Acoustic lens design system for correcting ultrasonic wavefront distortion, acoustic lens design method using same, and meta-ultrasonic probe comprising acoustic lens manufactured using same

Abstract

In an acoustic lens design system for correcting ultrasonic wavefront distortion and an acoustic lens design method using same, the acoustic lens design system comprises transmitting / receiving units on one side and the other side, a signal information acquisition unit, a signal mapping unit, a phase difference derivation unit, and a lens design unit. The transmitting / receiving units on one side and the other side transmit and receive ultrasonic waves for a visualization area so as to acquire an ultrasonic transmission and reception signal for a lens position in which a lens to be designed is positioned. The signal information acquisition unit acquires signal information for each coordinate of the lens position from the acquired ultrasonic transmission and reception signal. The signal mapping unit maps the acquired signal information for each coordinate of the lens position. The phase difference derivation unit calculates a mapping vector from a mapping result so as to derive a phase difference for each coordinate of the lens position. The lens design unit designs a lens so as to offset the phase difference.

Description

An acoustic lens design system for correcting ultrasonic wavefront distortion, an acoustic lens design method using the same, and a meta-ultrasonic probe including an acoustic lens fabricated by the same.

[0001] The present invention relates to an acoustic lens design system for correcting ultrasonic wavefront distortion, an acoustic lens design method using the same, and a meta-ultrasonic probe including an acoustic lens produced by the same. More specifically, the invention relates to an acoustic lens design system for correcting ultrasonic wavefront distortion that can obtain a more accurate ultrasonic signal by designing an acoustic lens that cancels out the distortion of a distortion target based on an ultrasonic signal transmitted and received through a distortion target, an acoustic lens design method using the same, and a meta-ultrasonic probe including an acoustic lens produced by the same.

[0002] As the need for early diagnosis of diseases increases, ultrasound-based imaging diagnostic and therapeutic technologies are advancing, and demand for them is rising. Furthermore, the demand for such ultrasound-based imaging is also increasing in the field of non-destructive testing.

[0003] However, in diagnostic, examination, or treatment techniques using ultrasound, image distortion is a major obstacle, because the transmission of ultrasound is restricted or the ultrasound signal is refracted or scattered due to specific structures within the object undergoing ultrasound diagnosis, causing signal distortion.

[0004] Accordingly, technology for designing lenses to minimize distortion of ultrasonic signals caused by the aforementioned specific structure is being developed. For example, Japanese Patent No. 7438511 discloses a technology for designing lenses to minimize distortion of ultrasonic signals through the simulation of ultrasonic wavefronts, and U.S. Patent No. 9636133 also discloses a technology for utilizing simulation results for the design of an ultrasonic system.

[0005] However, the technology for designing lenses to minimize ultrasound distortion based on such simulations has problems, such as the need for additional correction because the actual measured ultrasound signal differs from the simulation results, or distortion occurring even when the designed lens is applied.

[0006] Accordingly, the technical problem of the present invention is conceived from this point, and the objective of the present invention is to provide an acoustic lens design system for correcting ultrasonic wavefront distortion that can improve the accuracy of the acquired ultrasonic signal by more accurately correcting the distortion of the ultrasonic signal through the design of an acoustic lens that cancels out the distortion of the object of distortion using the results of directly measuring the ultrasonic signal transmitted and received through the object of distortion.

[0007] In addition, another objective of the present invention is to provide an acoustic lens design method using the acoustic lens design system.

[0008] In addition, another objective of the present invention is to provide a meta-ultrasonic probe comprising an acoustic lens manufactured by the acoustic lens design system.

[0009] An acoustic lens design system according to one embodiment for realizing the purpose of the present invention described above includes one-sided and other-sided transceivers, a signal information acquisition unit, a signal mapping unit, a phase difference derivation unit, and a lens design unit. The one-sided and other-sided transceivers transmit and receive ultrasound with respect to a visualization area and acquire an ultrasound transmission and reception signal for a lens position where the lens to be designed is located. The signal information acquisition unit acquires signal information for each coordinate of the lens position from the acquired ultrasound transmission and reception signal. The signal mapping unit maps the acquired signal information to each coordinate of the lens position. The phase difference derivation unit calculates a mapping vector from the mapping result to derive a phase difference for each coordinate of the lens position. The lens design unit designs the lens to cancel out the phase difference.

[0010] In one embodiment, the lens may be designed as being positioned between the one-sided and the other-sided transceivers and a distortion target that induces distortion of the ultrasonic reception signal.

[0011] In one embodiment, the lens may be designed assuming that it is positioned between a distortion target that induces distortion of the ultrasonic reception signal and the visualization area.

[0012] In one embodiment, each of the one-sided and other-sided transceivers may include a transceiver that generates and transmits an ultrasonic signal and a receiver that receives the ultrasonic signal.

[0013] In one embodiment, the one-sided transceiver includes one channel, and the other-sided transceiver may include at least one channel.

[0014] In one embodiment, the ultrasonic signal transmitted from one channel of the first transceiver is reflected at each location of the visualization area and received by each of at least one channel of the other transceiver, and the signal received at each of at least one channel of the other transceiver may be a signal reflected at different locations of the visualization area.

[0015] In one embodiment, the ultrasonic signal transmitted from each of at least one channel of the other transceiver is reflected at each location of the visualization area and received by one channel of the first transceiver, and the signal transmitted from each of at least one channel of the other transceiver may be reflected at different locations of the visualization area.

[0016] In one embodiment, the signal information acquisition unit can calculate the time between the transmission and reception of the ultrasonic signal for each coordinate and acquire magnitude and phase information of the ultrasonic signal for each coordinate.

[0017] In one embodiment, the signal information acquisition unit can acquire a first phase information when the one-sided transceiver is a transmitter and the other-sided transceiver is a receiver, and a second phase information when the other-sided transceiver is a transmitter and the one-sided transceiver is a receiver, respectively.

[0018] In one embodiment, the phase difference derivation unit defines the magnitude and phase information of the ultrasonic signal for each coordinate as a complex vector for each coordinate, and derives the phase difference for each coordinate by taking the inner product of the first complex vector for the first phase information and the second complex vector for the second phase information.

[0019] In one embodiment, the visualization area may be an area where the subject of diagnosis, examination, or treatment using ultrasound is located.

[0020] In an acoustic lens design method according to an embodiment for realizing another objective of the present invention described above, ultrasonic waves are transmitted and received over a visualization area to obtain ultrasonic transmission and reception signals for a lens position where the lens to be designed is located. From the obtained ultrasonic transmission and reception signals, signal information for each coordinate of the lens position is obtained. The obtained signal information is mapped to each coordinate of the lens position. From the mapping result, a mapping vector is calculated to derive a phase difference for each coordinate of the lens position. A lens is designed to cancel out the phase difference.

[0021] In one embodiment, the step of acquiring the ultrasonic transmission and reception signals may include the step of sequentially or independently transmitting the first to n ultrasonic signals (n is a natural number) to the one-side transceiver as a transmitter, and the step of sequentially or independently receiving the first to n ultrasonic signals reflected at a specific location in the visualization area for each of the first to n ultrasonic signals to the other-side transceiver as a receiver.

