Broad-beam imaging
Abstract
Problem to be solved.To provide a system and a method for inspecting a substance under investigation by using an ultrasonic beam. Echolocation data is generated using a multidimensional transformation that can use phase and amplitude information to distinguish echoes generated from ultrasonic beam components generated using different ultrasonic transducers 530. To. Since the multidimensional transformation does not depend on the use of transmit or receive beamlines, the multidimensional region can be visualized using a single ultrasonic transmission. In some embodiments, this increases the image frame rate and reduces the amount of ultrasonic energy required to generate the image. [Selection diagram] Fig. 5
Term
Projected expiry 29 January 2030.
- Priority
- Filed
- Published
- Today
- Projected expiry
10 claims: 6 independent, 4 dependent
- 1検査対象物質を検査する超音波システムによって実行される方法であって、 複数のトランスデューサにより、前記複数のトランスデューサの各トランスデューサによって発生された成分を含む超音波ビームを検査対象物質に送信する段階と、 前記超音波ビームと前記検査対象物質の間の相互作用によって発生されたエコーを受信する段階と、 受信したエコーから第1のデータを発生させる段階であって、前記第1のデータは位相情報及び振幅情報を含む値をとり、時間次元と関連付けられ、少なくとも一つの空間次元上で分布するデータを表す、段階と、 前記位相情報及び/又は振幅情報を使用して、受信したエコーの中から、前記複数のトランスデューサのうちのトランスデューサの部分集合によって発生された超音波ビーム成分から生じたエコーを区別する段階と、 区別されたエコーを使用して、前記第1のデータを、前記第1のデータよりも少なくとも1次元以上大きい空間次元上で分布した値をとる第2のデータに変換する段階と、を有する方法。
- 2前記振幅情報、前記位相情報または前記振幅情報と位相情報の両方が受信したエコーの間でエコーを区別するため使用される、請求項1記載の方法。
- 3前記超音波ビームは2次元以上の空間次元を含む対象領域を検査するように設定されており、 当該方法は、追加的超音波ビームを前記検査対象物質に送信する段階を更に含み、前記追加的超音波ビームは2次元以上の空間次元を含む前記対象領域と重なり合う第2の対象領域を検査するように設定されている、請求項1記載の方法。
- 4前記超音波ビームは2次元以上の空間次元を含む対象領域を検査するよう構成されており、 当該方法は、2次元以上の空間次元を含む対象領域と重なり合う第2の対象領域を検査するように設定されている追加的超音波ビームを前記検査対象物質に送信する段階と、 前記追加的超音波ビームと前記検査対象物質の間の相互作用によって発生した第2のエコーを受信する段階と、 受信した第2のエコーを使用して第3のデータを発生させる段階と、 前記第2のデータと前記第3のデータの両方を使用して画像を発生させる段階と、を更に有する請求項1記載の方法。
- 5検査対象物質を検査する超音波システムによって実行される方法であって、 単一の超音波ビームを検査対象物質に送信する段階と、 前記超音波ビームと前記検査対象物質の間の相互作用によって発生されたエコーを受信する段階と、 受信したエコーから、位相情報及び振幅情報を含み、時間次元及び少なくとも第1の空間次元に関連付けられた値をとる第1のデータを発生させる段階と、 変換されるべき第1のデータの一部を選択するために前記位相情報及び/又は前記振幅情報を用い、少なくとも第2の空間次元及び第3の空間次元に分布する第2のデータを生成し得る変換を使用して、前記第1のデータの一部を第2のデータに変換する段階と、を有する方法。
- 6検査対象物質を検査する超音波システムによって実行される方法であって、 超音波ビームを検査対象物質に送信する段階と、 送信された超音波ビームと前記検査対象物質との間の相互作用によって発生されたエコーを受信する段階と、 受信されたエコーを使用して、時間及び第1の空間次元における多数の位置と関連付けることが可能である第1のデータを発生させる段階と、を有し、位置の個数は少なくとも64個であり、位置の個数との関連付けは時間との関連付けとは独立であり、当該方法が、 前記第1のデータを、少なくとも前記第1の空間次元及びある第2の空間次元と関連付けることができる値をとる第2のデータに変換する段階を更に有する、方法。
- 7第2の超音波ビームと前記検査対象物質との間の相互作用によって発生させられた第2のエコーを受信する段階と、 受信した第2のエコーを使用して第3のデータを発生させる段階を更に有し、前記第1のデータと前記第3のデータの組み合わせは、前記第1のデータと同じ次元をもつ、請求項6記載の方法。
- 8検査対象物質を検査する超音波システムによって実行される方法であって、 少なくとも一つの空間次元において位置をずらされた少なくとも二つの重なり合う超音波ビームを検査対象物質中に送信する段階と、 前記少なくとも二つの重なり合う超音波ビームと前記検査対象物質との間の相互作用によって生成されたエコーを受信する段階と、 受信されたエコーから、振幅情報および位相情報を含み前記少なくとも一つの空間次元と関連付け可能な値をもつデータを生成する段階と、 受信ビーム形成に先立って、受信されたエコーから生成されたデータを組み合わせる段階とを有し、前記組み合わせる段階は前記生成されたデータの振幅および位相を調整することを含む、方法。
- 9検査対象物質を検査する超音波システムによって実行される方法であって、 少なくとも一つの空間次元において位置をずらされた少なくとも二つの重なり合う超音波ビームを検査対象物質中に送信する段階と、 前記少なくとも二つの重なり合う超音波ビームと前記検査対象物質との間の相互作用によって生成されたエコーを受信する段階と、 受信されたエコーから、振幅情報および位相情報を含み前記少なくとも一つの空間次元と関連付け可能な値をもつデータを生成する段階と、 前記少なくとも二つの重なり合う超音波ビームから同一の受信ビームが形成される受信ビーム形成を実行する段階と、 受信ビーム形成後に、受信されたエコーから生成されたデータを組み合わせる段階とを有し、前記組み合わせる段階は前記生成されたデータの振幅および位相を調整することを含み、前記データの振幅および位相の調整は前記少なくとも一つの空間次元の好適な線形変換において実行され、前記好適な線形変換はフーリエ変換である、方法。
- 10超音波撮像システムであって:検査対象物質の分析の要件に対するユーザ指示を受領するよう構成され、前記ユーザ指示に従って前記検査対象物質の撮像のための超音波ビームの数および形を決定するようさらに構成された制御装置と、 前記制御装置によって決定された超音波ビームの数および形に対応する超音波ビームを前記検査対象物質に送信するよう構成され、送信された超音波ビームに応答して生成されたエコーを検出して検出されたエコーに関するアナログ・チャネル・データを生成するようさらに構成されたトランスデューサ・アレイと、 振幅情報および位相情報を含むデジタル・チャネル・データを生成するよう構成されたマルチチャネルA/D変換器と、 前記デジタル・チャネル・データを記憶するよう構成されたチャネル・データ・バッファと、 記憶されたデジタル・チャネル・データの少なくとも振幅情報および位相情報の変換を通じて、送信ライン、受信ライン、走査ラインを使うことなく、多次元エコーロケーション・データを生成するよう構成された信号プロセッサと、 生成された多次元エコーロケーション・データを記憶するよう構成された、あらかじめ選択された座標系をもつエコーロケーション・データ・アレイと、 表示装置上に表示するための画像を生成するよう構成された画像コンバータであって、前記エコーロケーション・データ・アレイの前記あらかじめ選択された座標系に記憶された前記多次元エコーロケーション・データは前記表示装置上の特定の位置にマッピングされる、画像コンバータとを有する、超音波撮像システム。
Independent claims10
97 paragraphs, as filed
The present invention relates to the field of visualization, and more particularly to the field of ultrasonic visualization.
[Cross-reference to related applications] This application was filed on April 5, 2002, and the title of the invention assigned to the same applicant as this application is "Broad-beam Imaging". This is a priority claim application based on patent application No. 60 / 370,632.
This application is a partial continuation of US Patent Application No. 10 / 039,922, whose title of the invention, filed on October 20, 2001, is "Block Switching in Ultrasound Imaging".
This application was filed on May 18, 2001, and the title of the invention is "Parallel Multiple Mode / Multiple Band (M)".<sup>3</sup>B) Ultrasound visualization (Simultaneous Multi-Mode and Multi-Band (M)<sup>3</sup>B) Ultrasonic Imaging) "Simultaneously pending US Patent Application No. 10 / 039,862, filed May 31, 2001, the title of the invention is" System and Method. US Patent Application No. 09 / 872,541, which is "for Phase Inversion Ultrasonic Imaging", and the invention, which was filed on March 19, 2002, is called "Post-Processing Ultrasound Color Doppler Imaging System and Method (System and)". Method for Post-Processing Ultrasound Color Doppler Imaging) . The content of the related application is cited for reference. The related application has been transferred to the same applicant as this application.
Ultrasound imaging is a frequently used method for inspecting a wide range of substances. This method is particularly popular in the medical field because it is relatively non-invasive, low cost, and has a fast diagnostic cycle. Ultrasound imaging is typically achieved by generating ultrasound, pointing towards the substance under investigation, and observing the reflections that occur at the boundaries of dissimilar substances. For example, in medical applications, the observed reflexes occur at the boundaries of the patient's tissue. Observed reflections are converted to electrical signals by the receiving device (transducer), using methods known in the art to determine the location of an echo source is processed for. The obtained data is displayed using a display device such as a monitor.
The process of generating an ultrasonic beam by the prior art and analyzing the obtained echo is called "beam formation (processing method)". The production process optionally defines "transmitted" beam characteristics by aperture apodization, steering, and / or focusing. The analysis process optionally calculates a "received beam" and the received echoes are processed to isolate the echoes generated along the narrow area. Since this calculation involves identifying a one-dimensional line that is believed to have been along when the echo occurred, it is also referred to below as the "echo line calculation". Through beam formation, a one-dimensional set of echolocation data is generated using each transmit and / or receive beam. Echolocation data is position data related to the physical location of one or more echo sources and optionally includes intensity, velocity and / or similar physical information. The echolocation data includes rear beam forming raw data, detection data, or image data. Multidimensional echolocation data, such as ultrasound images, is generated by scanning the field of view within a material during an investigation using multiple transmit and / or receive beams.
The ultrasonic beam transmitted to the substance under investigation during the transmission phase is generated by supplying an electronic signal to the transducer. The ultrasonic beam is scattered, resonated, attenuated and / or reflected as it propagates through the material under investigation. Part of the reflected signal is received by the transducer and detected as an echo. The receiving transducer converts the echo signal into an electronic signal and optionally supplies the echo signal to an echo line calculator (beam former) that performs essential echo line calculations for analysis using the received beam.
After beam formation, the image scan converter uses the calculated echolocation data to generate the image data. For prior art systems, the image formation rate (frame rate) is limited by at least the total pulse return time of the total ultrasound beam used to generate the echo image. The pulse return time is the time from when the ultrasonic beam is transmitted to the substance under investigation until the last reflected echo is detected. Limiting the frame rate causes temporal artifacts due to the relative motion between the ultrasonic system and the substance under investigation.
FIG. 1 shows a prior art ultrasonic system 100. The ultrasonic system 100 includes an element array 105 of transducer elements 110, a substrate 120, an optional matching layer 130, a transmit / receive switch 140, and a beam transmitter 150. The substrate 120 supports the device array 105 and attenuates the ultrasonic energy propagating towards the substrate 120. The matching layer 130 transfers ultrasonic energy from the transducer element 110 to the substance under investigation (not shown). The transducer elements 110 include separate transducer elements 110A-110H, which are separately connected to the beam transmitter 150 by conductors 115 and 1117 via a transmit / receive switch 140. The transmit / receive switch 140 may include a multiplexer 145, which allows the number of conductors 117 to be less than the number of conductors 115. In the transmission phase, the beam transmitter 150 generates an electron pulse. The electronic pulse is supplied via the transmission / reception switch 140, is supplied to some or all of the transducer elements 110A-110H, and is converted into the ultrasonic pulse 160. Overall, the ultrasonic pulse 160 forms an ultrasonic beam 170 that examines the substance under investigation.
