KR20170005526A - An ultrasound transducer assembly for beam-forming and manufacturing method thereof - Google Patents
An ultrasound transducer assembly for beam-forming and manufacturing method thereof Download PDFInfo
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- KR20170005526A KR20170005526A KR1020150089202A KR20150089202A KR20170005526A KR 20170005526 A KR20170005526 A KR 20170005526A KR 1020150089202 A KR1020150089202 A KR 1020150089202A KR 20150089202 A KR20150089202 A KR 20150089202A KR 20170005526 A KR20170005526 A KR 20170005526A
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- 238000002604 ultrasonography Methods 0.000 title claims description 30
- 238000004519 manufacturing process Methods 0.000 title description 22
- 238000000034 method Methods 0.000 claims description 45
- 230000005540 biological transmission Effects 0.000 claims description 31
- 230000001225 therapeutic effect Effects 0.000 claims description 9
- 238000003384 imaging method Methods 0.000 claims description 7
- 230000000149 penetrating effect Effects 0.000 claims 1
- 238000006243 chemical reaction Methods 0.000 description 5
- 239000000463 material Substances 0.000 description 5
- 239000000523 sample Substances 0.000 description 5
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 5
- 230000000694 effects Effects 0.000 description 3
- 230000003902 lesion Effects 0.000 description 3
- 238000012285 ultrasound imaging Methods 0.000 description 3
- 238000010586 diagram Methods 0.000 description 2
- 238000003825 pressing Methods 0.000 description 2
- 230000001902 propagating effect Effects 0.000 description 2
- 239000002537 cosmetic Substances 0.000 description 1
- 230000006866 deterioration Effects 0.000 description 1
- 239000012466 permeate Substances 0.000 description 1
- 230000000704 physical effect Effects 0.000 description 1
- 230000000644 propagated effect Effects 0.000 description 1
- 238000004904 shortening Methods 0.000 description 1
- 231100000444 skin lesion Toxicity 0.000 description 1
- 206010040882 skin lesion Diseases 0.000 description 1
- 238000009210 therapy by ultrasound Methods 0.000 description 1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N7/02—Localised ultrasound hyperthermia
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- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R17/00—Piezoelectric transducers; Electrostrictive transducers
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Abstract
The ultrasonic transducer assembly for beam focusing comprises a concave piezoelectric element and a concave surface attached to the concave surface of the piezoelectric element so as to focus the ultrasonic wave to the first focus point, And an acoustic lens for converging the light to a second focus point closer to the element.
Description
BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic transducer for generating and radiating ultrasonic waves,
Single-element ultrasound transducers or array elements The ultrasound beam focusing of ultrasound transducers typically uses acoustical lenses. The acoustic lens shape can be designed to be concave or convex so as to focus the ultrasonic energy at a desired focusing point by using difference in ultrasonic velocity between the acoustic lens and the living tissue.
Alternatively, a technique of concave the surface of the transducer using pressed-focusing technique and concentrating the energy of the ultrasonic wave at the origin of the concave surface may be used. Further, the smaller the value of 'F-number (Focal length / Convergent aperture)' defined as the ratio of the focal point to the aperture of the ultrasonic transducer, the more the ultrasound energy is concentrated in the narrow region. For this reason, A transducer for ultrasound imaging or a transducer for high frequency ultrasonic cell manipulation should be designed and fabricated such that the F-number is close to '1'.
Thus, the therapeutic ultrasound transducer can focus the larger ultrasound energy, thereby increasing the therapeutic effect and shortening the treatment time. In the case of high-frequency ultrasound imaging, it is possible to provide a high spatial resolution. Energy can be used to trap cells and transfer them to a desired location. For this application, compression-focusing technology is mainly used. Prior art documents presented below introduce focusing methods using compression-focusing techniques.
SUMMARY OF THE INVENTION It is an object of the present invention to provide an ultrasound transducer which is capable of reducing the ratio of the focusing distance of a conventional ultrasound transducer to the diameter of a transducer, To overcome the physical limitations that exist in increasing the diameter of the transducer. Furthermore, an attempt is made to solve the problem of unnecessary hardware configuration being added to the required translator spacing when increasing the translator's aperture.
