Source: https://patents.google.com/patent/DE60222476T2/en
Timestamp: 2020-07-10 01:14:13
Document Index: 786628162

Matched Legal Cases: ['art 504', 'art 506', 'art 504', 'art 506', 'art 512', 'art 512', 'art 906']

DE60222476T2 - ultrasound transducer - Google Patents
DE60222476T2
DE60222476T2 DE60222476T DE60222476T DE60222476T2 DE 60222476 T2 DE60222476 T2 DE 60222476T2 DE 60222476 T DE60222476 T DE 60222476T DE 60222476 T DE60222476 T DE 60222476T DE 60222476 T2 DE60222476 T2 DE 60222476T2
DE60222476T
DE60222476D1 (en
2001-06-27 Priority to US301282P priority
2001-07-31 Priority to US919232 priority
2002-06-26 Priority to PCT/IB2002/002674 priority patent/WO2003003045A2/en
2007-10-25 Publication of DE60222476D1 publication Critical patent/DE60222476D1/en
2008-06-05 Publication of DE60222476T2 publication Critical patent/DE60222476T2/en
230000001681 protective Effects 0.000 claims description 107
238000003384 imaging method Methods 0.000 claims description 66
210000001519 tissues Anatomy 0.000 claims description 18
The The present application relates generally to the acoustic Imaging. In particular, the application relates to ultrasound imaging systems and methods in which converters with two-dimensional transducer element arrays be used.
Ultrasound imaging systems are becoming an important diagnostic tool for many medical specialties become. An important advantage of an ultrasound imaging system exists in the real-time sample. For example, an ultrasound imaging system Produce images so quickly that a sonographer takes internal organs can scan or movement within a body, such as the Blood flow, can detect and interactive in real-time visual feedback receives. this makes possible the sonographer to examine structures of interest and to modify the investigation in real time, which makes it both a better diagnostic quality as well as a higher one Patient throughput reached.
Next take advantage of interactive visual feedback in real time However, the sonographers are still dealing with the problem of system resolution. at An ultrasound imaging system depends on the system resolution of the ability to focus of the system. The focus ability in turn depends on the effective aperture of a transducer element array in one of the Ultrasonic imaging system belonging Probe off. Currently, there are two types of transducer element array arrangements for real-time ultrasound imaging systems used.
A Arrangement comprises a single transducer element or an annular array from transducer elements. Ultrasound imaging systems using these Arrangement of transducer element arrays is based on the mechanical movement of the probe to sweep over a person of interest Region with an acoustic beam.
A second array of transducer element arrays comprises an array Transducer elements activated by electronic circuits which electronically induced time delays in the acoustic Generate output signals of the transducer elements. These time delays to lead measurable phase delays, which cause the acoustic generated by the transducer element array ray beam directed and / or focused.
The Connections between electronic circuits, the transmission pulses for the Create transducer element arrays, and the transducer element arrays, the receive the transmit pulses are referred to as beamformer channels. Electronically steering and / or focusing one through the transducer element array generated acoustic beam is achieved by transmitting pulses from beamformer channel to beamformer channel electronically delayed be an efficient protective cover of different thickness to accomplish.
by virtue of of limitations regarding: (a) the size and complexity of a Cable for connecting the ultrasonic probe to the processing system and (b) the number of available ones Beamformer channels at An inexpensive ultrasound system was the electronic focusing in a lateral direction (a direction parallel to the imaging plane) limited. The focusing in an elevation direction (one direction perpendicular to the imaging plane) was achieved by a mechanical Lens with fixed curvature on the face the probe was placed.
conventional Modifications in elevation focusing were performed by the probe aperture and / or the properties of the mechanical lens changed were. Although it is known that a change in frequency is a change focal length (higher frequencies produce one lower focus than lower frequencies), it is not considered beneficial to change the frequency to change the focal length, because higher Frequencies in tissue are attenuated faster than lower frequencies.