The ultrasonic beam 170 is focused to limit the area where the echo is generated. When the echo source is confined to a small area, the calculation of echolocation data is simplified by assuming that the echo source is along the "transmission line". Under this assumption, the work of the beam calculator is simplified to the problem of determining the position of the echo source in one dimension. This position is determined using the echo return time. The accuracy of this assumption and the spacing of the transmission lines are important factors in determining the resolution of the prior art ultrasonic system. When the beam is finely focused, the resolution can be easily increased as compared with the coarsely focused beam. Similar assumptions and results appear in the context of the analysis related to the calculated received beam.
In the prior art focusing system shown in FIG. 2, the element array 105 is phased configured to focus the ultrasonic beam 170 by varying the timing of the electron pulses 210 applied to the transducer elements 110A-110H. It is an array. In the case of this system, the electronic pulse 210 is generated by the beam transmitter 150 and passed through the transmission / reception switch 140. The electron pulse 210 is delayed using a delay generator (not shown) and fed to the transducer elements 110A-H. The ultrasonic beam 170 is formed when the transducer elements 110A-H appropriately convert the delayed electron pulse into the ultrasonic pulse 160 (FIG. 1). Once formed, the ultrasonic beam 170 is directed towards the transmit beamline 250, including the focal point 230, resulting in a beam body 240 represented by the width of the ultrasonic beam 170. In a similar fashion, the phased excitation of the device array 150 is used to direct (steer) the ultrasonic beam 170 in a particular direction. The cross-sectional intensity of the ultrasonic beam 170 is typically Gaussian around the focal point and has a maximum along the transmitting beamline 250. The shape of the ultrasonic beam 170 depends on the aperture apodization.
In the scanning process, the ultrasonic system 100 transmits a series of separate ultrasonic beams 170 along different transmission beamlines 250 to form an image in two or more spatial dimensions. A particular ultrasonic beam 170 is optionally transmitted in several transmission and reception cycles before generating another ultrasonic beam 170. A reception phase appears between each transmission phase, during which echoes are detected. Since each ultrasonic beam 170 included in the ultrasonic scan requires at least one transmission / reception cycle, the scanning process takes many times longer than the pulse return time. This pulse return time, determined by the speed of sound in the material under investigation, is a major limitation on the rate at which prior art ultrasound images are generated. Furthermore, if the transducer elements 110A-110H move relative to the substance under investigation during the scanning process, unwanted temporal anomalies occur.
FIGS. 3A-3E show a prior art scanning process in a phased array 310 consisting of eight transducer elements 110A-110H. A subset 320A-320E of eight transducer elements 110A-110H is used to generate one separate ultrasonic beam 170A-170E. For example, FIG. 3A shows an ultrasonic beam 170A formed by a subset 320A including transducer elements 110A-110D. The next step in the scanning process is to form an ultrasonic beam 170B using a subset 320B containing transducer elements 110B-110E as shown in FIG. 3B. In the case of this example, the transmit beamline 250B associated with the ultrasonic beam 170B passes through the focal point 230B, which is typically separated from the focal point 230A by a distance that matches the width of one transducer element 110. .. As shown in FIGS. 3C to 3E, each subset 320C to 320E used to generate the ultrasonic beams 170C to 170E is displaced by one transducer element 110 with respect to the subsets 320B to 320D, respectively. are doing. Echoes that appear between each transmit phase and are detected during the receive phase are used to generate echolocation data, which is typically combined to form a display-friendly image. .. The scanning process is repeated to produce a large number of images.
In practice, the phased array 310 includes 64, 128, or more transducer elements 110. The resolution of the echolocation data depends on the aperture and number of transducer elements 110 and the extent to which the transmitting beamline 250 can accurately represent the possible echo sources within the ultrasonic beam 170. The representation of the ultrasonic beam 170A-E using the beamline 250A-E is an approximate representation that determines the resulting echolocation data. Poor approximation limits the resolution of the resulting echolocation data. Therefore, the maximum width of the ultrasonic beam 170A-E is limited by the desired resolution of the echolocation data. The accuracy of the approximation is a function of the distance from the focal point 230A-E, and the accuracy of the approximation deteriorates as this distance increases.
A common implementation uses each pair of received echoes to generate several ultrasonic beams at different focal 230A-E and generate data near focal 230A-E. The data generation of the prior art is limited to the area near the focal point 230A-E. This is because, at greater distances, the approximation of the transmit beamline 250 is inaccurate to obtain echolocation data at the desired resolution. Typically, one receive or transmit beamline 250 is generated for each transmit and receive cycle. The number of beams required to visualize an area depends on the width and depth of the area to be visualized and the desired resolution. By using only echoes near focus 230, only a portion of the total received signal (eg, less than 10%) is used and the remaining received signal is ignored. In the case of the prior art, the detection signal is not fully utilized. Similar drawbacks also occur in systems that utilize synthetic receive lines.
<p> In the prior art, the area to be covered, the transmission beam width, the number of transmission beams 170, and the resolution of the echolocation data are interdependent. The transmitted beamwidth determines the minimum lateral resolution width of the echolocation. Since each transmit beam 170 covers only a limited area, a large number of transmit beams 170 are required to visualize a large area. As the number of transmit beams 170 used increases, the maximum time required to generate an image increases.</p><p> Prior art shortcomings such as pulse return times and image formation rates limited by inadequate use of signals prevent prior art ultrasound systems from fully leveraging advances in microprocessing power. ing. Prior arts have sacrificed these shortcomings to produce images with the highest achievable resolution.</p>
<p> The method of inspecting a substance under investigation according to an embodiment of the present invention includes a procedure (1) in which a plurality of transducers are used to transmit an ultrasonic beam to the substance under investigation, and the ultrasonic beam has a plurality of. Step (2) to receive the echo generated by the interaction between the ultrasonic beam and the substance under investigation, including the components generated by each of the transducers, and generate the first data from the received echo. The first data takes a value including phase information and amplitude information, is associated with the time dimension, is distributed on at least one spatial dimension, and has the procedure (3) to make it, and from the received echo, In order to distinguish the echo generated from the ultrasonic beam component generated by the subset of the transducer among the multiple transducers, the procedure (4) using the phase information and / or the amplitude information and the distinguished echo are used. Therefore, it has a procedure (5) of converting the first data into the second data having a value distributed on a spatial dimension that is at least one dimension larger than the first data.</p><p> The method of inspecting the material under investigation according to one embodiment of the present invention is generated by the procedure (1) of transmitting an ultrasonic beam to the material under investigation and the interaction between the ultrasonic beam and the material under investigation. The procedure for receiving the echo (2) and the procedure for generating the first data from the received echo, which includes the phase information and the amplitude information and takes the values associated with the time dimension and at least the first spatial dimension (3). And, using the phase information and / or the amplitude information to select a part of the first data to be converted, generate the second data distributed in at least the second and third spatial dimensions. It has a procedure (4), in which a part of the first data is converted into the second data by using the conversion obtained.</p><p> The method of inspecting the substance under investigation according to one embodiment of the present invention includes a procedure (1) of transmitting one or more ultrasonic beams to the substance under investigation and one or more transmitted ultrasonic beams. Receives a first echo generated by the interaction between one ultrasonic beam and the material under investigation, which occurs at least at points distributed in the first and second spatial dimensions. Step (2) and the procedure to generate the first data from the received first echo, which is distributed in the time dimension and additionally has a value distributed in at least the first spatial dimension or the second spatial dimension. (3), the procedure (4) to convert the first data into the second data that takes values distributed in at least both the first and second spatial dimensions, and another ultrasonic beam. Echolocation using the procedure (5) to send to the material under investigation, the procedure (6) to receive additional echoes generated using another ultrasonic beam, and the additional echoes received. A procedure (7) to generate a third data that is data and has a specific dimension, and a procedure (8) to combine the third data and the second data so that they have the same dimension as the third data. , Have.</p><p> The method of inspecting a substance under investigation according to an embodiment of the present invention is a procedure (1) of transmitting an ultrasonic beam to the substance under investigation and mutual interaction between the transmitted ultrasonic beam and the substance under investigation. The procedure (2) of receiving the echo generated by the action and the procedure of using the received echo to generate the first data that can be associated with many points in time and the first spatial dimension. And (3), the number of points is at least 64, the relationship with the number of points is independent of the relationship with time, and the first data is at least the first spatial dimension and It further has a procedure (4) of converting to a second data that takes a value that can be associated with a second spatial dimension.</p><p> The method of inspecting the material under investigation according to one embodiment of the present invention includes a procedure (1) in which a plurality of ultrasonic transducers are used to transmit an ultrasonic beam to the material under investigation, and the ultrasonic beam and the material under investigation. The procedure (2) of receiving an echo generated by an interaction with a substance can be associated with the time and the position of two or more first numbers in the first spatial dimension from the received echo. The procedure (3) to generate the first data that takes multiple values that can be made, and the second that can be associated with the position of the second number in the second spatial dimension and the first spatial dimension from the first data. With the procedure (4) to generate the data of, the number of the first position is smaller than the number of the second position, and in the second data, among the second number of positions At least one value that can be associated with one of the values, but not the position of the first number, is generated without the use of interpolation between the values of the first data.</p><p> The method of inspecting the substance under investigation according to one embodiment of the present invention includes a procedure (1) in which a plurality of transducers are used to transmit a plurality of ultrasonic beams to the substance under investigation, and a plurality of ultrasonic beams. The procedure (2) for receiving the first echo generated by the interaction between the first member of the data and the substance under investigation and the first echo received can be associated with the time dimension, at least. The procedure (3) to generate the first echo data, which can be separately associated with two or more positions in the first spatial dimension and takes values that include phase and amplitude information, and in multiple ultrasonic beams. The procedure (4) for receiving the second echo generated by the interaction between at least the second member of the data and the substance under investigation and the second echo received can be associated with the time dimension. The procedure (5) to generate the second echo data, which has a value that can be separately associated with at least two or more positions in the second spatial dimension, the first echo data, and the phase information and / or amplitude. A procedure (6) that uses a data transformation that responds to information to generate the first echolocation data, a procedure (7) that uses the second echodata to generate the second echolocation data, and In order to generate a third echolocation data having the same dimension as the first echolocation data, there is a procedure (8) of combining the first location data and the second location data.</p><p> The method of generating echolocation data according to an embodiment of the present invention can be associated with multiple positions in time and at least one spatial dimension by converting the echo into an echo signal, including phase information and amplitude information. Use the procedure (1) to generate the first data that takes multiple values, the first data, and the data transformation according to the phase information and / or the amplitude information, and associate it with different positions at multiple positions. It has a procedure (2) of generating echolocation data that takes at least one value obtained from two or more members of a plurality of values that can be.</p>
<figref num="1">It is explanatory drawing of the ultrasonic system of the prior art.</figref><figref num="2">It is explanatory drawing of the method of concentrating an ultrasonic beam by a prior art.</figref><figref num="3">(A) to (E) are explanatory views of a conventional scanning process using a phased array consisting of eight transducer elements.</figref><figref num="4">It is a flowchart explaining the outline of the wide beam method by one Example of this invention.</figref><figref num="5">It is a block diagram of the wide beam system according to one Example of this invention.</figref><figref num="6">It is a detailed flowchart of the wide beam design step according to one Example of this invention.</figref><figref num="7A">It is explanatory drawing of the ultrasonic beam generated by using the linear transducer array by one Example of this invention.</figref><figref num="7B">It is explanatory drawing of the ultrasonic beam generated by using the curved transducer array by one Example of this invention.</figref><figref num="7C">It is explanatory drawing of the ultrasonic beam which generates the high frequency irradiation region generated by one Example of this invention.</figref><figref num="7D">It is a graph which plotted the ultrasonic intensity passing through the cross section of a wide beam.</figref><figref num="8">It is a detailed flowchart of the transmission step according to one Example of this invention.</figref><figref num="9">It is a detailed flowchart of the reception step according to one Embodiment of this invention.</figref><figref num="10">It is explanatory drawing of the storage data arranged in the channel data array by one Example of this invention.</figref><figref num="11A">FIG. 5 is an explanatory diagram of an echolocation data array according to an embodiment of the present invention having a first axis indicating the X position and a second axis indicating the Y position.</figref><figref num="11B">It is explanatory drawing of another Example of the echolocation data array by one Example of this invention which has the 1st axis which shows an angle (θ) and the 2nd axis which shows a radius (R).</figref><figref num="12A">It is explanatory drawing for exemplification of the Cartesian coordinate system by one Example of this invention which includes the data bin for 11 division of X.</figref><figref num="12B">It is explanatory drawing of the polar coordinate system which expresses the region irradiated with high frequency by the ultrasonic beam by one Example of this invention.</figref><figref num="13">(A) and (B) are explanatory views of ultrasonic waves propagating from a transducer element according to an embodiment of the present invention to an object in a substance under investigation.</figref><figref num="14">It is explanatory drawing of the channel data generated from the echo by one Example of this invention.</figref><figref num="15">FIG. 5 is an explanatory diagram of echolocation data generated using the data channel shown in FIG. 14 according to an embodiment of the present invention.</figref><figref num="16">It is a flowchart of the method included in the echo area calculation by one Example of this invention.</figref><figref num="17">It is a graph explaining three alternative apodization functions according to one Example of this invention.</figref><figref num="18">It is explanatory drawing of the ultrasonic wave transmitted from two transducer elements and collided with the ultrasonic wave reflecting object.</figref><figref num="19">It is explanatory drawing of the signal generated by the SCE transducer element stored in the channel data array by one Embodiment of this invention.</figref><figref num="20">It is a detailed flowchart of the echo area calculation step according to one Example of this invention.</figref>
New broad-beam<sup>TM</sup>) Technology is a system and method that can generate multidimensional (region 2D or volume 3D) echolocation data from as few single ultrasonic beams as possible. These techniques generate an ultrasonic beam, transmit the ultrasonic beam to the substance under investigation, generate an echo signal from the obtained echo, and generate echolocation data distributed in two or more dimensions. Process the echo signal.