According to an aspect of the present invention, there is provided an ultrasonic transducer assembly comprising: a piezoelectric element formed concavely so as to focus ultrasonic waves to a first focal point; And an acoustical lens attached to the concave surface of the piezoelectric element and focusing an ultrasonic wave radiated from the piezoelectric element to a second focusing point relatively closer to the piezoelectric element than the first focusing point.
In the ultrasonic transducer assembly according to an embodiment, it is preferable that the acousto-optic lens has the same conversion aperture as the piezoelectric element, and the converging distance is shorter than that of the piezoelectric element.
In the ultrasonic transducer assembly according to the embodiment, it is preferable that the ratio of the converging distance to the conversion aperture is relatively smaller when the piezoelectric element and the acoustic lens are combined as compared with the case of the piezoelectric element alone Do.
In the ultrasonic transducer assembly according to an embodiment, the converging distance of the ultrasonic transducer assembly and the ratio of the transducer aperture are relatively smaller than the converging distance of the ultrasonic transducer composed of piezoelectric elements without the acoustic lens and the ratio of the transducer aperture Value.
In the ultrasonic transducer assembly according to an embodiment, the second focusing point may include a time required from a center of the piezoelectric element through a center of the acoustic lens to pass straight through the acoustic medium, and a time from a distal end of the piezoelectric element The time required for passing the acoustic medium through the acoustic lens at the refracted angle becomes the same.
In an ultrasonic transducer assembly according to an embodiment, when the ultrasonic transmission speed for the acoustic lens is faster than the ultrasonic transmission speed for the acoustic medium, the facing surface of the acoustic lens facing the acoustic medium may be concave have. It is also preferable that the radius of the sphere formed by the concave facing surface of the acoustic lens has a value smaller than the radius of the sphere formed by the concave surface of the piezoelectric element.
In the ultrasonic transducer assembly according to an embodiment, when the ultrasonic transmission speed to the acoustic lens is slower than the ultrasonic transmission speed to the acoustic medium, the facing surface of the acoustic lens facing the acoustic medium is convex or flat . It is preferable that the radius of the sphere formed by the convex opposing face of the acoustic lens has a smaller value than the radius of the sphere formed by the concave surface of the piezoelectric element.
In an ultrasound transducer assembly according to an embodiment, a hole may be formed through the piezoelectric element and the acoustic lens, and the imaging element or the therapeutic element may be received through the formed hole.
An ultrasonic transducer assembly according to an exemplary embodiment of the present invention includes: a first acoustic matching layer positioned between the piezoelectric element and the acoustic lens to reduce energy reflection; Or a second acoustic matching layer in which the acoustic lens is located on an opposite surface of the acoustic lens facing the acoustic medium to reduce energy reflection; As shown in FIG.
According to another aspect of the present invention, there is provided a method of manufacturing an ultrasonic transducer assembly, comprising: pressing a piezoelectric element using a circular sphere so as to focus ultrasonic waves to a first focal point, ; Forming an acoustic lens so that an ultrasonic wave radiated from the piezoelectric element can be focused at a second focus point closer to the piezoelectric element than the first focus point; And attaching the acoustic lens to the concave surface of the piezoelectric element.
In the method of manufacturing an ultrasonic transducer assembly according to another embodiment, the step of forming the acoustic lens may include the steps of: determining the shape of the acoustic lens by comparing an ultrasonic transmission speed with respect to the acoustic lens and an ultrasonic transmission speed with respect to the acoustic medium step; And determining the curvature of the acoustic lens so that the focusing distance is shorter than the piezoelectric element in consideration of the speed and the refractive index of the ultrasonic waves passing through the acoustic lens and the acoustic medium depending on the shape of the determined acoustic lens.
In the method of manufacturing an ultrasonic transducer assembly according to another embodiment, when the ultrasonic transmission speed for the acoustic lens is faster than the ultrasonic transmission speed for the acoustic medium, the step of forming the acoustic lens may include: The facing surface facing the medium can be concave.
In the method of manufacturing an ultrasonic transducer assembly according to another embodiment, when the ultrasonic transmission speed for the acoustic lens is slower than the ultrasonic transmission speed for the acoustic medium, the step of forming the acoustic lens may include: The opposing surface facing the medium can be formed to be convex or flat.
