelength of the ultrasonic sound wave of the matching layer 12 is obtained by dividing the sound velocity of the matching layer 12 by the frequency of the ultrasonic transducer. Specifically, the sound velocity of the matching layer 12 may be divided by the frequency of the ultrasonic transducer to obtain the wavelength of the ultrasonic sound wave of the matching layer 12, and then a quarter of the wavelength of the ultrasonic sound wave may be used as the thickness of the matching layer 12.
The thickness of the piezoelectric layer 11 and the thickness of the matching layer 12 enable ultrasonic waves emitted by the ultrasonic transducer to be focused into a focus at a preset position even if part of the annular bulge in the structural layer is missing, and a focusing effect similar to that of the radian focusing transducer can be achieved, so that beams at the ultrasonic wave focus position are narrowed, and an ultrasonic image with high imaging resolution and high definition is obtained.
Referring to the simulation diagram of the ultrasonic transducer using the embodiment of the present invention described in fig. 5, as shown in fig. 5, the finite element software COMSO L is used to perform simulation on the ultrasonic transducer in the embodiment of the present invention, specifically, a focus diagram generated at a preset position right in front of the planar ultrasonic transducer in the prior art and the ultrasonic transducer in the embodiment of the present invention is observed on two cross sections perpendicular to the planar ultrasonic transducer in the prior art and the ultrasonic transducer in the embodiment of the present invention, respectively, where a diagram in fig. 5 is a focus generated by the planar ultrasonic transducer in the prior art, and b diagram in fig. 5 is a focus generated by the ultrasonic transducer in the embodiment of the present invention.
According to the technical scheme of the embodiment of the invention, the width of the structural layer 13 is determined based on the Fresnel diffraction theorem and the wavelength and the focal length of the ultrasonic sound wave of the structural layer 13, so that the annular bulge of the structural layer can be designed based on the determined width of the structural layer, the ultrasonic sound wave is regulated and controlled through the annular bulge, the focusing effect similar to that of a radian focusing transducer can be achieved, the wave beam at the focus position of the ultrasonic sound wave is narrowed, and the ultrasonic image with high imaging resolution and high definition is obtained. . The thickness of structural layer 13 is based on the wavelength of supersound sound wave, the first propagation speed of supersound sound wave in aqueous, the second propagation speed of supersound sound wave in structural layer 13, and through matching layer 12 the supersound sound wave with through structural layer 13 phase angle between the supersound sound wave is confirmed, can design the annular of structural layer protruding like this based on the thickness of the structural layer of confirming, adjusts and controls the supersound sound wave through the annular is protruding, can reach the similar focusing effect with radian focus transducer for the wave beam of supersound sound wave focus position narrows, thereby obtains the ultrasonic image of high imaging resolution and definition. The acoustic impedance of structural layer 13 is based on the material density of structural layer 13 material with first speed of transmission confirms, and the acoustic impedance of structural layer 13 is located the acoustic impedance of ultrasonic sound wave in aqueous with the acoustic impedance of ultrasonic sound wave is between the matching layer 12, can design the annular arch on the structural layer according to the acoustic impedance of structural layer like this, adjusts and controls ultrasonic sound wave through the annular arch, can reach the similar focusing effect with radian focus transducer for the wave beam of ultrasonic sound wave focus position narrows, thereby obtains the ultrasonic image of high imaging resolution and definition. The thickness of the piezoelectric layer 11 is half of the wavelength of the ultrasonic wave of the piezoelectric layer 11, wherein the wavelength of the ultrasonic wave of the piezoelectric layer 11 is obtained by dividing the sound velocity of the piezoelectric layer 11 by the frequency of the ultrasonic transducer, and the thickness of the matching layer 12 is one quarter of the wavelength of the ultrasonic wave of the matching layer 12, wherein the wavelength of the ultrasonic wave of the matching layer 12 is obtained by dividing the sound velocity of the matching layer 12 by the frequency of the ultrasonic transducer, so that even if part of the annular bulge in the structural layer is absent, the ultrasonic wave emitted by the ultrasonic transducer can be focused into a focus at a preset position, a focusing effect similar to that of an arc focusing transducer can be achieved, the wave beam at the focus position of the ultrasonic wave becomes narrow, and an ultrasonic image with high imaging resolution and definition is obtained.