Wide beam technology is not as complicated as prior art ultrasonic systems and methods. For example, wide systems and methods are not limited by the use of transmit lines, scan lines, or receive lines, and wide beam systems and methods can generate multidimensional echolocation data from just one transmit ultrasonic beam. .. Dependencies on transmit and receive lines are removed. This is because wide beam technology does not assume that the echo source is along a one-dimensional line such as the transmit beamline 250 and / or the receive line. Wide beam systems and methods do not require a large number of beam scans or scanning lines to generate 2D images. Also, unlike prior art, the resulting echolocation data can arise from a single transmitted ultrasonic beam distributed in two dimensions. When using wide beam systems and methods, the majority of received echo signals are used for image generation.
For embodiments of the prior art, wide beam systems and methods can determine the resolution of echolocation data independent of the shape or width of the transmitted ultrasonic beam. The reason for such independence is that the wide beam system does not assume that the transmitted ultrasonic beam is approximated by the transmitting line or the cylinder surrounding the transmitting line. Generally, the ultrasonic beam (wide beam) used in wide beam systems and methods is wider than the finely focused ultrasonic beam 170 used in the prior art.
The wide beam system and method differ from the prior art in the way data is manipulated. The wide beam system and method is based on a multidimensional inverse convolution algorithm that transforms the echo received by the receiving transducer into echolocation data, thus generating multidimensional echolocation data from a single transmitted ultrasound beam. .. For example, according to one embodiment, the inverse convolution algorithm (calculation) affects the conversion of 2D (time, ultrasonic transducer) raw data to 2D (X, Y position) echolocation data. .. Two-dimensional (time, ultrasonic transducer) raw data is optionally generated from a single transmit ultrasonic beam without assuming a transmit or receive line. Two-dimensional echolocation data is distributed in regions that require at least two spatial dimensions for representation. Data manipulations incorporated into wide beam systems and methods can use a single transmitting ultrasound beam to produce a two-dimensional image configured for display on a display device.
Wide beam systems and methods take advantage of increasing microprocessor capabilities and advances in integrated circuit technology. Current microprocessors have the ability to perform wide beam data analysis at a rate faster than the rate at which individual ultrasonic beams are transmitted and received using prior art beam forming techniques. Whereas prior art is limited by the pulse return time and the number of individual ultrasonic beams required to visualize the area, the wide beam embodiment presents the latest technology in progress in computing technology. use. Wide beam systems and methods achieve image generation rates that are not primarily limited by the use of finely focused ultrasonic beams, as in the prior art.
For example, in the case of a conventional system that visualizes images to a depth of 200 mm, 128 transmission / reception cycles take 33.3 milliseconds based on the speed of sound of 1.54 mm / microsecond. The frame rate obtained by this rate is about 30 frames / sec when the image resolution of the entire image area is 128 lines in the direction perpendicular to the axis of the basic array 105. In contrast, when using one embodiment of the invention to visualize the same depth, the same resolution is achieved using 5-7 send / receive cycles, for a total of only 1.3-1.8 ms. I don't need it. This time limits the final frame rate to 769 to 549 frames per second. In various embodiments, the 129-line image resolution image described above is acquired in 25, 17, 10.5, or less than 2 milliseconds.
Some embodiments of the wide beam technique produce images with minimal appearance of unwanted temporal anomalies associated with conventional scanning processes. The multidimensional echolocation data obtained from the wide beam ultrasonic beam represents the cross section of the material under investigation during the short pulse return time. Since this time is shorter than the time required to achieve two-dimensional (multiple beam) scanning in the prior art, the probability of relative motion between the transducer and the object under investigation during data acquisition is in the case of the prior art. Lower than.
Wide beam systems and methods do not rely on prior art approximations that ultrasonic beams can be represented by lines such as beamline 250. Therefore, the resolution of the resulting echolocation data is not a function of the distance from the focal point as in the prior art focal point 230A-E. Wide beams are typically wider and have the ability to image larger areas than each prior art focused beam.
Since each wide beam can visualize a wider area than the conventional ultrasonic beam, the number of ultrasonic beams required to visualize a specific area is smaller than that of the conventional technique. .. Since the number of ultrasonic beams required is very small, for example one, wide beam systems and methods use less power than prior art to visualize the material under investigation. As the power consumption decreases, the amount of energy given to the substance under investigation also decreases, and the amount of electricity required to generate each image also decreases. Relaxation of electrical requirements benefits devices that use built-in power sources such as batteries.
Examples of wide beam techniques include area forming for generating, receiving and analyzing ultrasonic beams.<sup>TM</sup>) The process is included. In this process, the set of echolocation data is distributed in a region that requires two spatial dimensions for representation and is generated using at most one ultrasonic beam. The receiving point where echo detection is performed and echolocation data is generated may be anywhere in the inspection area. The receiving points are optionally aligned along a variable grid where the particle size and regularity change with position. Another embodiment of the wide beam technique is volume forming.<sup>TM</sup>) The process is included. The volume formation process is similar to the area formation process, but requires three spatial dimensions to adequately represent the echolocation data generated using just one ultrasonic beam. It's different. Area formation and volume formation are optionally multidimensional forming<sup>TM</sup>) Combined with non-spatial dimensions such as time and velocity to accomplish the process.
FIG. 4 is a flowchart illustrating an outline of the wide beam method 400 according to an embodiment of the present invention. Method 400 begins with wide beam design step 410, which determines the number and shape of ultrasonic beams (wide beams) required to visualize a region or volume. Within this step, the desired properties of at least one determined wide beam are calculated and the parameters for the generation of this wide beam are set. Desirable properties of each wide beam include factors such as position, orientation, width, intensity, dispersion and the like. Parameters include voltage, aperture function, excitation delay, and so on.
In transmission step 420, the wide beam designed in step 410 is generated and transmitted to the substance under investigation. Transmission step 420 includes generating electronic waveforms using, for example, digital or analog waveform generators. This waveform is fed to a number of channels, each channel being independently delayed and amplified using a multi-channel delay generator and a multi-channel power device. Typically, the delay time is selected depending on the desired shape, width, and orientation of the wide beam. The amplified waveform excites the transducer element 110, which sends a wide beam to the material under investigation.
Reception step 430 uses the transducer element 110 to detect the echo produced by the wide beam transmitted. The transducer element 110 generates an electronic signal in response to the detected echo. The generated electronic signal (analog channel data) is optionally filtered using an analog filter to generate digital channel data, which is typically digitized using a multi-channel A / D converter. In one embodiment, the channel data preferably includes both amplitude and phase information. In data storage step 440, the channel data is stored in the channel data buffer. This channel data buffer is provided in a memory such as RAM, magnetic medium, optical medium, and the like.
Echo region calculation step 450 uses a multidimensional inverse convolution algorithm to manipulate the stored channel data. These algorithms are mathematical techniques that transform channel data into multidimensional echolocation data. Echo region calculation step 450 is capable of generating multidimensional echolocation data without the use of transmit, receive, or scan lines that characterize prior art.
Method 400 proceeds to echolocation data storage step 460, where the resulting echolocation data is stored using an echolocation data array that utilizes a preselected coordinate system. Echolocation data is typically provided in memory such as RAM, magnetic media, optical media, and the like.
At step 465, method 400 tests whether the data collection process has been completed (eg, whether the data needed to produce the desired image has been collected). If the data acquisition process is incomplete, this method returns to wide beam design step 410 and another wide beam is designed. At step 465, when the data collection process is complete, the image is generated in optional image generation step 470 and displayed on a display device such as a computer monitor in optional display step 480.
In another embodiment, wide beam design step 410 calculates the properties for some wide beams. In this embodiment, optionally, the process returns to step 410 between steps 465 and 420. This method may proceed directly from step 465 to transmission step 420. This is because the desired properties of the next wide beam are pre-calculated in the preceding scene of step 410.
FIG. 5 is a configuration diagram of a wide beam system 500 according to an embodiment of the present invention. A waveform generator 510, such as a programmable pulse sequence generator, is used to generate an electronic signal, such as an electronic pulse 210. This electron pulse will be used later to form a wide beam ultrasonic beam. The electronic signals are individually delayed on several signal channels by the delay device 515 using a set of delays configured to generate an ultrasonic beam with the characteristics designed in step 410 of FIG. To. The output of the delay device 515 is supplied to a power amplifier 520 such as a power transistor, operational amplifier, high speed FET, etc., where it is amplified and passes through the transmit / receive switch 525. The transmit / receive switch 525 optionally comprises a multiplexer 527 configured to connect an input channel containing a signal given by the delay device 515 to an output channel for transmission to the transducer array 530. The transducer array 530 is similar to the device array 105 of the prior art. The transducer array 530 includes an ultrasonic transducer element such as the ultrasonic transducer elements 110A-110H, and generates a wide beam by converting an electric signal received from the transmission / reception switch 525 into an ultrasonic pulse.
The transducer array 530 is configured to send a wide beam to the substance 535 under investigation. The transmission of the wide beam is done in step 420 of FIG. Echoes are generated within the material 535 under investigation by the interaction between the wide beam and ultrasonically reflecting objects such as tissue and bone. The transducer array 530 receives the generated echo and generates the corresponding electrical signal in step 430 of FIG. These electrical signals, which are typically analog signals, are voltage regulated operational amplifiers via a transmit / receive switch 525. It is supplied to the variable gain amplifier 540 such as a digital control type amplifier and a transistor coil for amplification.
After amplification, the signal passes through an optional analog filter 545 and is passed to the A / D converter 550, where the amplified signal is digitized. The analog filter 545 may be an analog filter known in the prior art such as a bandpass filter, a notch filter, etc., and the A / D converter 550 may typically be a commercially available analog-to-digital converter or the like. ..
The generated digital signal is stored in the channel data storage buffer 555 and manipulated by the signal processor 560 in step 440 (FIG. 4). The channel data storage buffer 555 is provided in a storage system known in the art. For example, the channel data storage buffer 555 is optionally provided in an electronic memory such as RAM, a magnetic memory or optical memory such as a disk drive, a compact disk, or the like. The operations performed by the signal processor 560 include the echo region calculation in step 450 of FIG. 4, and the time zone data stored in the channel data storage buffer 550 is stored in the echolocation data storage device 565 in step 460 of FIG. Convert to echolocation data such as raw or detected data to be processed. From the echolocation data storage device 565, the data is optionally transferred to the additional data storage device 570 or accessed by the image converter 575. The echolocation data storage device 565 and the additional data storage device 570 are any suitable storage devices such as electronic memory, magnetic medium, optical medium, and the like. The image converter 575 is similar to the image scan converter in the prior art, but is generated using a single ultrasonic beam rather than the data generated using a scan involving several ultrasonic beams. It works even more on the data. In step 470 of FIG. 4, the image converter 575 uses the data stored in the echolocation data storage device 565, the additional data storage device 570, or both storage devices to generate the detected data or image data. To do.