In the method of manufacturing an ultrasonic transducer assembly according to another embodiment, the step of forming the acoustical lens may include a step of arranging the ultrasonic transducer assembly so that the ratio of the converging distance of the ultrasonic transducer assembly to the transducer aperture is smaller than the converging point of the ultrasound transducer The position of the second focusing point may be determined to have a value that is relatively smaller than the ratio of the distance to the conversion aperture.
In the method of manufacturing an ultrasonic transducer assembly according to another embodiment, the step of forming the acoustical lens may include a time required for passing through the center of the acoustic lens through the center of the piezoelectric element and passing straight through the acoustical medium, The position of the second focusing point is determined so that the time required from the end of the piezoelectric element to pass the acoustic medium through the acoustic lens at the refracted angle becomes equal.
According to another aspect of the present invention, there is provided a method of manufacturing an ultrasonic transducer assembly, the method including forming a hole through the piezoelectric element and the acoustic lens to accommodate an imaging element or a therapeutic element.
The method of manufacturing an ultrasonic transducer assembly according to another embodiment further includes forming a first acoustic matching layer on the concave surface of the piezoelectric element to reduce energy reflection, May be performed on the formed first acoustic matching layer.
In the method of manufacturing an ultrasonic transducer assembly according to another embodiment, the acoustic lens may form a second acoustic matching layer that reduces energy reflection on the opposite surface of the acoustic lens facing the acoustic medium .
Embodiments of the present invention propose an ultrasonic transducer assembly including an acoustic lens designed to reduce the focusing distance in consideration of the velocity of a medium to which ultrasonic energy is to be transmitted and the speed of an acoustic lens, It is possible to reduce the size of the ultrasonic probe and to reduce the ultrasonic focusing distance effectively as well as to make the diameter of the transducer large and to allow the ultrasonic probe to converge at a shorter distance Dynamic design is possible.
1 illustrates an ultrasound transducer assembly for beam focusing distance reduction in accordance with an embodiment of the present invention.
2 is a view for explaining the difference in beam focusing distance according to the structure of the ultrasonic transducer.
3A to 3C are views illustrating a method of designing an acoustic lens in an ultrasonic transducer assembly according to an embodiment of the present invention.
Figs. 4A to 4C are views illustrating the shapes of acoustic lenses derived according to the designs of Figs. 3A to 3C, respectively.
FIGS. 5A to 5C are views for explaining another embodiment for utilizing the acoustic lenses of FIGS. 4A to 4C in an application field, respectively.
6 is an exemplary view for explaining an acoustic matching method for improving the energy focusing efficiency of the ultrasonic transducer assembly according to an embodiment of the present invention.
7 is a flowchart illustrating a method of manufacturing an ultrasound transducer assembly for reducing a beam focusing distance according to another embodiment of the present invention.
FIG. 8 is a flowchart illustrating a process of forming an acoustic lens in the method of manufacturing the ultrasonic transducer assembly of FIG. 7; FIG.
Before describing the embodiments of the present invention, it is to be understood that, after briefly introducing the problems that may occur depending on the characteristics of the ultrasonic transducer and the manufacturing technology of the ultrasonic transducer for treatment, technical solutions adopted by the embodiments of the present invention .
In the case of the F-number '1', which is generally the smallest, it is difficult to make the diameter of the ultrasonic transducer and the focal length of the converging point So that the above-described technique can not be used for a human body. The reason for this is that the ultrasound transducer must be brought into contact with the skin in order to use the above-described technology for the human body, in which case the focusing point can not be the surface of the skin.
In the case of an ultrasonic treatment apparatus for treating skin lesions and cosmetics, a method of separating the space between the transducer and the skin using water or another medium is used to focus the beam at a low depth from the surface due to the above-mentioned problems. In the case of separating the surface of the medium to be transduced with the transducer, it is difficult to permeate the air due to the characteristics of medical ultrasonic waves, so it is necessary to fill the space separated by water or another acoustic medium. However, this method inconveniences the necessity of a separate housing for fixing the water or other acoustic medium in front of the ultrasonic transducer, as well as increasingly larger spacing as the size of the transducer becomes larger. This limitation is pointed out as one of the factors that increase the manufacturing cost of the ultrasonic transducer at the same time as inconvenience in use. On the other hand, when the diameter of the transducer is designed to be small, the energy radiated from the acoustic device becomes small, and energy transferred to the medium becomes small.