EXAMPLE III
Fig. 6 is a schematic structural diagram of an ultrasound imaging apparatus according to a third embodiment of the present invention, and as shown in fig. 6, the ultrasound imaging apparatus includes: a connector 3, a catheter 2, and the ultrasonic transducer 1 according to any of the embodiments of the present invention; wherein, the catheter 2 is electrically connected with the ultrasonic transducer 1; one end of the connector 3 is electrically connected with the catheter 2, and the other end of the connector is electrically connected with the ultrasonic imaging system and the rotary withdrawing device respectively.
Alternatively, referring to the schematic cross-sectional structure of the ultrasonic imaging apparatus shown in fig. 7, as shown in fig. 7, a metal hose 21 and a coaxial cable 22 are provided inside the catheter 2; wherein, the metal hose 21 is a hollow helical structure; the coaxial cable 22 penetrates through the cavity of the metal hose 21, and has one end electrically connected to the ultrasonic transducer 1 and the other end electrically connected to the connector 3.
Optionally, a positioning module may be further provided in the catheter 2 for positioning the ultrasound transducer 1 to guide the ultrasound transducer to move to the vessel wall where the lesion is located and to the location where the atheroma is located.
Optionally, as shown in fig. 6, a water filling port 31 may be further disposed on the connector 3, and the water filling port 31 may be used for filling water into the ultrasound imaging apparatus.
Referring to the operation schematic diagram of the ultrasonic imaging device described in fig. 8, 100 is a blood vessel, B1 is a normal blood vessel map, and B2 is a blood vessel map with atherosclerotic plaque, the ultrasonic imaging device provided in the embodiment of the present invention can be used for intravascular ultrasonic work, and is inserted into a suspected lesion position in a blood vessel of a human body by using an ultrasonic transducer mounted on the tip of a catheter to perform two-dimensional tissue imaging, which not only can display the morphology of the inner wall of the blood vessel in real time, but also can measure the size of the lesion through tissue plane analysis and three-dimensional reconstruction, thereby providing a new visual field for deep understanding of the morphology and function of the blood vessel lesion, and providing more accurate and reliable information for clinical diagnosis and treatment. By utilizing the ultrasonic imaging device, the lumen morphology and the vessel wall information can be displayed based on the intravascular ultrasonic technology, the histomorphology characteristics of atherosclerotic plaques can be preliminarily determined, meanwhile, the diameter, the cross-sectional area and the stenosis degree of blood vessels are measured through accurate quantitative analysis, early atherosclerotic lesions which cannot be found by angiography can be identified, particularly critical lesions displayed by angiography, and the intravascular ultrasonic imaging device can be used for carrying out accurate quantitative analysis on the atherosclerotic plaques based on the intravascular ultrasonic technology to determine the stenosis degree and the lesion type of the atherosclerotic plaques so as to assist the selection of clinical treatment schemes. The ultrasonic imaging device has very important application value in the aspect of guiding coronary artery interventional therapy based on the intravascular ultrasonic technology. Because the technology can accurately reflect the conditions of the internal appearance of the blood vessel, the nature and the severity of the lesion and the like, the technology provides a basis for selecting the correct treatment strategy, such as selecting a stent with proper size and the like. Meanwhile, the ultrasonic imaging device can be used for evaluating the treatment effect of the postoperative stent based on the intravascular ultrasonic technology, such as whether the stent is expanded fully, adheres to the wall completely, is uniformly unfolded and covers lesion completely, and the like, so that certain problems existing after the stent is implanted can be found and corrected in time, and the optimal interventional treatment effect can be achieved.
The ultrasonic imaging device provided by the embodiment of the invention comprises the ultrasonic transducer provided by any embodiment of the invention, and has corresponding modules and beneficial effects of the ultrasonic transducer. Meanwhile, the ultrasonic imaging device provided by the embodiment of the invention improves the resolution and definition of the ultrasonic imaging in the blood vessel of the conventional ultrasonic imaging device, and can obtain better image resolution and definition.
It is to be noted that the foregoing is only illustrative of the preferred embodiments of the present invention and the technical principles employed. It will be understood by those skilled in the art that the present invention is not limited to the particular embodiments described herein, but is capable of various obvious changes, rearrangements and substitutions as will now become apparent to those skilled in the art without departing from the scope of the invention. Therefore, although the present invention has been described in greater detail by the above embodiments, the present invention is not limited to the above embodiments, and may include other equivalent embodiments without departing from the spirit of the present invention, and the scope of the present invention is determined by the scope of the appended claims.
Claims (10)
1. An ultrasonic transducer, comprising: a backing layer, a piezoelectric layer, a matching layer, and a structural layer; wherein,
the back lining layer is arranged at the bottom end of the ultrasonic transducer;
the piezoelectric layer is arranged above the back lining layer and is attached to the back lining layer;
the matching layer is arranged above the piezoelectric layer and is attached to the piezoelectric layer;
the structural layer is arranged above the matching layer and attached to the matching layer, and the structural layer comprises at least one annular protrusion.