The image generation process is similar to image generation techniques that use echolocation data generated by prior art beam forming methods. For example, a particular one in echolocation data storage 565 is optionally mapped to a particular location on the display screen. The intensity and / or color at a location in the image indicates the intensity property or other properties detected in substance 535 under investigation. This image is optionally displayed on a display 580 such as an LCD screen, CRT screen, computer monitor, electronic display, etc. in step 480 of FIG.
The data used by the image converter 575 can be obtained from a series of ultrasonic beams or from a single ultrasonic beam. The data in the additional data storage device 570 is fed to another component of the wide beam system 500, such as the image converter 575, the communication electronics 585, and the user interface electronics 590. The components of the wide beam system 500 are controlled and coordinated by the control electronics 595 shown in FIG. 5 through connections not shown in FIG. The control electronics 595 is composed of a microprocessor, DSP, and optional computer code 596, which are configured to control the elements of the wide beam system 500 and perform the methods of the invention, such as the wide beam processing 400. including.
FIG. 6 is a flowchart illustrating wide beam design step 410 according to an embodiment of the present invention. In this embodiment, the calculations are performed using computer code 596 and include, for example, mathematical models of ultrasonic beam generation, propagation and echo generation. In some examples, look-up tables are used to speed up the computation. For example, if the user specifies a particular analysis depth, the desired intensity is optionally determined from the look-up table. Wide beam design step 410 begins with coverage determination step 610. In the coverage determination step 610, the region (or volume) in the substance 535 to be investigated and the time cycle in which the investigation should be performed are determined. Coverage determination step 610 responds to options selected by the user and requests for the current visualization (analysis) mode. For example, in the Doppler visualization mode, the user selects continuous monitoring and a wide beam represented by a continuous sequence of ultrasonic pulses. In another example, the user chooses to focus on an area within the substance 535 under investigation using a restricted field of view. The selection of a particular field of view is optionally used when calculating the width of the generated wide beam. For example, the width of the wide beam is chosen so that an integer number of wide beams fit the selected field of view with 10% overlap.
In addition, coverage determination step 610 determines the number of wide beams required to image a region (or volume) within the substance 535 under investigation. For example, according to one embodiment, coverage determination step 61 is configured to simulate coverage in a distant field, by using three wide beams that are separated from each other using block switching techniques. Includes calculations to determine the best visualized area. In another embodiment, this calculation determines whether the number of wide beams used when a region is best visualized is one, two, or more. When the user selects a mode of operation that includes several wide beams, repetitive visualizations, or continuous monitoring, coverage determination step 610 is optionally performed once for each wide beam.
The coverage determination step 610 is followed by the characteristic determination step 620, which specifies the characteristics of the wider beam determined in the coverage determination step 610. These properties include, by way of example, ultrasonic frequency, direction, scattering, pulse shape, phase relationship, aperture, intensity, interval, repetition rate, and / or other properties of the ultrasonic beam. Not limited to the example. The characteristics typically depend on the visualization mode of the analysis being performed, the required resolution, and the options selected by the user. For example, continuous monitoring mode requires a wide beam generated at a particular pulse rate, high resolution requires the use of multiple ultrasonic frequencies, and the user is best examined by a narrow beam with less scattering. Select an area survey. Further, in addition to the above characteristics, the characteristic determination step 620 selects a coordinate system used to represent the region covered by the wide beam and the origin of this coordinate system. Such a coordinate system is used to store echolocation data. The choice of coordinate system optionally responds to the shape of the wide beam. An example of a feasible coordinate system is shown in Figure 7.
The coverage determination step 610 and the characteristic determination step 620 optionally respond to the resolution requirement and the dynamic range requirement. For example, in one embodiment, these steps respond to user input specifying a zoomed image for a particular area. In other embodiments, these steps respond to user input that specifies a very high image resolution for some or all of the image. In another embodiment, coverage determination step 610 should generate a single ultrasonic beam, but there are several types of echoes generated by this single ultrasonic beam, for example to increase resolution. It is determined that the set of receiving transducers should be detected in a plurality of transmission / reception cycles.
Coverage determination step 610 and characteristic determination step 620 optionally respond to feedback generated in other steps of the invention. For example, in one embodiment, the echolocation data did not image the area of the covered area very well, and this poor visualization was due to the nearest transducer element 110 to the area that was not well visualized. It is shown that this is because there is a very highly reflective boundary between them. In response to this feedback, coverage determination step 610 and characteristic determination step 620 provide a guided wide beam that inspects the area from an alternative ultrasonic transducer that is not on the same line as the reflection boundary and the area to be inspected. Define.
Wide beam selection step 630 selects a wide beam for transmission. This wide beam is selected from the wide beams defined in the characteristic determination step 620. If some wide beams are characterized in characterization step 620, wide beam selection step 630 is optionally performed more than once before the next characterization step 620 appears. In such a case, wide beam selection step 630 is repeated after step 465 in FIG.
Wide beam design step 410 ends at excitation calculation step 640. Excitation calculation step 640 determines the appropriate physical parameters required to generate the wide beam selected in wide beam selection step 630. These physical parameters include, for example, the transducer element 110 to be excited, the electron pulse voltage, the pulse delay time, the set value of the multiplexer 527, and the like. For example, in one embodiment, a selected ultrasonic beam with a particular desired shape and direction uses a set of particular transducer elements 110 excited by a particular electronic waveform characterized by amplitude, frequency and phase. There is a need to. Each transducer 110 in the required set of transducer elements 110 is excited with an appropriate delay. Suitable physical parameters are determined, for example, using a mathematical model to calculate the voltage, waveform, and delay used to excite a particular number of transducer elements 110. In one embodiment, the voltage depends on the distance to the material 535 under investigation where the wide beam is expected to penetrate.
7A-7C show examples (710A-710C) of the wide beam 710 determined in the coverage determination step 610 and the characteristic determination step 620. FIG. 7A shows a wide beam 710A generated using an example of a linear transducer array 530. The region 715A of the radiofrequency-irradiated area is optionally represented by a pole (θ, R) coordinate system in which the origin 720 is placed on the surface of the transducer element 110. Points within the high frequency sound wave irradiation area 715 are identified by a distance (R) from the origin 720 and an angular coordinate value (θ) with respect to the transducer array 530 or an axis such as axis 730 or axis 735. In another embodiment, the focal point of the wide beam 701B is located on the opposite side of the transducer array 530, rather than on the front surface of the transducer element 110, as shown in FIG.
FIG. 7B is an explanatory view of a wide beam 710B generated using an example of a curvilinear transducer array 530. The harmonically irradiated area 715B is optionally represented by a polar coordinate system with the origin 755 on the opposite side of the transducer array 530. This origin position irradiates a wider area near the transducer element 110 with high frequency sound waves than when the origin is closer to the transducer array 530 as shown in FIG. 7A. The position of the origin 755 on the opposite side of the transducer array 530 is optionally independent of the shape of the transducer array 755. Examples of the present invention also include, but are not limited to, examples in which the origin 755 and / or focus is located on the opposite side of the linear transducer array 530.
FIG. 7C is an explanatory diagram of a wide beam 710C that produces a harmonic sound wave irradiation region 715C. The harmonic sound wave irradiation area 715C has a more square shape than the harmonic sound wave irradiation area generated by the wide beam 710A shown in FIG. 7A and the wide beam 710B shown in FIG. 7B. Since the harmonic wave irradiation region by the wide beam 710C has a rectangular shape, it is preferably represented by the orthogonal (x, y) coordinate system 780.
The maximum intensity of a wide beam, such as the wide beam 710B or 710C, appears at points other than the beam centerline, as opposed to the prior art in which the maximum intensity is detected at the center of the ultrasonic beam. FIG. 7D is a graph 790 plotting the intensity of ultrasonic waves through the cross section of the wide beam 710C, measured at a distance from the transducer array 530 by a distance that corresponds to approximately half the width of the beam aperture. This cross section is shown by dashed line 785 in FIG. 7C. In certain situations, the intensity profile of the wide beam represents a more desirable energy distribution than that found in the prior art. For example, the energy distribution shown by Graph 790 is more evenly distributed on the harmonic wave irradiation region 715C than the energy distribution in the focal side ultrasonic beam according to the prior art.
FIG. 8 is a detailed explanatory view of an embodiment of the transmission step 420 of FIG. In the case of this embodiment, step 420 includes waveform generation step 810, which is used by the waveform generator 510 to generate an electrical waveform with the characteristics calculated in wide beam design step 410. The generated waveform optionally includes multiple pulses with varying frequencies or phases. In signal delay step 820, the generated waveform is reproduced on several signal channels and delayed by the delay device 515 for the time determined in wide beam design step 410. The waveform of each signal channel is amplified in amplification step 830 using a power amplifier 520. The amplified waveform is fed to the multiplexer 527 in multiplexing step 840. The multiplexer 527 guides the waveform in each signal channel to one or more members of the transducer element 110 in the transducer array 530. In sound wave generation step 850, the guided waveform causes the transducer array 530 to generate a wide beam 710. This wide beam is directed at material 535 under investigation. The sound wave generation step 850 ends the transmission step 420.
FIG. 9 is a detailed explanatory view of an embodiment of reception step 430 of FIG. 4, in which echo is detected and converted into digital data. In switch set step 910, the transmit / receive (transmit / receive) switch 525 is set so that the signal generated by the transducer element 110 is supplied to the variable gain amplifier 540 via the multiplexer 527. In echo detection step 920, echoes from the substance 535 under investigation are detected by members of the transducer element 110 within the transducer array 530. The member of the transducer element 110 used to detect the echo may optionally be a different member than the member of the transducer element 110 used to transmit the wide beam 710. In various embodiments, these two sets of transducer elements 110 are constructed in a number of ways. For example, the two sets are identical, interleaved, partially overlapped along the transducer array 530, or do not overlap along the transducer array 530. Since the transmission / reception switch 525 is set in the switch set step 910, the electronic signal generated from the detected echo is supplied to the variable gain amplifier 540.
The electronic signal supplied to the variable gain amplifier 540 is amplified in the variable amplification step 930. The variable amplification step 930 optionally includes feedback based on the data obtained using the previous wide beam 710. Feedback is used to provide adaptive processing and adjust the signals within each channel to maximize the dynamic range of subsequent data manipulation steps. For example, in one embodiment, if a particular channel is saturated by the execution of the previous variable amplification step 930, the amplification of that channel is optionally reduced during the subsequent execution of the variable amplification step 930. To. Such degradation, or adaptive front-end gain, is compensated for by subsequent data manipulation after digitization of the amplified signal. In another embodiment, it can be seen that the transducer element 110 near the center of the transducer array 530 responds systematically to echo more strongly than the transducer element 110 near the edge of the transducer array 530. The variable amplification step 930 optionally compensates for this systematic difference.
In the optional analog filtering step 940, the electronic signal amplified in the variable amplification step 930 is processed using the analog filter 945. This process includes, for example, I / Q mixing, removal of unwanted frequencies, and shifting of the signal to a suitable frequency range by subsequent data manipulation.
In data conversion step 950, the electronic signal that is optionally filtered in analog filtering step 940 is digitized using the A / D converter 550. The generation of digital data is completed in reception step 430 of FIG. In various embodiments, the data conversion step 950 is performed at another time within the wide beam processing 400. After the completion of receive step 430, the obtained digital signal is stored in the channel data storage buffer 555 in data storage step 440 (FIG. 4).
FIG. 10 is an explanatory diagram of an embodiment of the channel data array 1000 configured to hold the digital data stored in the data storage step 440. The channel data array 1000 is housed in the channel data storage buffer 555. The first axis 1010 of the channel data array 1000 is indexed by the echo receiving member of the transducer array 530. The second axis 1020 of the channel data array 1000 is divided into time channels. The values stored at each location in the array indicate the intensity and phase of the echo signal detected by a particular member of the transducer array 530 at a particular time.
The channel data storage buffer 555 optionally includes several channel data arrays 1000. In addition, the information stored in the channel data array 1000 is used to average or sum the received signals. In various embodiments, the channel data array 1000 is configured to store multidimensional data. For example, according to one embodiment, the transducer array 530 is a two-dimensional array of transducer elements 110. In the case of this embodiment, the channel data array 100 includes two axes representing the two dimensions of the transducer array 530, one axis representing the time channel.