Therefore, in order to solve the above-described problems, embodiments of the present invention, which will be described below, first reduce the focusing distance of a piezoelectric element using a compression-focusing method, By designing and focusing the beam again, we propose a technique that can effectively reduce the focusing distance.
More specifically, embodiments of the present invention first design a piezoelectric element to have a specific F-number by using a pressed-focusing technique, and determine the physical properties of the material used for the lens and the medium in which the ultrasonic waves propagate To determine the shape of the acoustic lens satisfying Snell's Law. And then calculates an optimum combination of the curvature radius and the thickness of the lens to be converged at a desired point. Finally, the lens is cast in the converter to have the parameters thus determined, or the manufactured lens is bonded.
The ultrasonic transducer manufactured by this method can effectively reduce the F-number to less than '1', and can be focused at a short distance with a large-diameter transducer, so that it can be effectively used for low depth lesions such as skin treatment And it is possible to acquire information of a shallow depth like a skin layer easily. Also, it can be effectively used for applications such as high resolution ultrasound imaging using ultrasound, high resolution photoacoustic imaging, and cell manipulation including cell images.
In addition, embodiments of the present invention include a technique for enabling selective design according to the properties of a lens material or an acoustic medium by suggesting various lens shapes, and a method for increasing beam focusing energy efficiency through acoustic matching.
Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.
FIG. 1 illustrates an
As shown in FIG. 1, by using a new type of
In summary, the
FIG. 2 is a view for explaining the difference in beam focusing distance according to the structure of the ultrasonic transducer. FIG. 2 is a cross-sectional view of the ultrasonic transducer using only the conventional single element piezoelectric transducer (A) and the ultrasonic transducer proposed by the embodiments of the present invention (B) in the case of the structure.
As described above, in general, in the case of a single ultrasound transducer that is compressed-focused (A), the F-number is difficult to have a value less than '1'. Therefore, a method of separating the surface of the medium propagated with the transducer is used to focus the beam at the desired point. However, this method is disadvantageous in that it requires a
FIGS. 3A through 3C illustrate a method of designing an acoustic lens in an ultrasonic transducer assembly according to an embodiment of the present invention. The shape of the acoustic lens is designed to satisfy Snell's Law.
3A and 3B) and the time taken for the ultrasound to reach the focusing point at the interface between the acoustic lens and the acoustic lens (Figs. 3A and 3B) (The path (2) shown in FIG. 3A and FIG. 3B) has a position that maximally coincides with the sum of the times when the ultrasound passes from the central portion of the piezoelectric element to the focusing point The curvature is selected.
3A shows a case where the speed of the acoustic lens is faster than the medium in which the acoustic lens propagates
FIGS. 3B and 3C show the case where the speed of the acoustic lens is slower than the medium in which the acoustic lens propagates
In FIGS. 3A and 3B, the transmission time of the ultrasonic waves can be summarized as the following
here,
In summary, the second focusing point formed by the attachment of the acoustic lens is the time required to pass straight through the acoustic medium through the center of the acoustic lens from the center of the piezoelectric element, and from the end of the piezoelectric element through the acoustic lens It can be determined that the time required for passing the acoustic medium through the deflected angle becomes the same.
Figs. 4A to 4C are diagrams illustrating the shape of the
At the interface where the medium traveling through the ultrasonic wave changes, the ultrasonic beam is refracted according to Snell's law. Therefore, when the speed of the acoustic lens material is higher than the speed of the medium to be advanced, it is possible to reduce the beam focusing distance by designing the
Figs. 5A to 5C are diagrams illustrating yet another embodiment for utilizing the acoustic lenses of Figs. 4A to 4C in an application field, respectively. Figs. 5A to 5C are views showing various sizes or various shapes And can be mixed with or accommodated by another ultrasonic transducer or other modality (for example, it can be an imaging device or a therapeutic device, etc.) through the hole formed therein have.
6 is an exemplary view for explaining an acoustic matching method for improving the energy focusing efficiency of the ultrasonic transducer assembly according to an embodiment of the present invention.