[0022] In one embodiment, the step of acquiring the ultrasonic transmission and reception signal may include the step of sequentially or independently transmitting the n+1 to m ultrasonic signals (m is a natural number) to the other side transceiver as a transmitter, and the step of sequentially or independently receiving the n+1 to m ultrasonic signals reflected at a specific location in the visualization area for each of the n+1 to m ultrasonic signals to the one side transceiver as a receiver.

[0023] In one embodiment, the step of acquiring the ultrasonic transmission and reception signal comprises: transmitting the first to n ultrasonic signals (n is a natural number) sequentially or independently to the first transceiver as a transmitter; and for each of the first to n ultrasonic signals, receiving is performed for each of the p ultrasonic signals to the other transceiver as a receiver, thereby forming an n*p transmission and reception matrix ( It may include the step of deriving q*q matrices by converting the n*q transmitting and receiving matrix into q beam forming modes (q is a natural number and may be equal to n or p) passing through the lens position.

[0024] In one embodiment, during the step of designing the lens, the thickness at each position of the lens can be derived through an operation in which an ultrasonic time delay having an opposite sign to cancel out the phase difference is divided by the difference between the reciprocal of the wave velocity of the background material and the reciprocal of the wave velocity of the lens material.

[0025] A meta-ultrasonic probe according to one embodiment for realizing another objective of the present invention described above comprises an ultrasonic unit for transmitting and receiving ultrasound, and an acoustic lens disposed adjacent to the ultrasonic unit.

[0026] In one embodiment, the ultrasonic unit includes an ultrasonic probe, and the ultrasonic probe may be at least one of the one-sided and other-sided transceivers.

[0027] In one embodiment, an active control unit for controlling the position of the acoustic lens, the distance between the acoustic lens and the ultrasonic probe, or the mounting and detachment of the acoustic lens may be further included.

[0028] In one embodiment, the ultrasonic unit may include a piezoelectric element.

[0029] According to embodiments of the present invention, since a lens is designed based on a signal that is distorted by passing through a distortion target while the distortion target is present, the signal distortion state caused by the actual distortion target can be reflected more accurately compared to a lens designed through conventional virtual simulation results, thereby enabling more accurate and effective correction of ultrasonic signal distortion using the designed lens.

[0030] That is, by using one-sided and other-sided transceivers, based on the ultrasonic signal transmitted and received through the distortion target and into the visualization area, a signal that is distorted according to the distortion target can be derived, and a lens can be designed to offset the degree of distortion of the distorted signal.

[0031] At this time, the one-sided transceiver and the other-sided transceiver both perform the role of a transceiver and a receiver, and thus can acquire signals at each location of the visualization area. Therefore, based on signals passing through the distortion target in various directions, the transmission and reception signals at each location can be acquired, and the signal distortion state caused by the distortion target can be precisely acquired.

[0032] In addition, even without information on whether the signal received from the visualization area corresponds to a specific location, the signal corresponding to a specific location can be extracted based on information regarding various coordinates of the lens position obtained through the one-sided and other-sided transceivers that perform both the roles of the transceiver and receiver, and thereby signal information for each coordinate of the lens position can be obtained.

[0033] In addition, the phase difference for each coordinate of the lens position can be derived through simple vector operations on the result mapped from the signal information obtained when the one-sided transceiver acts as a transmitter and the result mapped from the signal information obtained when the other-sided transceiver acts as a transmitter, and thereby, a lens structure that cancels out the phase difference for each coordinate of the lens position can be designed. Accordingly, since the lens can be designed based on numerical information such as a simple phase difference, the ease of designing the lens and the ease of manufacturing the designed lens are improved.

[0034] Accordingly, when performing various diagnoses or treatments, or when conducting various tests, even if a specific distortion target that distorts the ultrasonic signal exists inside, by immediately designing the lens through the transmission and reception of the ultrasonic signal, the ultrasonic signal for the structure can be acquired more accurately and precisely, thereby improving the accuracy and precision of diagnosis, treatment, and testing.

[0035] FIG. 1 is a block diagram illustrating an acoustic lens design system according to one embodiment of the present invention.

[0036] Figure 2 is a flowchart illustrating an acoustic lens design method using the acoustic lens design system of Figure 1.

[0037] FIG. 3 is a flowchart illustrating the steps for acquiring the ultrasonic transmission and reception signals of FIG. 2.

[0038] FIGS. 4a, FIGS. 4b, FIGS. 5a, and FIGS. 5b are schematic diagrams for explaining the transmission and reception steps of the ultrasonic signal of FIG. 3.

[0039] Figure 6 is a schematic diagram illustrating the step of acquiring signal information for each coordinate of the lens position of Figure 2.

[0040] FIGS. 7a and 7b are schematic diagrams illustrating the steps of transmitting and receiving ultrasonic signals in an acoustic lens design method according to another embodiment of the present invention.

[0041] Figures 8a and 8b are images showing the results of mapping the acquired signal information of Figure 2 to each coordinate.

[0042] Figures 9a and 9b are examples of lenses designed through the steps of designing the lens of Figure 2.

[0043] FIG. 10a is a schematic diagram illustrating the state of providing an ultrasonic signal when the lens of FIG. 9a is not applied, and FIG. 10b is a schematic diagram illustrating the state of providing an ultrasonic signal when the lens of FIG. 9a is applied.

[0044] Figures 11a and 11b are images showing the results of mapping the acquired signal information of Figure 2 to each coordinate when the lens of Figure 9a is applied.

[0045] FIGS. 12a to 12c are block diagrams illustrating a meta-ultrasonic probe including an acoustic lens fabricated using the acoustic lens design system of FIG. 1.

[0046] <Explanation of Symbols>

[0047] 10: Acoustic Lens Design System

[0048] 100: One-sided transceiver 101: First channel

[0049] 110: Incident wave 120, 130: Transmitted wave

[0050] 200 : Other side transceiver 201 : 2nd channel

[0051] 202: 3rd Channel 300: Signal Information Acquisition Unit

[0052] 400: Signal mapping unit 500: Phase difference derivation unit

[0053] 600 : Lens design section 601 : Lens position

[0054] 610, 611 : Lens 700 : Distortion object

[0055] 800: Visualization area

[0056] 900, 901, 902: Meta ultrasound probe

[0057] 910 : Acoustic lens 920 : Ultrasonic probe

[0058] The present invention is susceptible to various modifications and may take various forms, and embodiments are to be described in detail in the text. However, this is not intended to limit the invention to the specific disclosed forms, and it should be understood that the invention includes all modifications, equivalents, and substitutions that fall within the spirit and scope of the invention. Similar reference numerals have been used for similar components in the description of each figure. Terms such as "first," "second," etc., may be used to describe various components, but said components should not be limited by said terms.

[0059] The above terms are used solely for the purpose of distinguishing one component from another. The terms used in this application are used merely to describe specific embodiments and are not intended to limit the invention. The singular expression includes the plural expression unless the context clearly indicates otherwise. In this application, terms such as "comprising" or "consisting of" are intended to specify the existence of the features, numbers, steps, actions, components, parts, or combinations thereof described in the specification, and should be understood as not precluding the existence or addition of one or more other features, numbers, steps, actions, components, parts, or combinations thereof.