Echo region calculation step 450 uses the data stored in data storage step 440 to generate echolocation data indicating the location and intensity of the echo source within the substance 535 under investigation. The generation of this echolocation data involves converting the multidimensional time channel data into multidimensional position (echolocation) data within the channel data array 1000. For example, according to one embodiment, the two-dimensional time channel data is transformed into echolocation data represented by two-dimensional spatial coordinates. The data transformation of echo region calculation step 450 is performed using a number of alternative transformation algorithms described herein. These transformations are optionally used to generate two-dimensional echolocation data using the signal received as a result of a single wide beam 710. In one alternative embodiment, the echo region calculation step 450 is replaced by a similar echo volume calculation step that includes additional spatial dimensions. The echo volumetric calculation uses the signal received as a result of a single wide beam covering the 3D volume to generate 3D echolocation data.
11A and 11B are explanatory views of two embodiments of the echolocation data array 1100 stored in the echolocation data storage device 565 and configured to store the position data obtained from the echo region calculation step 450. .. These two examples utilize different coordinate systems. As detailed below, a more efficient coordinate system depends, in particular, on the shape of the individual ultrasonic beams 710. In most cases, a more efficient coordinate system overlays in close proximity to the area irradiated by the radiofrequency sound waves. For example, as shown in FIGS. 7A-7C, the regions irradiated with high frequency sound waves by the wide beam 710A, the wide beam 710B, and the wide beam 710C are represented by different coordinate systems having different origins, respectively. By using a more efficient coordinate system, sampling efficiency and spatial resolution are improved. The preferred coordinate system and selection of the echolocation data array 1100 is made depending on the shape of the ultrasonic beam, such as the wide beam 710, and optionally in steps 410, 440 or 450.
FIG. 11A illustrates an embodiment of an echolocation data blending 1100 using a Cartesian coordinate system that includes a first axis 1110 indicating the X coordinate (position) and a second axis 1120 indicating the Y coordinate (position). It is a figure. FIG. 11B is an explanatory diagram of another embodiment of the echolocation data array 1100 using a polar coordinate system including a first axis 1110 showing angular (θ) coordinates and a second axis 1120 showing radial coordinates. .. Another embodiment of the echolocation data array 1100 is represented by a different coordinate system. Additional data (not shown) is optionally used to associate axis 1100 and axis 21120 with the transducer array 530. For example, the echolocation data array 1100 is optionally represented by a vector that associates the origin of each coordinate system with a particular number of ultrasonic transducer elements 110.
Figures 12A and 12B illustrate situations where using one coordinate system is more efficient than using the other. 12A and 12B show examples of the echolocation data array 1100 shown in FIGS. 11A and 11B superimposed on the ultrasonic beam 1210, respectively. The ultrasonic beam 1210 is an embodiment of the wide beam 710. FIG. 12A represents a Cartesian coordinate system containing 11 X-division data bins (storage locations) 1220 for illustrative purposes. Data bin 1220 is suitable for covering distant fields 1230. The spacing of the data bins 1220 in the X dimension is the same as the spacing of the data bins in the neighborhood field 1240, and many data bins 1220 in the neighborhood field 1240 are mapped to areas not inspected by the ultrasonic beam 1219. Data bin 1220, which is not mapped to the inspection area, represents an inefficient sampling of substance 535 under investigation.
On the other hand, FIG. 12B shows an example of using a polar coordinate system to represent a region irradiated with harmonic waves by the ultrasonic beam 1210. For polar coordinate systems, the size of data bin 1250 varies as a function of R coordinates. The data points of this example of the echolocation data array 1100 are therefore more efficiently mapped to the area inspected by the ultrasonic beam 1210 than in the case of the example of the echolocation data array 1100 shown in FIG. 12A. To. Data bin 1250 size changes increase efficiently. This is because as many data bins 1250 as possible within the data array 1100 fit within the area covered by the ultrasonic beam 1210, as shown in FIG. 12B.
The particle size of the data bin is dynamic. In some embodiments, the echolocation data array 1100 represents a Nyquist sampling space. The density of bin 1250 is varied so that a certain number of specimens meet the Nyquist criteria for non-pseudo sampling throughout the area of interest. In some embodiments, the density of bin 1250 varies so that the resolution of the resulting echolocation increases in certain areas. For example, in one embodiment, the user specifies a particular area where a more detailed image is desired. Correspondingly, wide beam systems and methods use bin 1250 densified echolocation data arrays 1100 within this area.
Some embodiments of the invention perform extrapolation and interpolation between data bins 1250. For example, according to one embodiment, interpolation is used in a distant field, and each data bin 1250 represents a larger area to increase the density of echolocation data. Optionally, the data bin 1250 is denser if interpolation is rarely used in the neighborhood field.
The resolution (sampling frequency) of the channel data generated in receive step 430 basically limits the resolution of the echolocation obtained as a result of Nyquist theory. However, the resolution of the data generated in receive step 430 is optionally improved by signal averaging or upsampling techniques. Upsampling techniques include the use of additional data and, optionally, feedback so that the additional data is collected in areas where resolution improvements are highly demanded.
13 to 15 are used to show an example of echo region calculation step 450 (FIG. 4). FIG. 13 is an explanatory diagram of ultrasonic wave propagation between the transducer elements 110A-110S and the ultrasonic reflecting object inside the substance 535 under investigation. FIG. 14 shows the channel data generated from the detected echoes. FIG. 15 shows the echolocation data generated using the channel data shown in FIG.
In some embodiments of echo region calculation step 450, a data conversion method is included, and the main factor to the echo detected from each location within the substance 535 under investigation is the transducer element closest to that location. Assumed to be a member of 110. This element is called a main contributor element (MCE). Typically, the member of the transducer element 110 closest to a location is the MCE for that particular location and the ultrasonic reflecting object at that location. However, the uniqueness of MCE depends on the direction of the wide beam 710 and the shape of the transducer array 530. In such cases, the MCE is not the transducer element 110 closest to the particular location. The data conversion method of echo region calculation step 450 in FIG. 4 optionally refers to the direction of the wide beam 710, the geometry of the transducer array 530, the feedback, and the closest member of the transducer element 110 to the ultrasonic reflecting object. Includes other factors to determine which MCE is not.
FIG. 13A shows the ultrasonic wave 1305 transmitted from a single transducer element 110. The ultrasonic wave 1305 travels through the substance 535 (not shown) under investigation and collides with the ultrasonic reflecting object 1310A. The transducer element 110G is the transducer element closest to the ultrasonic reflecting object 1310A in the transducer elements 110A-110S and is therefore considered to be the MCE for the reflecting object 1310A. At the ultrasonic reflecting object 1310A, the ultrasonic 1305 generates an ultrasonic echo 1315. The ultrasonic echoes 1315A-1315F in it are shown. The ultrasonic echo 1315 propagates back to the transducer elements 110A-110S and is detected there.
FIG. 13A shows an ultrasonic wave 1305 transmitted from one transducer element 110G (MCE), but in most embodiments the ultrasonic waves are multiple transducer elements 110A during the formation of the wide beam 710. -Sent from 110S. FIG. 13B is a diagram showing ultrasonic waves 1330 generated by a single transducer element 110Q, which is an MCE for an ultrasonic reflecting object 1310B. Echo 1340, of which ultrasonic echo 1340A-1340F is illustrated, is generated by the reflective object 1310B, backpropagates, and is detected by the transducer elements 110A-110S.
FIG. 14 is an explanatory diagram of an embodiment of a channel data array 1000 containing data generated by ultrasonic waves 1305 and 1330 shown in FIG. Each column 1410A-1410S of the channel data array 1000 represents the signal detected by the corresponding transducer elements 110A-110S. Each row 1420A-1420U of the channel data array 1000 contains signals detected in a particular time period. In FIG. 14, the data element 1430 containing the data generated by the detection of echoes 1315 and 1340 is the data element 1430 that intersects the data location line 1440A or the data location line 1440B, respectively. Thus, the ultrasonic echo generated from a reflective object such as the ultrasonic reflecting object 1310 within the substance 535 under investigation produces data that resides along a line such as the data location line 1440A or 1440B. Data location lines 1440A and 1440B can be calculated from the physics and geometry principles that use the known geometry of Transducer 530 and the speed of sound within the material 535 under investigation. Data location lines 1440A and 1440B do not intersect the MCE, transducer element 110G, or typically other transducer elements 110. In practice, the substance 535 under investigation contains a large number of ultrasonic reflecting objects 1310, and the channel data array 1000 contains the data generated by each ultrasonic reflecting object.
According to the embodiment of echo region calculation step 450, echo location data is calculated by summing the data along lines such as data location line 1440A, data location line 1440B, and so on. For example, summing the data in the direction of data location line 1440B yields the amplitude of echo 1315 generated at the position occupied by the ultrasonic reflecting object 1310B and represented by a data bin such as data bin 1220 or data bin 1240. You will get the results you want. This total is stored in a typical data bin. Similar sums are optionally performed for each data bin in the echolocation data array 1100. By summing up multiple times, the echolocation data array 1100 is occupied by echolocation data representing the ultrasonically reflecting object in the material 535 under investigation.
FIG. 15 shows an embodiment of the echolocation data array 1100 including the echolocation data bin 1520. Each echolocation data bin 1520 is associated with a unique line, such as the data location line 1440A in the channel data array 1000, as shown in FIG. The data along the unique lines are summed to calculate the magnitude of echo occurrences made at the physical location represented by each data bin 1520. This sum is optionally performed for all data bins 1520 and can be used to calculate echolocation data for the entire echolocation data array 1100.
FIG. 16 is an explanatory diagram of a data conversion method included in an embodiment of the echo region calculation step 450. This embodiment includes element selection step 1610 in which one echolocation data bin 1520 in the echolocation data array 1100 is selected. Typically, the selection of each echolocation data bin 1520 is achieved by systematically traversing the echolocation data array 1100. The element selection step 1610 is followed by a line determination step 1620 to determine the unique line of the channel data array 1100 associated with the selected echolocation data bin 1520. Judgment is performed by calculating lines from geometric principles, such as using a look-up table containing previously calculated lines. The determination is made before the echo region calculation step 450 or during the echo region calculation step 450. In various embodiments, the determination is made before or during the wide beam design step 410. In an alternative embodiment, the determination is made before or during steps 420, 430 and / or 440 of FIG. The line determination step 1620 is followed by the data summing step 1630, which sums the data from the data element 1430 that intersects the line determined in the line determination step 1620. In one embodiment, data summing step 1630 performs simple data addition. In an alternative embodiment, data summing step 1630 uses mathematical techniques such as weighted functions, matrix operations, extrapolation, and interpolation. In one embodiment, the total data step 1630 is readily implemented by the firmware in the control electronics 595. In the result saving step 1640, the total result in step 1630 is stored in the data element selected in the element selection step 1610.
Steps 1610 to 1640 may optionally be repeated for all echolocation data bins 1520 in the echolocation data array 1100. FIG. 15 shows two sets (1550 and 1560) of echolocation data bins 1520 containing non-zero values obtained by summing along data location lines 1440A and 1440B using the method shown in FIG. .. Each set of echolocation data bins 1520 (1550 and 1560) typically contains an echolocation data bin containing various non-zero values. In some embodiments, one or more steps from steps 1610 to 1640 are performed as parallel processing.
Other embodiments of echo region calculation step 450 include alternative data conversion methods. These alternative methods use, for example, calculations performed in the frequency domain, use the phase relationship between received signals, and use an apodization function to weight the contribution of each transducer element 110. The feedback mechanism is used, and the correlation analysis of the transducer element 110 for transmission other than MCE is used and considered. These non-MCE transducer elements 110 are used to improve both the quality and speed of the conversion of channel data to echolocation data.
In one embodiment, the echo region calculation step 450 utilizes an apodization function to weight the contribution of each transducer element 110. Transducer elements 110 near the MCE receive stronger echoes from the particular reflective object 1310 than transducer elements 110 farther from the MCE and should be weighted.
FIG. 17 is an explanatory diagram of three different apodization functions according to the embodiment of the present invention. Graph 1710 shows three different apodization functions 1720, 1730 and 1740. For example, if the transducer element 110G is an MCE for one of the data elements 1430 selected in element selection step 1610 of FIG. 16, the apodization function 1720 results in a total close to the transducer element 110G. Used in data summing step 1630 to receive greater contribution from a transducer element 110. Similarly, for the sum when the transducer elements 110K and 110S are MCEs, the apodization function represented by lines 1730 and 1740 is optionally used.