It is known, therefore, that for a change in the elevation focusing of a transducer element array, one should change the elevation aperture and / or the effective curvature of a lens associated with the transducer element array. When imaging a deep organ, for example, the lens would have a large For example, in the imaging of shallower organs, the lens would need to have a smaller aperture and a narrower curvature.
generally known can Transducer element arrays in an ultrasonic probe as a one-dimensional (1D) array, as a one-half-dimensional (1.5D) array or as a two-dimensional array (2D) array (the size of a typical 1D transducer element array is on the order of magnitude of 0.5 wavelengths in the lateral direction and on the order of 50 wavelengths in Elevation direction). For a 1D array, the transducer elements are generally in the lateral direction with a single row of Elements arranged in the elevation direction. conventional linear and convex transducers are generally considered to be 1D transducer element arrays.
In a 1.5D array, transducer elements are mounted in both the lateral and elevation directions, however, the electrical control and data connections are symmetrically connected about the elevation center such that an acoustic beam generated by a 1.5D array is only lateral can be steered. In a 2D array, transducer elements are arranged in both the lateral and elevational directions, with the electrical connections providing the transducer elements with control and excitation signals for transmission and reception in both directions. An acoustic beam generated by a 2D array can be steered and focused in two dimensions. An example of a 2D array ultrasound probe is in U.S. Patent No. 5,186,175 to find.
The Advantages of 2D array imaging are well known. To these advantages belong for example the ability for electronic steering in two (2) dimensions (i.e., both lateral as well as elevation), a better resolution due to an improved Elevation focusing and improved phase aberration correction through refined comparison of propagation velocities. Has the flexibility and improved resolution associated with 2D converters the need for an acoustic lens with suitable shape for eliminated mechanical focusing of the acoustic beam. However, the transducer elements must still protected become. Consequently, the end faces of the 2D converter with a configured in a relatively flat, acoustically transparent material layer.
In the document US-A-6,139,496 An ultrasound imaging system including a probe assembly including a user interface and a sensor head integrated into a compact housing will be described. An ultrasound image is observed through an "acoustic window" implemented in a user interface view, the sensor head comprising a transducer array that is substantially planar and an acoustic lens Converter arrays can provide a high-resolution acoustic imaging by the use of a two-dimensional array of transducer elements.
Sonographeure can Get pictures of a region within a body by taking a Ultrasonic transducer properly against the body hold. In order to obtain images with diagnostic value, must the sonographer may push the position of the probe, Manipulate rotation and / or tilting of the probe with respect to the patient.
A flat transducer face, as for example with 2D converters, image quality deteriorates because they are a worse contact with the body structures of a patient provides as a transducer with a curved surface. Especially causes a flat transducer surface interfering reflections and blocked Parts of the acoustic aperture. Another downside with one with flat face configured converter is that such Transducer have sharp edges that cause discomfort to the patient, or the transducers have an excessively wide Supporting surface, the rounder corners allowed.
at Converters with an overly wide bearing surface are configured, the contact between the transducer face and Patient obstructed, leaving a sonographeur greater pressure along the longitudinal axis exercise of the converter need to improve the contact between the transducer face and the patient. The increase in pressure exerted by the sonographer may be on the patient Discomfort and cause sonographers injuries due to repeated movements. An area where maintaining an adequate contact between the transducer face and the patient is particularly problematic is the intercostal Cardiac imaging and thoracic imaging. In general, the converter housing contains for this Applications a 2D array of transducer elements, due to the improved Elevation focusing for the expected better resolution selected has been.
There is therefore a need for an improved converter that can handle these and / or others overcomes parts of conventional converters.