[0060] Hereinafter, preferred embodiments of the present invention will be described in more detail with reference to the attached drawings.

[0061] FIG. 1 is a block diagram illustrating an acoustic lens design system according to one embodiment of the present invention.

[0062] Referring to FIG. 1, the acoustic lens design system (10, hereinafter referred to as the design system) according to the present embodiment includes a one-sided transceiver (100), a other-sided transceiver (200), a signal information acquisition unit (300), a signal mapping unit (400), a phase difference derivation unit (500), and a lens design unit (600).

[0063] The above acoustic lens design system (10) refers to a system for designing a lens to prevent distortion of an ultrasonic signal received from a so-called visualization area (800), which is defined as an area where a target to be diagnosed, examined, or treated using ultrasound is located, as shown in FIG. 4a described later.

[0064] Generally, when an ultrasonic signal is provided to the visualization area (800) using ultrasound and the transmitted ultrasonic signal is received from the visualization area (800), if a distortion target (700) is located between the visualization area (800) and the ultrasound provider, the received ultrasonic signal is distorted by the distortion target (700). Therefore, it is difficult to obtain accurate information about the visualization area (800), and thus it may be difficult to accurately diagnose, examine, or treat a target located in the visualization area (800).

[0065] For example, when performing ultrasound on the human body, the distortion target (700) may be body tissue or skeleton such as bone, and when performing non-destructive testing, the distortion target (700) may be foreign matter such as sludge inside a pipe. Of course, the distortion target (700) is not limited to specific tissue, skeleton, or structure, and may include any structure that distorts the signal, such as by refracting or scattering the ultrasound signal.

[0066] Accordingly, the acoustic lens design system (10) is a system for designing a lens capable of canceling out signal distortion caused by the distortion target (700) based on information about the distortion target (700), that is, the degree to which the signal is distorted by the distortion target (700). Thus, by positioning the lens designed through the acoustic lens design system (10) to overlap with the distortion target (700), the ultrasonic signal can be acquired more accurately from the visualization area (800), and thereby, diagnosis, examination, or treatment using ultrasound on a target located in the visualization area (800) can be performed more accurately and precisely.

[0067] In particular, since the distortion target (700) exists in a very variable manner depending on the position or structure of the visualization area (800), when the visualization area (800) is determined, by obtaining information about the distortion target (700) according to the visualization area (800) and designing the lens, it is possible to design an optimal lens that can correct signal distortion caused by the distortion target in accordance with the characteristics such as the structure or properties of various distortion targets (700).

[0068] A more detailed description of the acoustic lens design system (10) according to this embodiment will be described later, together with an acoustic lens design method using the design system (10), for the convenience of explanation.

[0069] Figure 2 is a flowchart illustrating an acoustic lens design method using the acoustic lens design system of Figure 1.

[0070] Referring to FIGS. 1 and 2, in the acoustic lens design method (hereinafter referred to as the design method), first, the one-sided and other-sided transceivers (100, 200) transmit and receive ultrasound with respect to the visualization area (800) to obtain an ultrasound transmission and reception signal for the lens position where the lens to be designed is located (step S10).

[0071] In the present embodiment, the one-sided transceiver (100) may act as a transmitter to transmit an ultrasonic signal to the visualization area (800), and the other-sided transceiver (200) may act as a receiver to receive the ultrasonic signal received from the visualization area (800). Alternatively, the other-sided transceiver (200) may act as a transmitter to transmit an ultrasonic signal to the visualization area (800), and the one-sided transceiver (100) may act as a receiver to receive the ultrasonic signal received from the visualization area (800).

[0072] Meanwhile, the above-mentioned one-sided transceiver (100) may be composed of a single ultrasonic probe, and likewise, the above-mentioned other-sided transceiver (200) may also be composed of a single ultrasonic probe. However, if the above-mentioned one-sided transceiver (100) transmits and receives one or more transmission and reception signals as described below, the single ultrasonic probe may be equipped with one or more ultrasonic transducers or channels. Likewise, if the above-mentioned other-sided transceiver (200) transmits and receives one or more transmission and reception signals, the single ultrasonic probe may be equipped with one or more ultrasonic transducers or channels.

[0073] The step (step S10) of transmitting and receiving ultrasound for the more specific visualization area (800) and obtaining an ultrasound transmission and reception signal for the lens position where the designed lens is located is explained in more detail as follows.

[0074] FIG. 3 is a flowchart illustrating the step of acquiring the ultrasonic transmission and reception signal of FIG. 2. FIG. 4a, FIG. 4b, FIG. 5a, and FIG. 5b are schematic diagrams for explaining the step of transmitting and receiving the ultrasonic signal of FIG. 3.

[0075] Referring to FIGS. 3 and FIGS. 4a, in the step of acquiring the ultrasonic transmission and reception signal (step S10), a first ultrasonic signal is transmitted from the first channel (101) of the one-sided transmission and reception unit (100) to the visualization area (800) (step S11).

[0076] At this time, as illustrated in FIG. 4a, it is assumed that a distortion target (700) that distorts the ultrasonic signal exists between the visualization area (800) and the first channel (101). Additionally, it is assumed that the signal distorted by the distortion target (700) is corrected by a lens, and that the lens is positioned (601, lens position) between the first channel (101) and the distortion target (700).

[0077] That is, in this embodiment, the lens is designed by assuming that the lens to be finally designed is located at the lens position (601), that is, between the one-sided and other-sided transceivers (100, 200) and the distortion target (700).

[0078] Alternatively, the lens position (601) may be located between the distortion target (700) and the visualization area (800), and even when the lens position (601) is located between the distortion target (700) and the visualization area (800) in this manner, the design method described below can be applied in the same way. Accordingly, below, only the case where the lens position (601) is located between the one-sided and other-sided transceivers (100, 200) and the distortion target (700) will be described.

[0079] Additionally, the first channel (101) is a channel that transmits or receives an ultrasonic signal from the one-sided transmitting and receiving unit (100), and the one-sided transmitting and receiving unit (100) may be, for example, a transducer.

[0080] When the first ultrasonic signal is transmitted from the first channel (101), it is provided by focusing on the first transmission position (x1) among the lens positions (601), and the first ultrasonic signal focused on the first transmission position (x1) passes through the lens position (601) and is provided to the visualization area (800).

[0081] In this process, the first ultrasonic signal is provided to the visualization area (800) by passing through the distortion target (700), so that the first ultrasonic signal is provided to the visualization area (800) in a distorted state.

[0082] As described above, when a first ultrasonic signal is generated in the first channel (101), focused at the first transmission position (x1), and provided to the visualization area (800) (step S11), the first ultrasonic signal reflected from the visualization area (800) is received through the other side transceiver (200).

[0083] That is, referring to FIGS. 3 and FIGS. 4a, at least one other transceiver (200) receives a first ultrasonic signal reflected at a specific location (step S12).