In another embodiment, the echo region calculation step 450 is performed, at least in part, in the frequency range. The data is transformed using a reversible transform, such as a sine transform, a Fourier transform, a wavelet transform, and the like.
In some embodiments of echo region calculation step 450, the phase relationship between the received signals is the received signal obtained from the ultrasonic waves transmitted by the MCE and the received signal obtained from the secondary contributor (SCE). Is used to distinguish between. The SCE is a transducer element 110 other than the MCE, which contributes to a signal generated from a predetermined ultrasonic reflecting object such as the ultrasonic reflecting object 1310.
FIG. 18 is a diagram showing ultrasonic waves 1810 and 1305 transmitted from the transducer elements 110F and 110G and colliding with the ultrasonic reflecting object 1310A. Since the transducer element 110G is the closest member of the transducer element 110, it is considered to be an MCE for the ultrasonic reflecting object 1310A. In another embodiment, a set of closely assembled transducers is treated integrally as an MCE. Other transducer elements 110, such as the transducer element 110F, also generate ultrasonic waves that reach the reflective object 1310A. In the case of this example, the transducer element 110F is SCE. The ultrasonic waves from these SCE transducer elements 110 travel a longer distance than the ultrasonic waves from the MCE transducer element 110 before reaching the ultrasonic reflecting object 1310A. Similar to the ultrasonic waves generated by the MCE, the ultrasonic waves from the SCE generate echoes when they collide with the ultrasonic reflecting object 1310A. Some of the echoes are detected by the transducer array 530.
FIG. 19 is an explanatory diagram of the location of the signal generated by the SCE transducer element 110F in the channel data array 1000. These signals rest on data location line 1910, which is similar to data location line 1440A. Data location line 1910 is slightly behind data location line 1440A in time. The time difference between the data location line 1440A and the data location line 1910 is the time required for ultrasonic waves to reach the ultrasonic reflecting object 1310A from the transducer element 110F and the time required for ultrasonic waves to reach the ultrasonic reflecting object 1310A from the transducer element 110G. It is due to the difference from the time required for. It is desirable to distinguish between the data obtained from SCE and the data obtained from MCE. The signal from the MCE is typically stronger than the signal coming from the SCE (where the ultrasound travels longer distances), but the signal from the SCE is further distinguished by the phase difference resulting from the difference in travel distance. By considering only the signals with a specific phase, the signals obtained from the SCE can be separated by filtering. For example, according to one embodiment, the SCE signal is stripped above 10 dB and in some embodiments above 38 dB.
In various embodiments, the signal coming from the SCE is used to improve the results obtained in echo region calculation step 450. For example, in some embodiments, the data coming from the SCE is added to the data coming from the MCE. Thus, as shown in FIG. 19, the data along the data location line 1910 is added to the data along the data location line 1440A. The data overlapping the data location line 1910 includes data generated by the ultrasonic waves generated by the SCE transducer element 110F and reflected from the reflective object 1310A. After phase adjustment and weighting, this data is added to the data overlapping the data location line 1440A to enhance the signal-to-noise ratio of the echolocation data indicating the presence of the reflective object 1310A. Typically, the SCE closest to the MCE is given a greater weight than the SCE far away. For example, in one embodiment, a Chi square weighted distribution centered on the MCE is used to determine the weights of the neighboring SCEs. In another embodiment, the weight distribution responds to a feedback algorithm that reduces the weight of the SCE where the signal in the channel data array 1000 overlaps the strong MCE signal.
In another embodiment, the signal produced by the SCE is subtracted from the signal produced by the MCE. For example, if a large MCE signal is detected along data location line 1440A as shown in FIG. 19, it is expected that a corresponding large SCE signal will be present along data location line 1910. Because the corresponding SCE signal is predictable and the approximation can be calculated as a function of the MCE signal, the calculated value is the data before the data value is used to calculate the value for the other echolocation data bin 1250. It is subtracted from the channel data value stored in element 1430. Considering the data generated from the SCE to improve the echo region calculation is optionally done as part of the total data step 1630 (Figure 16).
Some embodiments of echo region calculation step 450 use feedback. For example, according to one embodiment, the calculated echolocation data is processed by a "reverse" data transformation that uses a technique to generate a simulated echo signal (simulated channel data) based on the calculated echolocation data. Will be done. This inverse transformation produces the simulation channel data expected when the calculation of echolocation data is optimal. The inverse transformation is optionally performed using conventional ray tracing. The simulated channel data is compared with the actual echo data stored in the channel data array 1000. The similarity between these two datasets represents the quality of the calculations used to generate the echolocation data. For optional iterative processing, the calculation of echolocation data is repeated with parameters that change with this similarity. These parameters include various weighting factors, apodization functions or SCEs that are manipulated to optimize the similarity between the data in the channel data array 1000 and the simulated echo signal.
According to another embodiment, the feedback utilizes echolocation data to control wide beam design step 410. For example, in one embodiment, the direction of the ultrasonic beam designed in step 410 responds to the location of the reflective boundary within the material 535 under investigation. In another embodiment, the focal point, width, frequency, or number of beams designed in step 410 is sensitive to calculated echolocation data.
Some embodiments of echo region calculation step 450 perform data transformation utilizing correlation analysis. Correlation methods are well known in data analysis techniques and are useful for emphasizing the similarity between data and making comparisons between the data. Correlation is especially useful when comparing systematically different data, for example due to changes in phase. Cross-correlation analysis of two sets of datasets that differ by a certain degree in a certain coordinate direction identifies this constant difference and the similarity of the data after considering this difference. Autocorrelation analysis of the dataset demonstrates periodic or repetitive signals in the data.
FIG. 20 is an explanatory diagram of an embodiment of the echo region calculation step 450 in which the cross-correlation method is used to identify the components of the SCE data that correlate well with the MCE data. In cross-correlation calculation step 2010, data on a line such as line data location 1440A (Fig. 14) associated with MCE will appear on a line such as line data location 1910 (Fig. 14) associated with SCE. Cross-correlation with the data is required. Each of these datasets is optionally preprocessed using a function such as the apodization function 1720. Cross-correlation produces a correlation dataset that can be expressed as a function of phase difference vs. similarity between two datasets. In phase difference calculation step 2020, the expected phase difference between the MCE and SCE data is calculated based on the known geometric relationship between the MCE and SCE. In reference (lookup) step 2030, the calculated phase difference is used to reference the similarity value in the correlation data set generated by the cross-correlation at a particular phase difference within the correlation dataset. The similarity value corresponding to the phase difference calculated in the phase difference calculation step 2020 indicates how effective the SCE data can be in improving the signal-to-noise ratio of the MCE data. This is because the higher the similarity of the SCE data, the more likely it is to be added to the MCE data to strengthen each other. In determination step 2040, the similarity value is compared with a predetermined threshold. If the similarity value is greater than the threshold, the SCE data is added to the MCE data in data addition step 2050. If, in step 2040, the similarity value is found to be below a predetermined threshold, computer code 596 determines in determination step 2060 whether it is appropriate to perform further analysis of the particular SCE dataset. To do. For example, if the nearby SCE has not yet been inspected, or if the user requires a further improvement in the signal-to-noise ratio, then a further solution. Analysis is naturally performed. Otherwise, the analysis of this particular SCE dataset will end. If it is determined in step 2060 that further analysis is guaranteed, the SCE dataset is processed in the optional filter step 2070. The processing in step 2070 includes filtering, censoring, or similar means designed to highlight the components of the SCE dataset that show good correlation with the MCE dataset. For example, according to one embodiment, an alternative function, such as the apodization function 1740, is applied to the SCE dataset. The steps shown in Figure 20 are optionally applied to two or more sets of SCE datasets.
Echolocation data generated using the alternative embodiment of echo region calculation step 450 is optionally compared and this comparison is used to determine the integrity of the calculation or to provide feedback. .. For example, in one embodiment, the two iterations of echo region calculation step 450 include consideration of different SCEs. The accuracy of these calculations is checked by comparing the results at each iteration. The closer the results are, the more likely it is that the use of SCE will produce accurate results. In another example, the echolocation data calculated using the two examples of echo region calculation step 450 turns out to be significantly different. These differences are used as feedback influencing other steps in wide beam technology. For example, the non-reproducibility of echolocation data in a particular area optionally provides feedback to wide beam design step 410 so that the characteristics of the wide beam inspecting that area (intensity, frequency, direction, etc.) are changed. Used to give.
The data stored in the echolocation data array 1100 is optionally used in image generation step 470 (FIG. 4), which produces an image of substance 535 under investigation that can be displayed to the user. Image generation and display is achieved by using the image converter 575 and the display 580, respectively. Since 2D data can be generated from a single ultrasound beam using wide beam technology, 2D images can be generated from a single ultrasound beam. In various embodiments, this ability increases the image frame rate over conventional methods. This is because the image is not the return time of many (ie, more than 100) pulses in the prior art, but the return time of a single pulse, or optionally a small number (ie, less than 5, 10). Less than, less than 20, less than 40, or less than 64) pulses are generated within the time limited by the return time. The advantage of generating an image from a single ultrasonic pulse is that it can reduce jitter in the generated image. This is because, compared to the prior art, there is less time for relative motion to occur between the transducer array 530 and the substance 535 under investigation during the period of data collection. Generating an image from a single ultrasonic beam reduces the amount of ultrasonic energy directed at the substance 535 under investigation and reduces the amount of electrical power required to generate the image.
Changes and additions to these embodiments may be made without departing from the principles of the invention, as will be apparent to those skilled in the art from the description of the various embodiments of the methods and devices described above. For example, the transducer element 110 can be replaced by another ultrasonic generating element, and the transmit / receive switch 515 is placed by a separate transmit and receive switch.<u style="single">Replacement</u>It is possible. The number of the illustrated transducer elements 110 is not limited. Typical examples include a large number of transducer elements 110. Similarly, the resolution of the illustrated data array is the resolution chosen for illustrative purposes only. A typical example includes a data array with a large number of data bins.
Wide beam technology is applicable to systems configured to use both region formation and conventional beam formation. Some embodiments include means of switching between these two approaches. For example, region formation techniques are used to study regions, and conventional beam formation techniques are used to focus energy on a particular region of interest. In certain embodiments that include a two-dimensional transducer array, the region formation technique is used in conjunction with conventional beam formation techniques. For example, one set of transducer elements is used for region formation and the other set of transducer elements is used for conventional beam formation. In another example, region formation is used to collect data in one spatial dimension, and conventional beam formation is used to collect data in the other spatial dimension. The ultrasonic beam is configured for region formation in one dimension and for conventional beam formation in the other dimension. For these examples, two or more echolocation methods are performed simultaneously, and each echolocation method is optionally associated with a particular spatial dimension.
Wide beam technology is applicable to systems limited by the use of phased arrays because it scans the concentrated beam in a two-dimensional region or three-dimensional volume. These systems include acoustic systems such as sonar, as well as electromagnetic systems such as radar. Examples of wide beam technology are used with a two-dimensional transducer array. For these examples, the echo volume calculation replaces the echo region calculation, and the transformation in step 450 transforms the three-dimensional (transducer, transducer, time) array of echo data into three-dimensional (x, y, z) echolocation data. Convert to an array. According to one embodiment, one 3D ultrasonic beam is used to perform volume formation, thereby producing echolocation data covering the volume in space.