2. The ultrasonic transducer of claim 1, wherein the structural layer comprises two annular protrusions, the two annular protrusions forming a chevron-shaped structure;
wherein one of the two annular protrusions has a size larger than that of the other annular protrusion, and the annular protrusion having the smaller size is located in a central region of the matching layer.
3. The ultrasonic transducer of claim 1, wherein the structural layer comprises one annular protrusion and two strip-shaped protrusions;
wherein, the annular bulge is positioned in the central area of the matching layer, and the two strip-shaped bulges are positioned in the two opposite side areas of the matching layer.
4. The ultrasonic transducer of claim 1, wherein the width of the structural layer is determined based on fresnel diffraction theorem and the wavelength and focal length of the ultrasonic sound waves of the structural layer.
5. The ultrasonic transducer of claim 4, wherein the thickness of the structural layer is determined based on a wavelength of the ultrasonic sound wave, a first propagation velocity of the ultrasonic sound wave in water, a second propagation velocity of the ultrasonic sound wave in the structural layer, and a phase angle between the ultrasonic sound wave passing through the matching layer and the ultrasonic sound wave passing through the structural layer.
6. The ultrasonic transducer of claim 5, wherein the acoustic impedance of the structural layer is determined based on the material density of the structural layer material and the first propagation speed, the acoustic impedance of the structural layer being between the acoustic impedance of the ultrasonic sound wave in water and the acoustic impedance of the ultrasonic sound wave in the matching layer.
7. The ultrasonic transducer of claim 1, wherein the thickness of the piezoelectric layer is half the wavelength of the ultrasonic wave of the piezoelectric layer, wherein the wavelength of the ultrasonic wave of the piezoelectric layer is obtained by dividing the acoustic velocity of the piezoelectric layer by the frequency of the ultrasonic transducer.
8. The ultrasonic transducer of claim 1, wherein the thickness of the matching layer is one quarter of the wavelength of the ultrasonic sound waves of the matching layer, wherein the wavelength of the ultrasonic sound waves of the matching layer is obtained by dividing the speed of sound of the matching layer by the frequency of the ultrasonic transducer.
9. The ultrasonic transducer of claim 1, wherein the annular protrusion is a hollow or solid structure; the annular protrusion comprises at least one of a square protrusion, a circular protrusion, a triangular protrusion or a star-shaped protrusion.
10. An ultrasound imaging apparatus, characterized in that the apparatus comprises: a connector, a catheter and the ultrasound transducer of any of claims 1-9; wherein,
the catheter is electrically connected with the ultrasonic transducer;
one end of the connector is electrically connected with the catheter, and the other end of the connector is electrically connected with the ultrasonic imaging system and the rotary withdrawing device respectively.
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| CN202010260301.3A CN111407313B (en) | 2020-04-03 | 2020-04-03 | Ultrasound transducer and ultrasound imaging device |
| PCT/CN2020/103678 WO2021196455A1 (en) | 2020-04-03 | 2020-07-23 | Ultrasonic transducer and ultrasonic imaging apparatus |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2021196455A1 (en) * | 2020-04-03 | 2021-10-07 | 深圳先进技术研究院 | Ultrasonic transducer and ultrasonic imaging apparatus |
| CN116266894A (en) * | 2021-12-18 | 2023-06-20 | 中国科学院深圳先进技术研究院 | Ultrasonic Focused Sound Field Modulation System and Its Modulation Method Based on Acoustic Artificial Structure |