The The invention provides an acoustic imaging system according to claim 1 and a method for acoustic imaging of a patient Claim 14. In a preferred embodiment, the system according to the invention comprises for acoustic imaging, a molded protective cover that so is configured to mate with the transducer body. The molded protective cover consists at least partially of a material that has acoustic properties comprising the ultrasonic energy flowing through the material in the body to be imaged according to a Distracting focus property. The molded protective cover offers Comfort for the patient as well as an enlarged acoustic Window and reduces the occurrence of injury to the sonographer due to repeated movements. The improved with such Transducer configured system focused on acoustic imaging the acoustic energy passing through the protective cover and compensated at the same time the focusing characteristic of the molded protective cover.
Other Systems, methods and features of the improved ultrasonic transducer become the expert in consideration of the following drawings and detailed description. It is intended, that all such additional Systems, methods and features included in this specification are, in the context of the improved ultrasonic transducer lie and by the accompanying claims protected become.
Of the improved ultrasonic transducer can be better by referring to the following drawings are understood. The components in the drawings are not necessarily to scale; rather lies the emphasis on the clear illustration of the principles of Converter. About that In addition, in the drawings, corresponding parts are in all views denoted by the same reference numerals.
1 shows a schematic representation of a conventional 1D converter, which emits acoustic energy in a representative body.
2 shows a schematic representation of the improved ultrasonic transducer in conjunction with an image processing system.
3 shows a schematic representation of the improved ultrasonic transducer 2 with details of the image processing system.
4 shows a schematic representation of the control of the transducer elements of the improved ultrasonic transducer 2 illustrated.
5A shows a partial sectional side view of an embodiment of the improved ultrasonic transducer 2 ,
5B shows a side view of another embodiment of the improved ultrasonic transducer 2 ,
6 Figure 4 shows a flow chart of the preferred functionality of the imaging system 2 ,
7A shows a plan view of an alternative embodiment of the present invention.
7B shows a schematic representation of the details of the protective cover 7A ,
8A shows a plan view of an alternative embodiment of the improved ultrasonic transducer.
8B shows a schematic representation of the details of the protective cover 8A ,
9 FIG. 12 is a schematic representation of the representative placement of the improved ultrasound transducer during a representative thoracic imaging procedure. FIG.
10 shows a schematic representation of an acoustic beam in the transmit and in the receive mode for imaging a target.
11 shows a schematic representation of several acoustic beams in the transmit and in the receive mode for imaging multiple targets.
12 Figure 12 is a schematic representation of the spatial relationship between the protective cover of the improved transducer 2 and the two-dimensional transducer element array.
conventional One-dimensional (1D) sector transducer used for ultrasound imaging are typically lenses that include that of the Focus on transducers emitted acoustic beams. Especially the mechanical configuration of such a lens is chosen so that an acoustic beam is focused by a transducer in the elevation direction. The focus in elevation Rich tion can also be done mechanically, for example by implementing a concave shape on the array of the transducer. The focusing in the lateral direction is typically carried out electronically.
For example, a conventional 1D sector transducer uses a lens that promotes focusing of the emitted acoustic energy within a body, eg, a human body. Often, the material of such a lens has an acoustic velocity which is less than that of the human body (about 1.5 mm / μs). The acoustic energy thus delivered, which is conducted into the body by the ultrasonic transducer through the acoustic lens, tends to converge or focus within the body. The focusing of the acoustic energy emitted by a conventional 1D transducer within a body is in 1 shown schematically.
In 1 are representative acoustic waves 12 . 14 . 16 . 18 and 20 represented by the converter 22 over a focusing lens 24 to be sent out. As shown, the acoustic waves tend at least partially due to the material of the lens 24 in addition, with increasing penetration into the body 30 to focus.
generally known acoustic energy propagates at different speeds and with different wavefront shapes depending on for example the acoustic velocity and the acoustic impedance of a material through which the acoustic energy propagates. The closer to Example the acoustic speed of a lens material the body lies, the closer the energy is emitted by the transducer at the angle of incidence into the body. The nearer the acoustic impedance of the lens material is that of the body, The more ultrasonic energy will also be from the transducer in the Body transfer.