The following aspects are conceivable in connection with the present application. [Aspect 1] A method of inspecting a substance to be inspected, in which a procedure using multiple transducers to transmit an ultrasonic beam containing components generated by each transducer to the substance to be inspected and between the ultrasonic beam and the substance to be inspected. When the procedure for receiving the echo generated by the interaction of the first data takes a value including phase information and amplitude information, is associated with the time dimension, and represents the data distributed on at least one spatial dimension. In order to distinguish between the procedure for generating this first data from the received echo and the echo generated from the ultrasonic beam component generated by the subset of the transducers among the received echoes, the phase A procedure that uses information and / or amplitude information and a second that uses distinct echoes to take the first data distributed over a spatial dimension that is at least one dimension larger than the first data. A procedure for converting data and a method having. [Aspect 2] The method of aspect 1, wherein the amplitude information is used to distinguish between echoes received. [Aspect 3] The method according to aspect 1, wherein the echo is used to distinguish between echoes received by both amplitude and phase information. [Aspect 4] The method of aspect 1, wherein the phase information is used to distinguish between echoes received. [Aspect 5] The method of aspect 4, wherein the ultrasonic beam is set to inspect a target area that includes a spatial dimension of two or more dimensions. [Aspect 6] Aspect 5 which further includes a procedure of transmitting an additional ultrasonic beam to a substance to be inspected, wherein the additional ultrasonic beam is set to inspect a second target area overlapping a target area including two or more spatial dimensions. The method described. [Aspect 7] Between the procedure of transmitting an additional ultrasonic beam set to inspect the second target area that overlaps the target area including the spatial dimension of two or more dimensions to the test target substance and the additional ultrasonic beam and the test target substance. Using both the second and third data, the procedure for receiving the second echo generated by the interaction of, the procedure for generating the third data using the received second echo, and the procedure for generating the third data. The method according to aspect 5, further comprising a procedure for generating an image. [Aspect 8] The method according to Aspect 4, further comprising a procedure for setting an ultrasonic beam in response to an imaging mode. [Aspect 9] Generated using a procedure of generating an electronic signal from a received echo using a receiving transducer and a weighting function having a coefficient according to the uniqueness of a member of a set of receiving transducers. The method according to aspect 4, further comprising a procedure for amplifying an electronic signal. [Aspect 10] The method of aspect 9, wherein the weighting function responds to the uniqueness of the major contributor. [Aspect 11] The method according to Aspect 1, wherein the procedure for converting the first data is multidimensional data conversion. [Aspect 12] A method of inspecting a substance to be inspected, that is, a procedure of transmitting an ultrasonic beam to the substance to be inspected, a procedure of receiving an echo generated by an interaction between the ultrasonic beam and the substance to be inspected, and a received echo. Select from the procedure for generating first data, including phase and amplitude information, which takes values associated with the time dimension and at least the first spatial dimension, and a portion of the first data to be converted. To use phase and / or amplitude information to generate a portion of the first data, using a transformation that can generate second data distributed in at least the second and third spatial dimensions. A procedure to convert to 2 data, and a method to have. [Aspect 13] The method of aspect 12, wherein the echo is used to distinguish between echoes received by both amplitude and phase information. [Aspect 14] The method of aspect 12, wherein the phase information is used to distinguish between echoes received. [Aspect 15] The method according to aspect 14, wherein the first spatial dimension is the same dimension as the second spatial dimension. [Aspect 16] The method according to Aspect 14, further comprising a procedure for determining the characteristics of an ultrasonic beam set to analyze a region under examination. [Aspect 17] The method according to aspect 12, further comprising a procedure for determining a region to be inspected by an ultrasonic beam, the second data being distributed in that region. [Aspect 18] The method of aspect 12, wherein the conversion procedure comprises the procedure of determining a data location line using the location of a major contributor. [Aspect 19] The method of aspect 18, wherein the data location line is curved. [Aspect 20] The method of aspect 18, wherein the data location line does not intersect the major contributor elements. [Aspect 21] The method of aspect 12, wherein the procedure for converting the first data comprises a conversion using correlation analysis. [Aspect 22] The method of aspect 12, wherein the procedure for converting the first data comprises determining a major contributor. [Aspect 23] The method of aspect 12, wherein the procedure for converting the first data includes consideration of secondary contributors. [Aspect 24] The method according to aspect 12, wherein the procedure for transmitting the additional ultrasonic beam is further provided, and the procedure for converting the first data is performed before the procedure for transmitting the additional ultrasonic beam. [Aspect 25] A method for inspecting a substance to be inspected, in a procedure of transmitting one or more ultrasonic beams to the substance to be inspected and a point of distribution on at least the first spatial dimension and the second spatial dimension. The procedure for receiving the first echo generated by the interaction between one ultrasonic beam in one or more transmitted ultrasonic beams and the object to be inspected, and the received first. The procedure for generating the first data from the echo of 1, which takes a value distributed in the time dimension and additionally distributed in at least the first spatial dimension or the second spatial dimension, and the first data at least the first. Use a procedure to convert to a second data that takes values distributed in both one spatial dimension and a second spatial dimension, a procedure to send another ultrasonic beam to the object to be inspected, and another ultrasonic beam. A procedure for receiving the further echo generated in the process, a procedure for generating a third data having a specific dimension, which is echolocation data, and a third data using the received further echo. A method having a procedure for combining the third and second data so as to have the same dimensions as. [Aspect 26] The method of aspect 25, wherein the properties of another ultrasonic beam are modified depending on the algorithm for processing the second data. [Aspect 27] The procedure for combining the second data and the third data was obtained from the signal-to-noise ratio of the image generated using only one of the second data or the third data. 25. The method of aspect 25, which improves the signal-to-noise ratio of an image. [Aspect 28] The method of aspect 25, wherein the procedure of transmitting another ultrasonic beam responds to the second data. 29. The method of aspect 25, further comprising a procedure for setting one or more transmitted beams in response to the visualization mode. [Aspect 30] The method according to Aspect 25, further comprising a procedure for determining an area to be inspected using one or more ultrasonic beams. [Aspect 31] The method according to aspect 25, wherein the procedure for converting the first data uses data conversion by a weighting function according to the uniqueness of the main contributing element. [Aspect 32] The method of aspect 25, wherein the second data is indexed using a coordinate system corresponding to the shape of one or more ultrasonic beams. [Aspect 33] A method of inspecting a substance to be inspected, that is, a procedure of transmitting an ultrasonic beam to the substance to be inspected and a procedure of receiving an echo generated by an interaction between the transmitted ultrasonic beam and the substance to be inspected. The number of positions is at least 64, with the procedure of using the received echo to generate the first data, which can be associated with multiple positions in time and the first spatial dimension. Yes, the relevance to the number of positions is independent of the relevance to time, and the first data takes a value that can be associated with at least the first spatial dimension and the second spatial dimension. A method having additional steps to convert to data. [Aspect 34] The method according to aspect 33, wherein the number of positions is at least 128. [Aspect 35] The method according to aspect 33, wherein the number of positions is at least 256. [Aspect 36] 33. The method of aspect 33, further comprising a procedure for receiving a second echo generated by the interaction between the second ultrasonic beam and the substance under test. [Aspect 37] Further having a procedure for generating a third data using the received second echo, the combination of the first data and the third data has the same dimensions as the first data. The method according to aspect 36. [Aspect 38] The method according to aspect 33, wherein the second data is echolocation data. [Aspect 39] A method of inspecting a substance to be inspected, in which a procedure using a plurality of ultrasonic transducers to transmit an ultrasonic beam to the substance to be inspected and an interaction between the ultrasonic beam and the substance to be inspected. The procedure for receiving the echo generated by and the first data from the received echo that takes multiple values that can be associated with time and two or more first number of positions in the first spatial dimension. And a procedure for generating second data from the first data, which can be associated with a second number of positions in the second spatial dimension and the first spatial dimension. The number of positions 1 is less than the number of positions 2 and can be associated with one of the positions of the second number in the second data, but with the position of the first number. A method in which at least one value that cannot be associated occurs without the use of interpolation between the values of the first data. [Aspect 40] The method of aspect 39, wherein the number of spatial dimensions that can be associated with the second data is independent of the number of transmitted ultrasonic waves. [Aspect 41] The transmitted ultrasonic beam is represented by a direction, a focal point, and a beam width at the focal point, the beam width being measured along a straight line passing through the focal point, orthogonal to the direction of the beam, and a second. The method of aspect 39, wherein the data is echolocation data having a resolution in a spatial dimension smaller than the beam width that is orthogonal to the direction of the beam. [Aspect 42] The method of aspect 39, wherein the procedure for generating the second data uses a conversion algorithm that uses a weighting function that assigns weights to the echo according to the echo reception location. [Aspect 43] The procedure of using a plurality of transducers to transmit an ultrasonic beam uses a plurality of transducers, and the procedure of generating a second data uses the phase relationship of the received echo or receives. 39. The method of aspect 39, wherein a transformation algorithm is set up to distinguish signals obtained from different members of multiple transducers using the amplitude of the echo. [Aspect 44] A method of inspecting a substance to be inspected, wherein a procedure of using a plurality of transducers to transmit a plurality of ultrasonic beams to the substance to be inspected, and a first member among the plurality of ultrasonic beams. The procedure for receiving the first echo generated by the interaction with the substance under test and the first echo received can be associated with the time dimension and at least two or more in the first spatial dimension. Between the procedure for generating the first echo data, which can be associated separately with the position and takes values containing phase and amplitude information, and at least the second member of the multiple ultrasonic beams and the material to be inspected. From the procedure for receiving the second echo generated by the interaction of, and from the received second echo, it can be associated with the time dimension and separately with at least two or more positions in the second spatial dimension. Generate the first echolocation data using the procedure to generate the second echo data that takes a possible value, the first echo data, and the data transformation in response to the phase and / or amplitude information. A procedure, a procedure that uses the second echo data to generate the second echolocation data, and a first location to generate a third echolocation data that has the same dimensions as the first echolocation data. A method having a procedure for combining data and a second location data. [Aspect 45] The method of aspect 44, wherein the data conversion responds to phase and amplitude information. [Aspect 46] The method of aspect 44, wherein the data conversion responds to phase information. [Aspect 47] The method according to aspect 44, wherein the first spatial dimension is the same dimension as the second spatial dimension. [Aspect 48] The method of aspect 44, wherein the first echo is received using at least one of a plurality of transducers. [Aspect 49] The method according to Aspect 44, further comprising a procedure for displaying an image by trying a third echolocation data. [Aspect 50] The first echo location data has a time dimension and a position dimension, the position dimension can be associated with the location of the transducer element, and the first echo location data is two represented in a Cartesian coordinate system. The method of aspect 44, which has a spatial dimension. [Aspect 51] The first echo location data has a time dimension and a position dimension, the position dimension can be associated with the location of the transducer element, and the first echo location data is two spaces represented by a polar coordinate system. The method of aspect 44, which has dimensions. [Aspect 52] A method of generating echolocation data, comprising a procedure of generating first data by converting the echo into an echo signal, the first data being able to be associated with time and Takes a plurality of values that can be separately associated with a plurality of positions in at least one spatial dimension, the plurality of values including phase information and amplitude information, in the first data, as well as phase information and / or amplitude information. It further has a procedure to generate echolocation data using the corresponding data transformation, and the echolocation data is obtained from two or more members of multiple values that can be associated with different positions at multiple positions. A method that takes at least one value. [Aspect 53] The method of aspect 52, wherein at least one value is generated without the use of interpolation between members of a plurality of values. [Aspect 54] The method of aspect 52, wherein each of the plurality of data in the echolocation data is obtained from a member of a plurality of values that occupy different positions in at least one one-dimensional spatial dimension. [Aspect 55] The echo is received by a plurality of transducer elements, and the different positions of two or more members of the plurality of values are at least twice the shortest distance between any two members of the plurality of transducer elements. 52. The method of aspect 52, which is separated. [Aspect 56] The method of aspect 52, wherein the data conversion responds to phase information.