| WO2023124886A1 (en) * | 2021-12-30 | 2023-07-06 | 深圳先进技术研究院 | Multipoint focusing sound field modulation ultrasonic transducer, preparation method, and modulation method |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN119024317B (en) * | 2024-10-28 | 2025-03-11 | 之江实验室 | Imaging sonar and matching layer encapsulation method |
Citations (22)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5488954A (en) * | 1994-09-09 | 1996-02-06 | Georgia Tech Research Corp. | Ultrasonic transducer and method for using same |
| JP2000131298A (en) * | 1998-10-23 | 2000-05-12 | Matsushita Electric Ind Co Ltd | Ultrasonic probe |
| US6162178A (en) * | 1998-07-31 | 2000-12-19 | Scimed Life Systems, Inc. | Ultrasonic transducer off-aperture connection |
| US20020188200A1 (en) * | 2001-06-08 | 2002-12-12 | Pascal Mauchamp | Multi-purpose ultrasonic slotted array transducer |
| US20080284820A1 (en) * | 2007-05-18 | 2008-11-20 | Min-Chun Pan | Highly-Efficient Ultrasonic Ink-Jet Head and Fabrication Method of for the same |
| CN101677811A (en) * | 2007-03-26 | 2010-03-24 | 麦迪斯技术公司 | Interchangeable high intensity focused ultrasound transducer |
| CN101828960A (en) * | 2010-05-07 | 2010-09-15 | 上海交通大学 | High-intensity focused ultrasound spherical phased array with array elements annually and intensively distributed |
| CN102706436A (en) * | 2012-05-16 | 2012-10-03 | 北京工业大学 | Point focusing ultrasonic transducer used for detecting wave speed of surface wave |
| CN104905815A (en) * | 2015-05-22 | 2015-09-16 | 深圳先进技术研究院 | Linear array ultrasonic probe |
| CN105021271A (en) * | 2015-07-08 | 2015-11-04 | 华中科技大学 | Optical fiber EFPI infrasonic wave sensor and infrasonic sound signal detection system |
| CN105080822A (en) * | 2015-09-07 | 2015-11-25 | 上海爱声生物医疗科技有限公司 | Novel ultrasonic transducer |
| CN105105790A (en) * | 2015-09-02 | 2015-12-02 | 上海爱声生物医疗科技有限公司 | Uterus-passing oviduct ultrasonic detection method, uterus-passing oviduct ultrasonicdiagnosis device and transducer |
| CN105105791A (en) * | 2015-09-02 | 2015-12-02 | 上海爱声生物医疗科技有限公司 | Intravascular ultrasonic focusing method, focusing diagnostic device and focusing energy transducer |
| CN105232090A (en) * | 2015-10-28 | 2016-01-13 | 上海爱声生物医疗科技有限公司 | High frequency ultrasonic energy transducer with optimized performance and manufacturing method thereof |
| CN105251140A (en) * | 2015-11-23 | 2016-01-20 | 南京大学 | Design method of focused acoustic lens |
| CN205006919U (en) * | 2015-09-02 | 2016-02-03 | 上海爱声生物医疗科技有限公司 | Through urethral prostate diasonograph and transducer |
| CN107644636A (en) * | 2017-09-01 | 2018-01-30 | 深圳先进技术研究院 | A kind of focus ultrasonic lens based on plane artificial structure |
| CN107736900A (en) * | 2017-11-09 | 2018-02-27 | 深圳先进技术研究院 | A kind of dual transducers intravascular ultrasound imaging device |
| CN108286952A (en) * | 2017-12-13 | 2018-07-17 | 大连理工大学 | A Simultaneous Ultrasonic Inversion Method of Coating Layer Thickness, Density and P-wave Sound Velocity |
| CN108426545A (en) * | 2018-03-22 | 2018-08-21 | 天津大学 | A method of using ultrasonic surface wave non-destructive testing film thickness |
| CN109141493A (en) * | 2018-09-25 | 2019-01-04 | 中国科学院电工研究所 | The ultrasonic probe and its ultrasonic image-forming system of optical drive |
| CN109431543A (en) * | 2018-12-20 | 2019-03-08 | 深圳先进技术研究院 | Sound wave condenser lens, supersonic imaging device and method |
Family Cites Families (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2001149371A (en) * | 1999-11-25 | 2001-06-05 | Aloka Co Ltd | Ultrasonic probe |
| US10693053B2 (en) * | 2014-01-29 | 2020-06-23 | Sogang University Research Foundation | Method for producing intravascular ultrasonic transducers and structure thereof |
| CN107550519A (en) * | 2017-08-22 | 2018-01-09 | 深圳先进技术研究院 | A kind of Multifunctional blood intraductal ultrasonography imaging device |
| CN111407313B (en) * | 2020-04-03 | 2022-05-10 | 深圳先进技术研究院 | Ultrasound transducer and ultrasound imaging device |
-
2020
- 2020-04-03 CN CN202010260301.3A patent/CN111407313B/en active Active
- 2020-07-23 WO PCT/CN2020/103678 patent/WO2021196455A1/en not_active Ceased