6 shows the first
By using the ultrasonic transducer assembly according to the embodiments of the present invention described above, it is possible to effectively reduce the focusing distance while removing an unnecessary housing, and since the F-number can be less than '1' It is possible to transmit a relatively large energy by using the transducer aperture larger than the focusing distance). In other words, by designing a new type of lens in consideration of the speed of the medium to which the ultrasonic energy is transmitted and the speed of the acoustic lens, unnecessary spacing can be eliminated to reduce the size of the ultrasonic probe and effectively reduce the ultrasonic focusing distance. Also, it is possible to make the diameter of the converter large, and to enable the dynamic design to enable the convergence at a short distance.
FIG. 7 is a flowchart illustrating a method of manufacturing an ultrasound transducer assembly for reducing beam focusing distance according to another embodiment of the present invention. Referring to FIGS. 1, 3A, and 3C, And therefore, only the outline thereof will be described in order to avoid duplication of explanation.
In step S710, the piezoelectric element is concavely formed by using a circular sphere so as to focus the ultrasonic wave to the first focal point.
In step S720, an acoustic lens is formed so that the ultrasonic waves radiated from the piezoelectric element can be focused at a second focusing point relatively closer to the piezoelectric element than the first focusing point. The process of forming the acoustic lens includes the time required for the acoustic lens to pass straight through the center of the acoustic lens from the center of the acoustic lens and the time required to pass the acoustic medium from the end of the piezoelectric element through the acoustic lens And determining the position of the second focal point so that the time required to pass through the refracted angle becomes equal. The distance between the converging distance of the ultrasonic transducer assembly and the transducer diameter may be smaller than the ratio of the converging distance of the ultrasonic transducer composed only of the piezoelectric element to the transducer aperture without the acoustic lens, It is desirable to determine the position.
In step S730, the acoustic lens is attached to the concave surface of the piezoelectric element.
Meanwhile, the method for manufacturing the ultrasonic transducer assembly for reducing the beam focusing distance may further include forming a first acoustic matching layer on the concave surface of the piezoelectric element to reduce energy reflection through step S715 And the step S720 of attaching the acoustic lens may be performed on the first acoustic matching layer formed in step S715. In addition, in the method of manufacturing the ultrasonic transducer assembly for reducing the beam focusing distance, the acoustic lens may include a second acoustic matching layer that reduces energy reflection on the opposite surface of the acoustic lens facing the acoustic medium, And the like.
Further, a method of manufacturing an ultrasound transducer assembly for reducing the beam focusing distance may further include forming a hole (not shown) through the piezoelectric element and the acoustic lens so as to accommodate the imaging device or the therapeutic device .
FIG. 8 is a flowchart specifically illustrating a process (S720) of forming an acoustic lens in the method of manufacturing the ultrasonic transducer assembly of FIG. 7, wherein a circular electrode is used to converge the ultrasonic wave to the first focal point, A step after step S710 of forming a concave shape by pressing the first and second molds will be described.
In step S720 of forming the acoustic lens, the shape of the acoustic lens is determined by comparing the ultrasonic transmission speed for the acoustic lens with the ultrasonic transmission speed for the acoustic medium through step S721. At this time, if the ultrasonic transmission speed for the acoustic lens is faster than the ultrasonic transmission speed for the acoustic medium, the process proceeds to step S722 where the acoustic lens forms a concave surface facing the acoustic medium. On the other hand, if the ultrasonic transmission speed for the acoustic lens is slower than the ultrasonic transmission speed for the acoustic medium, the process proceeds to step S723 where the acoustic lens forms the facing surface facing the acoustic medium to be convex or flat. In step S724, the curvature of the acoustic lens is determined such that the convergence distance of the acoustic lens is shorter than that of the piezoelectric element in consideration of the speed and the refractive index of the ultrasonic waves passing through the acoustic lens and the acoustic medium according to the shape of the acoustic lens determined previously.
In the embodiments of the present invention described above, a new type of lens is designed in consideration of the speed of the medium to be transferred with the ultrasonic energy and the speed of the acoustic lens, thereby reducing the size of the ultrasonic probe by eliminating the spacing space, . Also, it is possible to make the diameter of the converter large, and to enable the dynamic design to enable the convergence at a short distance.