As in 2 illustrated, comprises a preferred embodiment 200 of the imaging system, a transducer probe ("transducer") 202 , For example, the converter 202 a two-dimensional (2D) sector converter. The converter 202 is electric with an image processing system 204 coupled. The image processing system 204 provides the converter 202 different signals to the converter 202 to allow acoustic energy over a variety of in a 2D array around a transducer face 207 around arranged transducer elements emit. The emitted acoustic energy as well as reflected acoustic echoes can then provide a protective cover 206 traversed, which is made of an acoustically transparent material. The converter 202 converts the reflected acoustic echoes into electrical signals that are returned to the image processing system.
The protective cover 206 is by a projection 210 of the transducer body 208 in a position relative to the transducer body 208 held. In particular, the protective cover 206 adjusted so that they are at least partially within one by the projection 210 defined aperture (not shown) sits. However, various other configurations may be used.
In prior art transducers, the protective cover is 206 configured as an acoustically non-focusing lens. More specifically, the protective cover 206 formed of selected material and / or has a certain shape, which allows the propagation of acoustic energy in a body, such as a human body, without the acoustic energy is mechanically substantially focused. For example, embodiments of the ultrasonic transducer 200 According to the prior art, a protective cover 206 comprise, at least partially, an acoustically matched material is formed. Such an acoustically matching material preferably has an acoustic velocity and impedance that substantially correspond to the acoustic velocity and acoustic impedance of a typical body.
In alternative embodiments of the prior art, the non-focusing is achieved by the transducer face 207 is made flat or convexly curved and a uniform thickness in that part of the protective cover 206 is maintained, which lies in the acoustic path. For example, a material having an acoustic velocity within the range of about 1.4 mm / μs to about 1.6 mm / μs could be considered as an acoustically suitable material for medical diagnostic applications. An acoustically suitable material preferably also has an acoustic impedance in the range from about 1.3 MRayl to about 1.7 MRayl.
In some embodiments, the acoustically non-focussing protective cover 206 are formed, inter alia, from butadiene, styrene-butadiene and / or associated rubber and / or polymer classes. These materials typically attenuate the acoustic energy at about 3 dB / cm at 2 MHz and about 8 dB / cm at 5 MHz. As is known, conventional lens materials such as silicone attenuate the acoustic energy at about 9 dB / cm at 2 MHz and about 33 dB / cm at 5 MHz.
It should be noted that the ordinary person skilled in the art can choose a protective cover 206 from materials that may not be considered as acoustically appropriate materials per se. However, the creation of a combination of materials having acoustically matched properties together, eg, an acoustic velocity within the range of about 1.4 mm / μs to about 1.6 mm / μs and an acoustic impedance within the range of about 1.3 MRayl to about 1.7 MRayl, considered for the improved ultrasonic transducer.
By creating an acoustically non-focusing protective cover 206 can the imaging system 200 enable the transmission of acoustic energy into the body of a patient suitable for electronic focusing both in the lateral direction and in the elevation direction. In particular, the imaging system 200 provide acoustic beams suitable for comparatively sensitive electronic focusing. This could allow an improved zoom imaging function compared to other ultrasound imaging systems which use mechanically focusing lenses. It is also assumed that an imaging system that provides an acoustically non-focusing protective cover 206 which can provide acoustic beams that are very well suited for contrast imaging applications. As described in detail below, improved imaging systems can use various forms of protective covers 206 comprise, which are at least partially formed of acoustically matching material.
A disadvantage of the prior art is that the use of a non-focusing protective cover 206 may not be desired. A suitable acoustically matched material that meets other transducer requirements such as durability, chemical resistance and biocompatibility may not be available or requires excessive development effort. In addition, requirements for maintaining contact between the transducer dictate 202 and the patient may have some form of protective covering surface that results in significant focusing of the acoustic energy. The improved ultrasonic transducer 202 brings advances in the technique of ultrasound imaging by providing the focusing properties of the protective cover 206 be electronically compensated.