In addition, the following aspects are also conceivable. [Aspect 1] An ultrasonic system: The procedure for generating a single ultrasonic beam from the first multiple transducers, The procedure for receiving echoes generated from the second multiple transducers, and A procedure for generating a first piece of data, including phase and amplitude information, associated with a time dimension and distributed on at least one spatial dimension, from a received echo. The procedure for generating the second data by applying the transformation to the phase and amplitude information from the first data, and It has a procedure for generating an image from the second data. An ultrasound system configured to perform an ultrasound visualization method. [Aspect 2] A means for distinguishing an echo from among the echoes received using the amplitude information, Further provided with means for generating the second data based on the distinguished echoes. The ultrasonic system according to aspect 1. [Aspect 3] A means for distinguishing an echo from among echoes received by using both the amplitude information and the phase information, and Further provided with means for generating the second data based on the distinguished echoes. The ultrasonic system according to aspect 1. [Aspect 4] A means for distinguishing an echo from among echoes received using the phase information, Further provided with means for generating the second data based on the distinguished echoes. The ultrasonic system according to aspect 1. [Aspect 5] The ultrasonic system according to aspect 4, wherein the procedure for generating an ultrasonic beam comprises configuring the ultrasonic beam to inspect a first area of interest that includes a spatial dimension of two or more dimensions. [Aspect 6] The method is: Further including a procedure for generating an additional ultrasonic beam, the additional ultrasonic beam is configured to inspect a second target area that overlaps the first target area, including two or more spatial dimensions. The ultrasonic system according to aspect 5. [Aspect 7] The method is: The procedure for receiving the second echo generated by the additional ultrasonic beam and The procedure to generate the third data using the received second echo, It further comprises a procedure for generating an image using both the second data and the third data. The ultrasonic system according to aspect 6. [Aspect 8] Further having means for receiving a choice about the configuration of the ultrasonic beam based on the visualization mode. The ultrasonic system according to aspect 4. [Aspect 9] The method is: A means of generating an electronic signal from an echo received via a second plurality of transducers, The ultrasonic system according to aspect 4, further comprising means for amplifying the generated electronic signal based on the contribution of the generated electronic signal from one of the second plurality of receiving transducers. [Aspect 10] The ultrasonic system according to aspect 9, wherein the amplification comprises applying a weighting function to the generated electronic signal. [Aspect 11] The ultrasonic system according to aspect 1, wherein the procedure for generating the second data comprises applying a multidimensional data transformation to the first data. [Aspect 12] A method of operating an ultrasonic visualization system. The procedure for generating a single ultrasonic beam and The procedure for receiving echoes from a single generated ultrasonic beam, A procedure for generating first data, including phase and amplitude information, from a received echo based on the first spatial dimension and time. By applying a data transformation from a portion of the first data to the portion of the first data based on any of the phase information, the amplitude information and any combination thereof, at least the first. A method having a procedure for generating second data distributed in two spatial dimensions and a third spatial dimension. [Aspect 13] The method according to aspect 12, wherein the echo is used to distinguish between echoes received by both the amplitude information and the phase information. [Aspect 14] The method according to aspect 12, wherein the phase information is used to distinguish between echoes received. [Aspect 15] The method according to aspect 14, wherein the first spatial dimension is the same dimension as the second spatial dimension. [Aspect 16] The method according to aspect 14, further comprising a procedure for determining the characteristics of an ultrasonic beam configured to analyze a region in a substance to be inspected. [Aspect 17] The method according to aspect 12, further comprising a procedure for determining a region to be imaged using the ultrasonic beam, wherein the second data is distributed over the region. [Aspect 18] The method of aspect 12, wherein the procedure of applying the transformation to said portion of the first data includes a procedure of determining a data location line using the location of the contributor element of the received echo. [Aspect 19] The method of aspect 18, wherein the data location line is curved. [Aspect 20] The method of aspect 18, wherein the data location line does not intersect the major contributor elements. [Aspect 21] The method of aspect 12, wherein the procedure for transforming the first data comprises a transformation using correlation analysis. [Aspect 22] The procedure for generating the second data is received from the second plurality of transducers based on a comparison of any of the phase information, the amplitude information and any combination thereof. The ultrasonic system according to aspect 1, comprising identifying the element that contributes to the echo. [Aspect 23] The ultrasonic system according to aspect 22, wherein the procedure for identifying a contributing element comprises identifying a major transducer from the second transducer based on the comparison. [Aspect 24] The method according to aspect 12, further comprising a procedure for generating an additional ultrasonic beam after generating the second data. [Aspect 25] An operating method of the substance inspection system to be inspected: The procedure for generating a single ultrasonic beam and The procedure for receiving the first echo from the generated ultrasonic beam, A procedure for generating first data distributed in the time dimension and distributed in at least the first spatial dimension or the second spatial dimension of the substance to be inspected from the received first echo. By determining the data location trajectory from the first data, the first data is converted into second data including echolocation data distributed in at least the first spatial dimension and the second spatial dimension. Procedure and A procedure for determining whether the echolocation data from the second data is complete, and And the procedure to generate another single ultrasonic beam, The procedure for receiving further echoes generated by the other ultrasonic beam and A procedure that uses the further echoes received to generate a third piece of data that is echolocation data and has a particular dimension. A method comprising a procedure of combining the third data and the second data so as to have the same dimensions as the third data. [Aspect 26] The method according to aspect 25, wherein the characteristics of the other ultrasonic beam are modified according to an algorithm for processing the second data. [Aspect 27] The procedure of combining the second data and the third data is more than the signal-to-noise ratio of an image that can be generated using only one of the second data or the third data. 25. The method of aspect 25, wherein the signal-to-noise ratio of the resulting image is improved. [Aspect 28] The method of aspect 25, further comprising a procedure for receiving a choice about the configuration of the ultrasonic beam based on the imaging mode. 29. The method of aspect 25, further comprising a procedure for determining a region to be imaged by the ultrasonic beam. [Aspect 30] The method according to aspect 25, wherein the procedure for converting the first data includes using data conversion by a weighting function. [Aspect 31] The method according to aspect 25, wherein the second data is indexed using a coordinate system corresponding to the shape of the ultrasonic beam. [Aspect 32] A method of operating the substance inspection system to be inspected: The procedure for generating the first single ultrasonic beam, The procedure for receiving the first echo generated by the first single ultrasonic beam generated, and It has a procedure for using the first echo received to generate first data that can be associated with time and position in the first spatial dimension, with at least 64 positions. Yes, the association with position is independent of the association with time, A method further comprising a procedure for converting the first data into second data distributed on the first spatial dimension and a second spatial dimension. [Aspect 33] The method according to Aspect 32, wherein the number of the positions is at least 128. [Aspect 34] The method according to Aspect 32, wherein the number of the positions is at least 256. [Aspect 35] A procedure for generating a second ultrasonic beam and 32. The method of aspect 32, further comprising a procedure for receiving a second echo for the second ultrasonic beam. [Aspect 36] Further comprising a procedure for generating a third data using the received second echo. 35. The method of aspect 35, wherein the combination of the first data and the third data has the same dimensions as the first data. [Aspect 37] The method according to aspect 32, wherein the second data is echolocation data. [Aspect 38] A method of operating the substance inspection system to be inspected: Procedures using multiple ultrasonic transducers to generate a single ultrasonic beam to the material to be inspected, and The procedure for receiving the echo generated by the single ultrasonic beam and A procedure for generating first data from a received echo that takes multiple values that can be associated with time and two or more first number of positions in the first spatial dimension. It has a procedure for generating a second piece of data from the first piece of data that can be associated with a second spatial dimension and a second number of positions in the first spatial dimension, of the first position. The number is smaller than the number of the second position, and can be associated with one of the positions of the second number in the second data, but the position of the first number is A method in which at least one value that cannot be associated occurs without the use of interpolation between the values of the first data. [Aspect 39] The method of aspect 38, wherein the number of spatial dimensions that can be associated with the second data is independent of the number of ultrasonic beams generated. [Aspect 40] The generated ultrasonic beam is characterized by direction, focus, and beam width at the focal point, the beam width being measured along a straight line passing through the focal point, orthogonal to the direction of the beam. The method of aspect 38, wherein the data of aspect 2 is echolocation data having a resolution smaller than the beam width in a spatial dimension orthogonal to the direction of the beam. [Aspect 41] The method of aspect 38, wherein the procedure for generating the second data comprises using a conversion algorithm with a weighting function that assigns weights to the echo according to the echo reception location. [Aspect 42] The procedure of using a plurality of transducers to generate an ultrasonic beam includes using a plurality of transducers, and the procedure of generating a second data determines the phase relationship of the received echo. 38. The method of aspect 38, wherein a conversion algorithm is used that is configured to use or use the amplitude of the received echo to distinguish signals obtained from different transducers of the plurality of transducers . [Aspect 43] A method of operating the substance inspection system to be inspected: The procedure for generating a first single ultrasonic beam from a first set of transducers from multiple transducers, A procedure for generating a second ultrasonic beam that overlaps a part of the first ultrasonic beam from the second set of transducers from the plurality of ultrasonic beams, and The procedure for receiving the first echo generated by the first ultrasonic beam, and From the first echo received, the first echo can be associated with the time dimension, can be associated with at least two or more positions in the first spatial dimension separately, and takes a value containing phase and amplitude information. The procedure for generating data and The procedure for receiving the second echo generated by the second ultrasonic beam, and From the received second echo, the procedure for generating second echo data with a value that can be associated with the time dimension and can be associated with at least two or more positions in the second spatial dimension separately. A procedure for generating the first echolocation data using the first echo data and a data transformation that responds to the phase information and / or the amplitude information. The procedure for using the second echo data to generate the second echo location data, and A method comprising a procedure of combining the first echolocation data and the second echolocation data in order to generate a third echolocation data having the same dimensions as the first echolocation data. [Aspect 44] The method according to aspect 43, wherein the data conversion responds to phase information and amplitude information. [Aspect 45] The method according to aspect 43, wherein the data conversion responds to phase information. [Aspect 46] The method according to aspect 43, wherein the first spatial dimension is the same dimension as the second spatial dimension. [Aspect 47] The method of aspect 43, wherein the first echo is received using at least one of the plurality of transducers. [Aspect 48] The method according to aspect 43, further comprising a procedure for displaying an image using the third echolocation data. [Aspect 49] The first echo location data has a time dimension and a position dimension, the position dimension can be associated with the location of the transducer element, and the first echo location data is represented by a Cartesian coordinate system. The method of aspect 43, which has two spatial dimensions. [Aspect 50] The first echo location data has a time dimension and a position dimension, the position dimension can be associated with the location of the transducer element, and the first echo location data is expressed in a polar coordinate system 2 The method of aspect 43, which has multiple spatial dimensions. [Aspect 51] A method of generating echolocation data: It has a procedure to generate the first data by converting an echo from a single emitted ultrasonic beam into an electronic signal, the echoes being arranged in an array indexed in at least one spatial dimension. Received at multiple times by the transducer element, the first data can be associated with one of the plurality of times and separately with the position of a transducer element in the array. Has a plurality of values including the phase information and the amplitude information of the electronic signal. The method is: Echolocation data is generated by applying data transformation from the first data to the first data according to the phase information and / or amplitude information, and the echolocation data is associated with a transducer element from the array. A method that further has a procedure derived from two or more values that can be. [Aspect 52] The method according to aspect 51, wherein a plurality of values occupying different positions in at least one one-dimensional spatial dimension in the echolocation data are derived from the values from the first data, respectively. [Aspect 53] Aspect 51, wherein the positions of the two or more values from the first data are separated by at least twice the shortest distance of any two elements from the plurality of transducer elements. the method of. [Aspect 54] The method according to aspect 51, wherein the data conversion is based on phase information. [Aspect 55] An ultrasonic imaging method: A procedure for generating a first single ultrasonic beam through a first plurality of ultrasonic transducer elements, and The procedure for detecting the echo of the first single ultrasonic beam in the second plurality of ultrasonic transducer elements arranged in the array distributed in the spatial dimension, and the procedure for detecting the echo of the first single ultrasonic beam. A procedure for storing data from the detected echo for each time when the echo was detected and for each transducer element in which the echo was detected, and a procedure for storing the data from the detected echo. A procedure for generating echolocation data distributed at least in two dimensions of spatial dimension from the stored data by determining a data location locus from the first data, and It has a procedure for generating an ultrasonic image from the echolocation data. Method. [Aspect 56] A second method according to aspect 55, which overlaps a part of the first ultrasonic beam and is emitted via a plurality of second ultrasonic transducer elements to the substance to be inspected. A method that further comprises a procedure for generating an ultrasonic beam.
510 waveform generator 515 Delay device 520 power amplifier 525 Send / receive switch 527 multiplexer 530 Transducer Array 535 Substance under investigation 540 Variable Gain Amplifier 545 analog filter 550 A / D converter 555 channel data storage buffer 560 signal processor 565 Echo location data storage 570 Additional data storage device 575 image converter 580 display 585 Communication electronic equipment 590 user interface electronics 595 Control electronics 596 computer code
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Numbers
- Publication
- 2010142658
- Publication, DOCDB
- 2010142658
- Publication, EPODOC
- JP2010142658
- Application
- 19579
- Application, DOCDB
- 2010019579
- Application, EPODOC
- JP20100019579
Titles2
- Japanese
- 幅広ビーム映像化
- English
- Wide beam visualization
Classification
- IPC, 1
- A61B8 00