[0084] At this time, in FIG. 4a, assuming that there are two other transceivers (200), they are exemplified by being divided into a second channel (201) and a third channel (202). Alternatively, the other transceivers (200) may be one or three or more.

[0085] Additionally, the ultrasonic signal provided to the visualization area (800) by the first channel (101) is reflected at specific locations (P1, P2) of the visualization area (800) and received by the second and third channels (201, 202). In this case, although two specific locations are exemplified in the drawings for convenience of explanation, they are not limited thereto and may be one location or three or more locations.

[0086] As described above, the ultrasonic signals reflected from the first and second positions (P1, P2) as specific positions are distorted as they pass through the distortion target (700), and the 11th receiving position (y) of the lens position (601) 11 Received via the second channel (201) through ), and the 12th receiving position (y) of the lens position (601). 12 It is received through the third channel (202) above.

[0087] As described above, through the transmission and reception of the first ultrasonic signal, transmission and reception coordinate information (x1, y) for the first position (P1) of the visualization area (800)11 ), and transmission / reception coordinate information (x1, y) for the second position (P2) 12 ) is obtained.

[0088] Meanwhile, when receiving the first ultrasonic signal as described above, it is obvious that reception in each channel can be performed sequentially or individually (independently). This applies equally to the transmission and reception of ultrasonic signals below.

[0089] Afterwards, referring to FIGS. 3 and FIGS. 4b, in the step of acquiring the ultrasonic transmission and reception signal (step S10), a second ultrasonic signal is transmitted from the first channel (101) of the one-sided transmission and reception unit (100) to the visualization area (800) (step S13).

[0090] That is, a second ultrasonic signal different from the first ultrasonic signal is transmitted. When the second ultrasonic signal is transmitted from the first channel (101), it is provided by focusing on the second transmission position (x2) among the lens positions (601), and the second ultrasonic signal focused on the second transmission position (x2) passes through the lens position (601) and is provided to the visualization area (800).

[0091] In this process, the second ultrasonic signal is provided to the visualization area (800) by passing through the distortion target (700), so that the second ultrasonic signal is provided to the visualization area (800) in a distorted state.

[0092] As described above, when a second ultrasonic signal is generated in the first channel (101) and focused to the second transmission position (x2) and provided to the visualization area (800) (step S13), the second ultrasonic signal reflected from the visualization area (800) is received through the other side transceiver (200).

[0093] That is, referring to FIGS. 3 and FIGS. 4b, at least one other transceiver (200) receives a second ultrasonic signal reflected at a specific location (step S14).

[0094] The second ultrasonic signal reflected from the first and second positions (P1, P2) is distorted as it passes through the distortion target (700), and the 21st receiving position (y) of the lens position (601) 21 Received via the second channel (201) through ), and the 22nd receiving position (y) of the lens position (601). 22 It is received through the third channel (202) above.

[0095] As described above, through the transmission and reception of the second ultrasonic signal, transmission and reception coordinate information (x2, y) for the first position (P1) of the visualization area (800) 21 ), and transmission / reception coordinate information (x2, y) for the second position (P2) 22 ) is obtained.

[0096] Furthermore, the one-sided transceiver (100) transmits up to the nth ultrasonic signal (n is a natural number), and the other-sided transceiver (200) receives up to the nth ultrasonic signal. Thus, the step of the one-sided transceiver (100) transmitting the ultrasonic signal as a transmitter and the other-sided transceiver (200) receiving the ultrasonic signal as a receiver is completed.

[0097] In addition, while performing transmission and reception for the nth ultrasonic signal as described above, n transmission and reception coordinates for the first position (P1) are obtained, and n transmission and reception coordinates for the second position (P2) are also obtained.

[0098] Afterwards, referring to FIG. 3 and FIG. 5a, in the step of acquiring the ultrasonic transmission and reception signal (step S10), the n+1 ultrasonic signal is transmitted to the visualization area (800) from the second channel (201) and the third channel (302) of the other side transmission and reception unit (100) (step S15).

[0099] At this time, when the n+1 ultrasonic signal is transmitted from the second channel (201), among the lens positions (601), the n+11 transmission position (y 11 It is provided by focusing on ), and the above n+11th transmission position (y 11 The n+1 ultrasonic signal focused on ) passes through the lens position (601) and is provided to the visualization area (800).

[0100] Additionally, when transmitting the n+1 ultrasonic signal in the third channel (202), among the lens positions (601), the n+12 transmission position (y 12 It is provided by focusing on ), and the above n+12th transmission position (y 12 The n+1 ultrasonic signal focused on ) passes through the lens position (601) and is provided to the visualization area (800).

[0101] As described above, the n+1 ultrasonic signals are generated respectively in the second and third channels (201, 202) to the n+11 and n+12 transmission positions (y 11 , y 12 When each is focused and provided to the visualization area (800) (step S15), the n+1 ultrasonic signals reflected from the visualization area (800) are received through the one-sided transceiver (100).

[0102] That is, referring to FIG. 3 and FIG. 5a, the one-sided transceiver (100) receives the n+1th ultrasonic signal reflected at a specific location (step S16).

[0103] At this time, assuming that the n+1 ultrasonic signal provided by the second channel (201) is reflected from the first position (P1) and received by the first channel (201), the n+11 transmission position (y) 11 The ultrasonic signal provided through ) is at the n+11th receiving position (x 11 It is received through the first channel (201) above.

[0104] Additionally, assuming that the n+1 ultrasonic signal provided by the third channel (202) is reflected at the second position (P2) and received by the first channel (201), the n+12 transmission position (y) 12 The ultrasonic signal provided through ) is at the n+12th receiving position (x 12 It is received through the first channel (201) above.

[0105] At this time, the n+1 ultrasonic signal received in the first channel (101) likewise passes through the distortion target (700) and corresponds to the distorted signal.

[0106] As described above, through the transmission and reception of the n+1 ultrasonic signal, the transmission and reception coordinate information (y) for the first position (P1) of the visualization area (800) 11 , x 11 ), and transmission / reception coordinate information (y) for the second position (P2) 12 , x 12 ) is obtained.

[0107] Afterwards, referring to FIG. 3 and FIG. 5b, in the step of acquiring the ultrasonic transmission and reception signal (step S10), the n+2 ultrasonic signal is transmitted to the visualization area (800) from the second channel (201) and the third channel (302) of the other side transmission and reception unit (100) (step S17).

[0108] At this time, when the n+2 ultrasonic signal is transmitted from the second channel (201), among the lens positions (601), the n+21 transmission position (y 21 It is provided by focusing on ), and the above n+21 transmission position (y 21 The n+2 ultrasonic signal focused on ) passes through the lens position (601) and is provided to the visualization area (800).

[0109] Additionally, when transmitting the n+2 ultrasonic signal in the third channel (202), among the lens positions (601), the n+22 transmission position (y 22It is provided by focusing on ), and the above n+22nd transmission position (y 22 The n+2 ultrasonic signal focused on ) passes through the lens position (601) and is provided to the visualization area (800).