Therefore, unlike a conventional ultrasonic transducer, a housing for preserving an acoustic medium is not required, so that it is possible not only to reduce the size of the entire transducer probe but also to reduce the manufacturing cost. In addition, since it is possible to make the diameter of the transducer large, it is expected that the use of the acoustic lens proposed by the embodiments of the present invention, compared with the conventional ultrasonic transducer, And thus can have an effect of increasing the signal size or SNR. Furthermore, it is expected to be effective for therapeutic transducer by focusing energy on lesions of low depth, paying attention to the fact that the amount of energy transferred can be increased. In addition, it is possible to acquire precise structural information of shallow depth lesions like skin layer, and can be effectively used for application of high-resolution ultrasound image (including cell image), high resolution photoacoustic image and cell manipulation using high frequency ultrasound. That is, since it is possible to use various types of lenses depending on the material of the acoustic lens, it is advantageous that it can be used with new ultrasound transducers or other images.
The present invention has been described above with reference to various embodiments. It will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention as defined by the appended claims. Therefore, the disclosed embodiments should be considered in an illustrative rather than a restrictive sense. The scope of the present invention is defined by the appended claims rather than by the foregoing description, and all differences within the scope of equivalents thereof should be construed as being included in the present invention.
10: Ultrasonic transducer assembly
13: piezoelectric element 15: acoustic lens
17: hole
18, 19: Acoustic matching layer
210: housing 220: water or acoustic medium
Claims (20)
And an acoustic lens attached to the concave surface of the piezoelectric element to focus ultrasound emitted from the piezoelectric element to a second focusing point relatively closer to the piezoelectric element than the first focusing point.
The acoustic lens includes:
The piezoelectric element and the converter aperture are the same,
Wherein the converging distance is shorter than that of the piezoelectric element.
The ratio of the focal length to the converter aperture,
Wherein the piezoelectric element and the acoustic lens have a relatively smaller value when the piezoelectric element is combined with the acoustic lens.
Wherein the converging distance of the ultrasonic transducer assembly and the ratio of the transducer aperture are relatively smaller than the converging distance of the ultrasonic transducer composed only of the piezoelectric element and the transducer aperture without the acoustic lens. .
Wherein the second focus point comprises:
A time required to pass through the center of the piezoelectric element from the center of the acoustic lens through the acoustic medium in a straight line and a time required to pass the acoustic medium through the acoustic lens from the end of the piezoelectric element through the acoustic lens at a refracted angle Is determined to be the same. ≪ Desc / Clms Page number 19 >
When the ultrasonic transmission speed for the acoustic lens is faster than the ultrasonic transmission speed for the acoustic medium,
Wherein the facing surface of the acoustic lens facing the acoustic medium is concave.
Wherein the radius of the sphere formed by the concave facing surface of the acoustic lens has a value that is relatively smaller than the radius of the sphere formed by the concave surface of the piezoelectric element.
When the ultrasonic transmission speed for the acoustic lens is slower than the ultrasonic transmission speed for the acoustic medium,
Wherein the facing surface of the acoustic lens facing the acoustic medium is convex or flat.
Wherein a radius of a sphere formed by the convex opposed surface of the acoustic lens has a value that is relatively smaller than a radius of a sphere formed by the concave surface of the piezoelectric element.
A hole penetrating the piezoelectric element and the acoustic lens is formed,
And the imaging element or therapeutic element is received through the hole formed therein.
A first acoustic matching layer positioned between the piezoelectric element and the acoustic lens to reduce energy reflection; or
A second acoustic matching layer positioned above the opposite surface of the acoustic lens facing the acoustic medium to reduce energy reflection; ≪ / RTI >
Forming an acoustic lens so that an ultrasonic wave radiated from the piezoelectric element can be focused at a second focus point closer to the piezoelectric element than the first focus point; And
And attaching the acoustic lens to a concave surface of the piezoelectric element.