Patent Citations (22)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US5488954A (en) * | 1994-09-09 | 1996-02-06 | Georgia Tech Research Corp. | Ultrasonic transducer and method for using same |
| US6162178A (en) * | 1998-07-31 | 2000-12-19 | Scimed Life Systems, Inc. | Ultrasonic transducer off-aperture connection |
| JP2000131298A (en) * | 1998-10-23 | 2000-05-12 | Matsushita Electric Ind Co Ltd | Ultrasonic probe |
| US20020188200A1 (en) * | 2001-06-08 | 2002-12-12 | Pascal Mauchamp | Multi-purpose ultrasonic slotted array transducer |
| CN101677811A (en) * | 2007-03-26 | 2010-03-24 | 麦迪斯技术公司 | Interchangeable high intensity focused ultrasound transducer |
| US20080284820A1 (en) * | 2007-05-18 | 2008-11-20 | Min-Chun Pan | Highly-Efficient Ultrasonic Ink-Jet Head and Fabrication Method of for the same |
| CN101828960A (en) * | 2010-05-07 | 2010-09-15 | 上海交通大学 | High-intensity focused ultrasound spherical phased array with array elements annually and intensively distributed |
| CN102706436A (en) * | 2012-05-16 | 2012-10-03 | 北京工业大学 | Point focusing ultrasonic transducer used for detecting wave speed of surface wave |
| CN104905815A (en) * | 2015-05-22 | 2015-09-16 | 深圳先进技术研究院 | Linear array ultrasonic probe |
| CN105021271A (en) * | 2015-07-08 | 2015-11-04 | 华中科技大学 | Optical fiber EFPI infrasonic wave sensor and infrasonic sound signal detection system |
| CN205006919U (en) * | 2015-09-02 | 2016-02-03 | 上海爱声生物医疗科技有限公司 | Through urethral prostate diasonograph and transducer |
| CN105105790A (en) * | 2015-09-02 | 2015-12-02 | 上海爱声生物医疗科技有限公司 | Uterus-passing oviduct ultrasonic detection method, uterus-passing oviduct ultrasonicdiagnosis device and transducer |
| CN105105791A (en) * | 2015-09-02 | 2015-12-02 | 上海爱声生物医疗科技有限公司 | Intravascular ultrasonic focusing method, focusing diagnostic device and focusing energy transducer |
| CN105080822A (en) * | 2015-09-07 | 2015-11-25 | 上海爱声生物医疗科技有限公司 | Novel ultrasonic transducer |
| CN105232090A (en) * | 2015-10-28 | 2016-01-13 | 上海爱声生物医疗科技有限公司 | High frequency ultrasonic energy transducer with optimized performance and manufacturing method thereof |
| CN105251140A (en) * | 2015-11-23 | 2016-01-20 | 南京大学 | Design method of focused acoustic lens |
| CN107644636A (en) * | 2017-09-01 | 2018-01-30 | 深圳先进技术研究院 | A kind of focus ultrasonic lens based on plane artificial structure |
| CN107736900A (en) * | 2017-11-09 | 2018-02-27 | 深圳先进技术研究院 | A kind of dual transducers intravascular ultrasound imaging device |
| CN108286952A (en) * | 2017-12-13 | 2018-07-17 | 大连理工大学 | A Simultaneous Ultrasonic Inversion Method of Coating Layer Thickness, Density and P-wave Sound Velocity |
| CN108426545A (en) * | 2018-03-22 | 2018-08-21 | 天津大学 | A method of using ultrasonic surface wave non-destructive testing film thickness |
| CN109141493A (en) * | 2018-09-25 | 2019-01-04 | 中国科学院电工研究所 | The ultrasonic probe and its ultrasonic image-forming system of optical drive |
| CN109431543A (en) * | 2018-12-20 | 2019-03-08 | 深圳先进技术研究院 | Sound wave condenser lens, supersonic imaging device and method |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2021196455A1 (en) * | 2020-04-03 | 2021-10-07 | 深圳先进技术研究院 | Ultrasonic transducer and ultrasonic imaging apparatus |
| CN116266894A (en) * | 2021-12-18 | 2023-06-20 | 中国科学院深圳先进技术研究院 | Ultrasonic Focused Sound Field Modulation System and Its Modulation Method Based on Acoustic Artificial Structure |
| WO2023108878A1 (en) * | 2021-12-18 | 2023-06-22 | 中国科学院深圳先进技术研究院 | Ultrasound focusing field modulation system based on artificial acoustic structure, and modulation method thereof |
| WO2023124886A1 (en) * | 2021-12-30 | 2023-07-06 | 深圳先进技术研究院 | Multipoint focusing sound field modulation ultrasonic transducer, preparation method, and modulation method |
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| Publication number | Publication date |
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| CN111407313B (en) | 2022-05-10 |
| WO2021196455A1 (en) | 2021-10-07 |
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