[0110] As described above, the n+2 ultrasonic signals are generated respectively in the second and third channels (201, 202) to the n+21 and n+22 transmission positions (y 21 , y 22 When each is focused and provided to the visualization area (800) (step S17), the n+2 ultrasonic signals reflected from the visualization area (800) are received through the one-sided transceiver (100).

[0111] That is, referring to FIG. 3 and FIG. 5b, the one-sided transceiver (100) receives the n+2th ultrasonic signal reflected at a specific location (step S18).

[0112] At this time, assuming that the n+2 ultrasonic signal provided by the second channel (201) is reflected from the first position (P1) and received by the first channel (201), the n+21 transmission position (y) 21 The ultrasonic signal provided through ) is at the n+21st receiving position (x 21 It is received through the first channel (201) above.

[0113] Additionally, assuming that the n+2 ultrasonic signal provided by the third channel (202) is reflected at the second position (P2) and received by the first channel (201), the n+22 transmission position (y) 22 The ultrasonic signal provided through ) is at the n+22nd receiving position (x 22 It is received through the first channel (201) above.

[0114] At this time, the n+2 ultrasonic signal received in the first channel (101) likewise passes through the distortion target (700) and corresponds to the distorted signal.

[0115] As described above, through the transmission and reception of the n+2 ultrasonic signal, the transmission and reception coordinate information (y) for the first position (P1) of the visualization area (800) 21 , x 21 ), and transmission / reception coordinate information (y) for the second position (P2) 22 , x 22 ) is obtained.

[0116] Afterwards, for each of the ultrasonic signals from the n+3rd ultrasonic signal to the mth ultrasonic signal (m is a natural number greater than n), transmission and reception are performed with the other side transceiver (200) as the transmitter and the one side transceiver (100) as the receiver.

[0117] Thus, when the transmission and reception as described above are performed, m transmission and reception coordinates transmitted and received for the first position (P1), i.e., m transmission and reception coordinates of the lens position (601), are obtained, and m transmission and reception coordinates transmitted and received for the second position (P2), i.e., m transmission and reception coordinates of the lens position (601), are also obtained. At this time, if m=2n, then the number of transmission and reception coordinates of the lens position (601) obtained with one side transmission and reception unit (100) as the transmitting unit and the number of transmission and reception coordinates of the lens position (601) obtained with the other side transmission and reception unit (200) as the transmitting unit may be the same.

[0118] Furthermore, as described above, coordinate information of the lens position (601) is obtained while performing transmission and reception in one direction (i.e., one side transmitting / receiving unit as the transmitting unit and the other side transmitting / receiving unit as the receiving unit) with respect to the first position (P1), and coordinate information of the lens position (601) is obtained while performing transmission and reception in the other direction (i.e., the other side transmitting / receiving unit as the transmitting unit and the one side transmitting / receiving unit as the receiving unit).

[0119] In addition, for the second position (P2), coordinate information of the lens position (601) is obtained while performing transmission and reception in one direction, and coordinate information of the lens position (601) is obtained while performing transmission and reception in the other direction.

[0120] Meanwhile, although the above description explains the sequential transmission and reception of the ultrasonic signals, the transmission and reception of these ultrasonic signals can be performed independently and simultaneously. That is, while the transmission signals may be provided sequentially, the reception signals may be received independently and simultaneously, and the signals received in this manner can be processed as if they were received sequentially by combining time delays. Through this, the reception mode can be processed in parallel in a so-called post-processing manner.

[0121] Figure 6 is a schematic diagram illustrating the step of acquiring signal information for each coordinate of the lens position of Figure 2.

[0122] That is, referring to FIG. 6, with respect to the first position (P1), unidirectional transmission and reception are performed so that all coordinates on the lens position (601) {(x1, y1), ... (x p , y p )} (p is a natural number) can be obtained, and likewise, by performing transmission and reception in the other direction, all coordinates on the lens position (601) {(x1, y1), ... (x p , y p )}(p is a natural number) can be obtained.

[0123] Through this, when transmitting and receiving ultrasound at the first position (P1), an arbitrary coordinate (x) of the lens position (601) p , y p Regarding ), coordinate information for one-way transmission and reception, and coordinate information for other-way transmission and reception can be obtained.

[0124] Furthermore, by transmitting and receiving ultrasound with respect to the second position (P1), an arbitrary coordinate (x) of the lens position (601) is likewise p , y p Regarding ), coordinate information for one-way transmission and reception, and coordinate information for other-way transmission and reception can be obtained.

[0125] Furthermore, for any position (Px) included in the visualization area (800), the same applies to any coordinate (x) of the lens position (601). p , y p Regarding ), coordinate information for one-way transmission and reception, and coordinate information for other-way transmission and reception can be obtained.

[0126] Meanwhile, when obtaining coordinate information during transmission and reception as described above, it is possible to obtain information using the following matrix. That is, as previously explained, after sequentially or independently transmitting the first to nth ultrasonic signals (n is a natural number) to the one-sided transceiver as the transmitter, reception is performed for each of the first to nth ultrasonic signals for each of the p ultrasonic signals to the other-sided transceiver as the receiver, thereby constructing n*p transmission and reception matrices ( ) can.

[0127] Afterwards, the above n*q transmission and reception matrix can be converted into q beam forming modes (where q is a natural number and may be equal to n or p) passing through the lens position to derive q*q matrices. Thus, by transposing the derived matrix q*q, it is possible to convert the one-sided transmission and reception unit into a receiver and the other-sided transmission and reception unit into a transmitter. Accordingly, even if the one-sided transmission and reception unit is utilized as a transmitter and the other-sided transmission and reception unit as a receiver, the case where the one-sided transmission and reception unit becomes a receiver and the other-sided transmission and reception unit becomes a transmitter can also be implemented through signal reconstruction, and consequently, the transmission and reception steps can be minimized.

[0128] FIGS. 7a and 7b are schematic diagrams illustrating the steps of transmitting and receiving ultrasonic signals in an acoustic lens design method according to another embodiment of the present invention.

[0129] Referring to FIG. 7a and FIG. 7b, in the acoustic lens design method according to the present embodiment, in the step of acquiring the ultrasonic transmission and reception signal (step S10), one side transmission and reception unit (100) and one side transmission and reception unit (200) are each provided, so that transmission and reception can be performed in one direction or the other direction in a one-to-one correspondence between the first channel (101) and the second channel (201).

[0130] As described above, by performing transmission and reception in one direction and the other direction using the first channel (101) and the second channel (201), for any position (Px) included in the visualization area (800) as explained in FIG. 6, any coordinate (x) of the lens position (601) p , y p Regarding ), coordinate information for one-way transmission and reception, and coordinate information for other-way transmission and reception can be obtained.

[0131] Accordingly, the step (step S10) of obtaining an ultrasonic transmission and reception signal for the visualization area (800) is terminated.

[0132] Afterwards, referring to FIGS. 1 and FIGS. 2, the signal information acquisition unit (300) acquires signal information for each coordinate of the lens position (601) from the acquired ultrasonic transmission and reception signal (step S20).

[0133] As previously explained, through the acquired ultrasonic transmission and reception signal, for any position (Px) included in the visualization area (800), an arbitrary coordinate (x) of the lens position (601) p , y p It is possible to obtain coordinate information for one-way transmission and reception in ), and coordinate information for other-way transmission and reception.