Wherein forming the acoustic lens comprises:
Determining the shape of the acoustic lens by comparing the ultrasonic transmission speed with respect to the acoustic lens and the ultrasonic transmission speed with respect to the acoustic medium; And
And determining the curvature of the acoustic lens so that the focusing distance is shorter than the piezoelectric element in consideration of the speed and the refractive index of the ultrasonic waves passing through the acoustic lens and the acoustic medium depending on the shape of the determined acoustic lens. Gt;
Wherein when the ultrasonic transmission speed for the acoustic lens is faster than the ultrasonic transmission speed for the acoustic medium,
Wherein the acoustic lens forms a concave facing surface facing the acoustic medium. ≪ RTI ID = 0.0 > 15. < / RTI >
Wherein when the ultrasonic transmission speed for the acoustic lens is slower than the ultrasonic transmission speed for the acoustic medium,
Wherein the acoustic lens forms a convex or flat surface facing the acoustic medium. ≪ Desc / Clms Page number 19 >
Wherein forming the acoustic lens comprises:
The position of the second focus point is set such that the convergence distance of the ultrasound transducer assembly and the ratio of the transducer aperture are relatively smaller than the converging distance of the ultrasonic transducer composed only of the piezoelectric element and the converter aperture without the acoustic lens, Wherein the ultrasonic transducer assembly comprises an ultrasonic transducer.
Wherein forming the acoustic lens comprises:
A time required to pass through the center of the piezoelectric element from the center of the acoustic lens through the acoustic medium in a straight line and a time required to pass the acoustic medium through the acoustic lens from the end of the piezoelectric element through the acoustic lens at a refracted angle The position of the second focusing point is determined so that the position of the second focusing point is determined to be the same.
And forming a hole through the piezoelectric element and the acoustic lens to accommodate the imaging element or the therapeutic element.
Forming a first acoustic matching layer on the concave side of the piezoelectric element to reduce energy reflection,
Wherein attaching the acoustical lens is performed on the formed first acoustic matching layer.
Further comprising: forming a second acoustic matching layer on the opposite side of the acoustic lens where the acoustic lens faces the acoustic medium to reduce energy reflection.
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| KR1020150089202A KR20170005526A (en) | 2015-06-23 | 2015-06-23 | An ultrasound transducer assembly for beam-forming and manufacturing method thereof |
| PCT/KR2016/005084 WO2016208872A1 (en) | 2015-06-23 | 2016-05-13 | Ultrasonic transducer assembly for beam focusing and method for manufacturing same |
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| KR1020150089202A KR20170005526A (en) | 2015-06-23 | 2015-06-23 | An ultrasound transducer assembly for beam-forming and manufacturing method thereof |
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| KR20180092729A (en) * | 2017-02-10 | 2018-08-20 | 한국표준과학연구원 | An ultrasonic transducer for moxibustion therapy having temperature sensor |
| KR20200132084A (en) * | 2019-05-15 | 2020-11-25 | 서강대학교산학협력단 | Ultrasound transducer and manufacturing method thereof |
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| CN111112037A (en) * | 2020-01-20 | 2020-05-08 | 重庆医科大学 | Lens type multi-frequency focusing ultrasonic transducer, transduction system and method for determining axial length of acoustic focal region of lens type multi-frequency focusing ultrasonic transducer |
| CN114209995A (en) * | 2021-11-23 | 2022-03-22 | 天津大学 | Planar acoustic lens ultrasonic focusing sensor based on velocity gradient matching layer |
| CN114129189B (en) * | 2021-11-30 | 2023-02-03 | 深圳先进技术研究院 | Dual-frequency intravascular ultrasonic transducer, and method and device for calculating Young modulus of vascular wall |
| WO2024020348A2 (en) * | 2022-07-18 | 2024-01-25 | Acoustic Bio Inc. | Submersion transducer with adjustable focus |
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| KR20140143597A (en) | 2013-06-07 | 2014-12-17 | 동국대학교 산학협력단 | Apparatus and method to expand view angle of intravascular ultrasound transducer |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
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| KR20180092729A (en) * | 2017-02-10 | 2018-08-20 | 한국표준과학연구원 | An ultrasonic transducer for moxibustion therapy having temperature sensor |
| KR20200132084A (en) * | 2019-05-15 | 2020-11-25 | 서강대학교산학협력단 | Ultrasound transducer and manufacturing method thereof |
| WO2020231093A3 (en) * | 2019-05-15 | 2020-12-30 | 서강대학교산학협력단 | Ultrasonic transducer and method for producing ultrasonic transducer |
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