[0134] Ultimately, in the signal information acquisition unit (300), an arbitrary coordinate (x) of the lens position (601) p , y pSignal information can be obtained at ), where the signal information refers to the aforementioned arbitrary coordinate (x p , y p It means information about the magnitude and phase of the above ultrasonic signal in ).

[0135] In particular, when performing the transmission and reception of the preceding ultrasonic signal, an arbitrary coordinate (x p , y p When calculating the time between the transmission and reception of the ultrasonic signal at ), an arbitrary coordinate (x) of the lens position (601) p , y p Magnitude and phase information of the ultrasonic signal at ) can be obtained. That is, assuming that the ultrasonic signal passes through the medium at the same speed, the corresponding coordinate (here, the corresponding coordinate refers to an arbitrary coordinate (x p , y p The time difference between transmission and reception can be derived through the selected coordinates (meaning the coordinates among them), and through this, the magnitude and phase information of the ultrasonic signal passing through the coordinates can be obtained.

[0136] Afterwards, referring to FIGS. 1 and FIGS. 2, the signal mapping unit (400) performs mapping of the signal information obtained from the signal information acquisition unit (300) for each coordinate of the lens position (601) (step S30).

[0137] Figures 8a and 8b are images showing the results of mapping the acquired signal information of Figure 2 to each coordinate.

[0138] That is, as previously explained, for each case where an ultrasonic signal is transmitted and received in one direction and the other direction through the signal information acquisition unit (300), an arbitrary coordinate (x) of the lens position (601) p , y p Signal information can be obtained from ).

[0139] Accordingly, FIG. 8a is an image of the result (401) of mapping the magnitude and phase information of the ultrasonic signal at all coordinates of the lens position (601) for each coordinate when the ultrasonic signal is transmitted and received in one direction (i.e., when one side transceiver is the transmitter and the other side transceiver is the receiver).

[0140] In addition, FIG. 8b is an image of the result (402) of mapping the magnitude and phase information of the ultrasonic signal at all coordinates of the lens position (601) for each coordinate when the ultrasonic signal is transmitted and received in the other direction (i.e., when the other transceiver is the transmitter and the one transceiver is the receiver).

[0141] As described above, through the signal mapping unit (400), the signal information obtained through the signal information acquisition unit (300) can be distinguished into one-way and other-way signal information and imaged to derive a mapping result.

[0142] Meanwhile, the images (401, 402) of the mapping results exemplified in FIGS. 8a and 8b represent a state in which there is no lens designed at the lens position (601), and the result is a state in which the ultrasonic signal is distorted and transmitted by the distortion target (700).

[0143] Afterwards, referring to FIGS. 1 and FIGS. 2, the phase difference derivation unit (500) calculates a mapping vector based on the mapping result of the signal mapping unit (400) to derive the phase difference for each coordinate of the lens position (601) (step S40).

[0144] The result mapped for each coordinate of the lens position (601) through the signal mapping unit (400) can be defined as a complex vector by assigning the magnitude and phase of the ultrasonic signal, which is signal information, as two factors of the complex vector.

[0145] That is, the magnitude and phase of the ultrasonic signal (referred to as the first phase information), which is signal information derived from the mapping result of FIG. 8a, that is, the result of performing signal transmission and reception in one direction, can be defined as the first complex number vector. Additionally, the magnitude and phase of the ultrasonic signal (referred to as the second phase information), which is signal information derived from the mapping result of FIG. 8b, that is, the result of performing signal transmission and reception in the other direction, can be defined as the second complex number vector. At this time, the first complex number vector is a set of vectors derived for all coordinates of the lens position (601), and the second complex number vector is also a set of vectors derived for all coordinates of the lens position (601).

[0146] Thus, the phase difference derivation unit (500) can derive the angle between the first complex vector and the second complex vector at each coordinate by performing an operation of the inner product of the first complex vector and the second complex vector at each coordinate. Thus, the phase difference derivation unit (500) can derive the phase difference for each of all coordinates of the lens position (601), and the phase difference ultimately refers to the degree of aberration or wavefront distortion.

[0147] At this time, the phase difference information derived through the phase difference derivation unit (500) relates to the signal distortion state caused by the distortion target (700) at each coordinate of the lens position (601). Accordingly, as the transmission and reception signals are repeatedly acquired and the phase difference derivation operation is repeatedly performed, the accuracy and precision of the derived phase difference information increase.

[0148] Afterwards, referring to FIGS. 1 and FIGS. 2, the lens design unit (600) designs a lens to cancel out the phase difference based on the phase difference information derived through the phase difference derivation unit (500) (step S50).

[0149] As previously explained, the phase difference refers to the distortion state of the ultrasonic signal at each coordinate of the lens position (601) as the distortion target (700) is positioned interposed therein; therefore, if the phase difference at each coordinate of the lens position (601) is offset, the distortion caused by the distortion target (700) can be corrected.

[0150] In particular, the phase difference at each coordinate of the lens position (601) can be considered a physical factor, and the phase difference can be offset by designing the thickness of the lens at each coordinate.

[0151] Figures 9a and 9b are examples of lenses designed through the steps of designing the lens of Figure 2.

[0152] Accordingly, as shown in FIG. 9a and FIG. 9b, the lens design unit (600) can derive the thickness of the lens corresponding to each phase difference of the lens position (601) under the assumption that the lens is positioned at the lens position (601), and thereby design the entire lens (610, 611) placed at the lens position (601).

[0153] That is, the thickness at each position of the lens (610, 611) can be derived through a calculation in which an ultrasonic time delay having an opposite sign to cancel out the previously calculated phase difference is divided by the difference between the reciprocal of the wave speed of the background material and the reciprocal of the wave speed of the lens material. At this time, the ultrasonic time delay can be calculated by standardizing the calculated phase difference into periods and then multiplying it by the ultrasonic period in time units.

[0154] Ultimately, the lenses (610, 611) can be designed to vary in various ways depending on the wave velocity of the background material through which the ultrasonic signal is transmitted and the wave velocity of the material contained in the lenses. At this time, since the lenses (610, 611) can be formed from various materials such as polymers, metals, and composite materials, it is sufficient if information regarding the characteristics of the material contained in the lenses is provided in advance.

[0155] For example, even when the same phase difference information is provided, depending on whether the distortion target (700) has an ultrasonic speed slower or faster than the background material, respectively, the shape of the designed lens (610, 611) can have a structure that is inverted from each other, as shown in FIG. 9a and FIG. 9b.

[0156] Furthermore, in this embodiment, the lens design result is exemplified when the lens position (601) is positioned between the distortion target (700) and the one-sided and other-sided transceivers (100, 200). It is obvious that the lens design result may differ if the lens position (601) is positioned between the distortion target (700) and the visualization area (800).

[0157] FIG. 10a is a schematic diagram illustrating the state of providing an ultrasonic signal when the lens of FIG. 9a is not applied, and FIG. 10b is a schematic diagram illustrating the state of providing an ultrasonic signal when the lens of FIG. 9a is applied.

[0158] Referring to FIG. 10a, when an ultrasonic signal is incident (110) from outside the subject of treatment, diagnosis, or examination, if a distortion target (700) is present at the front of the visualization area (800), the ultrasonic signal (110) is distorted by the distortion target (700), that is, the waveform is refracted or scattered (120) in a disorderly manner and provided to the visualization area (800).

[0159] In contrast, referring to FIG. 10b, when an ultrasonic signal (110) is incident from outside the object, even if the distortion target (700) is present at the front of the visualization area (800), if the lens (610) is additionally provided, the ultrasonic signal (110) passes through the lens (610) before being distorted by the distortion target (700) and enters in a distorted state with an opposite waveform, and thus the ultrasonic signal (130) finally provided to the visualization area (800) maintains the same waveform as the incident ultrasonic signal (110).

[0160] Furthermore, the design of the lens (610) as described above is performed based on the results derived through the design method described above, assuming the lens position (601), so that a lens suitable for the subject can be designed in advance before treatment, diagnosis, or examination is performed on the actual subject. Through this, ultrasonic signals can be accurately provided to the visualization area for various subjects and various distorted objects.

[0161] Figures 11a and 11b are images showing the results of mapping the acquired signal information of Figure 2 to each coordinate when the lens of Figure 9a is applied.

[0162] That is, as shown in FIG. 11a, in the result (403) obtained by mapping the signal information obtained at all coordinates of the lens position (601) before the lens (610) is positioned, it can be confirmed that the wavefront of the ultrasonic signal is refracted or scattered in a disorderly manner. Such ultrasonic signals are also confirmed in FIG. 8a and FIG. 8b.

[0163] In contrast, as shown in FIG. 11b, when the lens (610) is positioned, as confirmed in the mapping result (404), it can be confirmed that the wavefront of the ultrasonic signal is maintained uniformly, and through this, it can be confirmed that the lens (610) can correct signal distortion caused by the distortion target (700).

[0164] FIGS. 12a to 12c are block diagrams illustrating a meta-ultrasonic probe including an acoustic lens fabricated using the acoustic lens design system of FIG. 1.

[0165] First, referring to FIG. 12a, when the lens (610) is manufactured through the acoustic lens design system (10) described with reference to FIG. 1, the manufactured lens can be positioned adjacent to the ultrasonic probe (920) as a so-called acoustic lens (910) to form the meta-ultrasonic probe (900).

[0166] At this time, as previously explained, the ultrasonic probe (920) may be at least one of the one-sided transceiver (100) and the other-sided transceiver (200), and the design described above for the acoustic lens (910) may be performed by transmitting and receiving ultrasonic signals through the ultrasonic probe (920).

[0167] That is, the meta-ultrasonic probe (900) includes the ultrasonic probe (920) and the acoustic lens (910). At this time, the ultrasonic probe (920) performs the transmission and reception of ultrasonic signals for the design of the acoustic lens (910), and at the same time, the acoustic lens (910) is finally positioned adjacent to the ultrasonic probe (920) to transmit and receive ultrasound for performing various diagnoses, treatments, or examinations.

[0168] At this time, the ultrasonic probe (920) may be a conventional general ultrasonic probe.

[0169] Additionally, as shown in FIG. 12b, the meta-ultrasonic probe (901) may further include an active control unit (930) in addition to the acoustic lens (910) and the ultrasonic probe (920).

[0170] The active control unit (930) can actively control various states of the acoustic lens (910), for example, actively control the position of the acoustic lens (910), actively control the distance between the acoustic lens (910) and the ultrasonic probe (920), or control the attachment and detachment of the acoustic lens (910).

[0171] Meanwhile, active control of the state of the acoustic lens (910) is performed to minimize such distortion when it is determined that the signal is distorted through the additional transmission and reception of the ultrasonic signal while the acoustic lens (910) is designed and positioned adjacent to the ultrasonic probe (920).

[0172] Accordingly, although not illustrated, the meta-ultrasonic probe (901) may be configured with the same system as the design system of the aforementioned acoustic lens (910) and may be equipped with a separate judgment unit to provide control commands to the active control unit (930). That is, if the judgment unit determines that the signal is distorted even when the acoustic lens (910) is placed, it applies the same method as the lens design method using the lens design system (10) described with reference to FIG. 1 to receive information for the optimal placement of the acoustic lens (910). Thus, based on the information regarding the optimal placement of the acoustic lens (910), additional control regarding the position, spacing, or attachment / detachment of the acoustic lens (910) can be performed through the active control unit (930).

[0173] Meanwhile, referring to FIG. 12c, the meta ultrasonic probe (902) may include a front material (950), a rear material (970), and a piezoelectric element (960) in place of the ultrasonic probe (920).

[0174] That is, ultrasonic waves are generated using the piezoelectric element (960), and the acoustic lens (910) can be configured to be positioned adjacent to the piezoelectric element (960). At this time, the front material (950) and the rear material (970) may be materials that cover the front and rear sides of the piezoelectric element (960).

[0175] Thus, by omitting a separate ultrasonic probe and utilizing the ultrasonic signal generated through the piezoelectric element (960), the meta-ultrasonic probe (902) can provide an ultrasonic signal for various diagnoses, treatments, or examinations.

[0176] Furthermore, the meta-ultrasonic probes (900, 901, 902) described in FIGS. 12a to 12c can be applied as ultrasonic probes for ultrasonic transmission and reception in an ultrasonic imaging diagnostic device. In this case, the ultrasonic imaging diagnostic device may further include separate signal and data processing units for processing ultrasonic signals in conjunction with ultrasonic transmission and reception in the meta-ultrasonic probes and displaying them as images. In this case, the signal and data processing units are configured for processing conventional ultrasonic signals, so a detailed description is omitted.

[0177] According to the embodiments of the present invention as described above, since a lens is designed based on a signal that is distorted by passing through a distortion target while the distortion target is present, the signal distortion state caused by the actual distortion target can be reflected more accurately compared to a lens designed through conventional virtual simulation results, thereby enabling more accurate and effective correction of ultrasonic signal distortion using the designed lens.

[0178] That is, by using one-sided and other-sided transceivers, based on the ultrasonic signal transmitted and received through the distortion target and into the visualization area, a signal that is distorted according to the distortion target can be derived, and a lens can be designed to offset the degree of distortion of the distorted signal.

[0179] At this time, the one-sided transceiver and the other-sided transceiver both perform the role of a transceiver and a receiver, and thus can acquire signals at each location of the visualization area. Therefore, based on signals passing through the distortion target in various directions, the transmission and reception signals at each location can be acquired, and the signal distortion state caused by the distortion target can be precisely acquired.

[0180] In addition, even without information on whether the signal received from the visualization area corresponds to a specific location, the signal corresponding to a specific location can be extracted based on information regarding various coordinates of the lens position obtained through the one-sided and other-sided transceivers that perform both the roles of the transceiver and receiver, and thereby signal information for each coordinate of the lens position can be obtained.

[0181] In addition, the phase difference for each coordinate of the lens position can be derived through simple vector operations on the result mapped from the signal information obtained when the one-sided transceiver acts as a transmitter and the result mapped from the signal information obtained when the other-sided transceiver acts as a transmitter, and thereby, a lens structure that cancels out the phase difference for each coordinate of the lens position can be designed. Accordingly, since the lens can be designed based on numerical information such as a simple phase difference, the ease of designing the lens and the ease of manufacturing the designed lens are improved.

[0182] Accordingly, when performing various diagnoses or treatments, or when conducting various tests, even if a specific distortion target that distorts the ultrasonic signal exists inside, by immediately designing the lens through the transmission and reception of the ultrasonic signal, the ultrasonic signal for the structure can be acquired more accurately and precisely, thereby improving the accuracy and precision of diagnosis, treatment, and testing.

[0183] Although the present invention has been described above with reference to preferred embodiments, those skilled in the art will understand that various modifications and changes can be made to the invention without departing from the spirit and scope of the invention as set forth in the following claims.

Claims

1. One-sided and other-sided transceivers that transmit and receive ultrasound over a visualization area and acquire an ultrasound transmission and reception signal for a lens position where the designed lens is located; A signal information acquisition unit that acquires signal information for each coordinate of the lens position from the acquired ultrasonic transmission and reception signal; A signal mapping unit that maps acquired signal information to each coordinate of the lens position; A phase difference derivation unit that derives a phase difference for each coordinate of the lens position by calculating a mapping vector from the above mapping result; and An acoustic lens design system comprising a lens design unit that designs a lens to cancel out the above-mentioned phase difference.

2. In paragraph 1, the lens is, An acoustic lens design system characterized by being designed such that it is assumed to be positioned between a distortion target that induces distortion of an ultrasonic reception signal and the one-sided and other-sided transmitting and receiving units.

3. In paragraph 1, the lens is, An acoustic lens design system characterized by being designed to be positioned between a distortion target that induces distortion of an ultrasonic reception signal and the visualization area.

4. In paragraph 1, each of the above-mentioned one-side and other-side transceivers is, An acoustic lens design system characterized by including both a transmitting unit that generates and transmits an ultrasonic signal and a receiving unit that receives the ultrasonic signal.

5. In Paragraph 4, The above-mentioned one-sided transceiver includes a single channel, and An acoustic lens design system characterized in that the other side transceiver includes at least one channel.

6. In Paragraph 5, The ultrasonic signal transmitted from one channel of the above-mentioned one-sided transceiver is reflected at each location of the visualization area and received by each of at least one channel of the other-sided transceiver, and An acoustic lens design system characterized in that the signal received at each of at least one channel of the other side transmitting and receiving unit is a signal reflected at different locations in the visualization area.

7. In Paragraph 5, The ultrasonic signal transmitted from each of at least one channel of the other transceiver is reflected at each location of the visualization area and received by one channel of the first transceiver. An acoustic lens design system characterized in that signals transmitted from each of at least one channel of the other side transmitting and receiving unit are reflected at different locations in the visualization area.

8. In paragraph 1, the signal information acquisition unit, An acoustic lens design system characterized by calculating the time between transmission and reception of the ultrasonic signal for each of the above coordinates and obtaining magnitude and phase information of the ultrasonic signal for each of the above coordinates.

9. In paragraph 8, the signal information acquisition unit is, A first phase information in the case where the above-mentioned one-sided transceiver is a transmitter and the above-mentioned other-sided transceiver is a receiver, and An acoustic lens design system characterized by acquiring second phase information in the case where the other side transceiver is the transmitter and the one side transceiver is the receiver.

10. In claim 9, the phase difference derivation unit is, The magnitude and phase information of the ultrasonic signal for each of the above coordinates are defined as complex vectors for each coordinate, and An acoustic lens design system characterized by deriving a phase difference for each coordinate by taking the inner product of a first complex vector for the first phase information and a second complex vector for the second phase information.

11. In Paragraph 1, An acoustic lens design system characterized in that the above-mentioned visualization area is an area where the subject of diagnosis, examination, or treatment using ultrasound is located.

12. A step of transmitting and receiving ultrasound over a visualization area to obtain an ultrasound transmission and reception signal for a lens position where the designed lens is located; A step of obtaining signal information for each coordinate of the lens position from the acquired ultrasonic transmission and reception signal; A step of mapping the acquired signal information to each coordinate of the lens position; A step of deriving a phase difference for each coordinate of the lens position by calculating a mapping vector from the above mapping result; and An acoustic lens design method comprising the step of designing a lens to cancel out the above-mentioned phase difference.

13. In paragraph 12, the step of acquiring the ultrasonic transmission and reception signal is, A step of transmitting the first to n ultrasonic signals (n is a natural number) sequentially or independently to the one-sided transceiver as a transmitter; and An acoustic lens design method characterized by including the step of receiving, for each of the first to n ultrasonic signals, the first to n ultrasonic signals reflected at a specific location in the visualization area sequentially or independently, using the other transceiver as a receiver.

14. In Clause 12, the step of acquiring the ultrasonic transmission and reception signal is, A step of sequentially or independently transmitting the n+1 to m ultrasonic signals (m is a natural number) to the other transceiver as a transmitter; and An acoustic lens design method characterized by including the step of receiving, for each of the n+1 to m ultrasonic signals, the n+1 to m ultrasonic signals reflected from a specific position in the visualization area sequentially or independently, using the above-mentioned one-sided transmitting and receiving unit as a receiving unit.

15. In paragraph 12, the step of acquiring the ultrasonic transmission and reception signal is, A step of transmitting the first to n ultrasonic signals (n is a natural number) sequentially or independently to the above-mentioned one-sided transceiver to the transmitting unit; A step of forming an n*p transmission and reception matrix by using the other side transceiver as a receiver, receiving for each of the first to n ultrasonic signals for each of the p ultrasonic signals ( ); and An acoustic lens design method characterized by including the step of converting the above n*q transmission and reception matrix into q beamforming modes (where q is a natural number and may be equal to n or p) passing through the above lens position to derive q*q matrices.

16. In the step of designing the lens according to Clause 12, An acoustic lens design method characterized by deriving the thickness at each position of the lens through an operation in which an ultrasonic time delay having an opposite sign to cancel out the phase difference is divided by the difference between the reciprocal of the wave velocity of the background material and the reciprocal of the wave velocity of the lens material.

17. Ultrasonic unit for transmitting and receiving ultrasound; and A meta-ultrasonic probe comprising an acoustic lens manufactured using the acoustic lens design system of claim 1, positioned adjacent to the above-mentioned ultrasonic unit.

18. In Paragraph 17, The above-mentioned ultrasonic unit includes an ultrasonic probe, and A meta-ultrasonic probe characterized in that the above-mentioned ultrasonic probe is at least one of the above-mentioned one-sided and other-sided transceivers.

19. In Paragraph 18, A meta-ultrasonic probe further comprising an active control unit that controls the position of the acoustic lens, the distance between the acoustic lens and the ultrasonic probe, or the mounting and detachment of the acoustic lens.

20. In Paragraph 17, A meta-ultrasonic probe characterized in that the above-described ultrasonic unit includes a piezoelectric element.

Images