Now referring to 3 becomes a preferred embodiment of the image processing system 204 described in detail. It should be noted that 3 not necessarily each component of the preferred system, but instead emphasizes the components most relevant to the systems and methods described herein.
As in 3 illustrated, includes the image processing system 204 the improved converter 202 which is electrically connected to a S / E switch 302 of the image processing system 204 connected is. The S / E switch 302 brings the converter 202 either in a transmit or a receive mode. To the transmission of acoustic energy through the converter 202 during operation in transmit mode, includes the image processing system 204 a transmit beamformer 304 which sets the transmission frequency f 0 and magnitude of various transmission signals. The transmit beamformer 304 communicates with a transmit waveform modulator 306 which generates the different emitted signal lines. As in 3 shown, the transmit beamformer work 304 and the transmit waveform modulator 306 under the control of a central control unit 310 ,
To the receipt of acoustic energy through the converter 202 during operation in the receive mode, includes the image processing system 204 an A / D converter 312 that of the converter 202 converted analog signals into digital signals. A digital filter 314 , eg an RF filter, filters out signals outside a desired receive band from the received data. Next, a receive beamformer receives 316 the filtered digital signals representing the received ultrasonic echoes.
The receiving beam former 316 may be designed to provide a plurality of digital echo waveforms (corresponding to a plurality of transducer element groups from the 2D array of transducer elements) from the A / D converter 314 receives. The receiving beam former 316 may combine the multiple digitized echo waveforms into a single acoustic line. To accomplish this task, a plurality of parallel processing channels within the Empfangsstrahlformers 316 Delay the separate echo waveforms by different amounts of time and then add the delayed waveforms to create a composite digital acoustic line. Furthermore, the Empfangsstrahlformer 316 successively receive a series of data collections for separate acoustic lines and process the data in a pipeline processing technique.
An image processor 318 may include a suitable type of random access memory (RAM) and be configured to receive a series of composite digital acoustic lines from the receive beamformer 316 receives. The acoustic lines may be defined within a three-dimensional coordinate space. The image processor 318 can be configured to mathematically manipulate image information in the received and filtered digital acoustic lines. In addition, the image processor 318 be configured to accumulate acoustic data lines over time for signal manipulation. In this regard, the image processor 318 further comprising a scan converter to convert the data stored in the RAM and to generate pixels for display. Each raster converter can process the data in the RAM after a complete data frame (ie, a group of all acoustic lines in a single view or image to be displayed) has been accumulated by the RAM.
For example, if the received data has been stored in RAM using polar coordinates to define the relative position of the echo information, then the raster converter can convert the polar coordinate data into rectangular (orthogonal) data which can be raster scanned over a raster scannable processor. The ultrasound imaging system 204 After completion of the reception, echo recovery and image processing functions for forming a plurality of frames belonging to the plurality of ultrasonic image planes, the echo image data information may be supplied to a video processor 320 forward as in 3 shown.
The video processor 320 may be designed to receive the echo image data information and may be configured to raster scan the image information. The video processor 320 generates picture elements (ie pixels) which are applied to the display device 322 can be forwarded. In addition, the picture elements may be forwarded to a video storage device (not shown). Video storage devices may include a digital video disc (DVD) player / recorder, a compact disc (CD) player / recorder, a video cassette recorder (VCR), or other video information storage device. As is known in the art, these video storage devices allow viewing and / or image processing after data acquisition by a user / operator other than real time.
As in 3 illustrated, the display device 322 be configured to capture the picture elements (ie the pixel data) from the video processor 320 receives and drives a suitable screen display or other imaging device (eg, a printer / plotter) to display the ultrasound images.
There are many variants of the image processing system 204 out 3 with the improved ultrasonic transducer 202 operate. For example, the receive beamformer 316 be divided into two parts, in an analog part between the S / E switch 302 and the A / D converter 312 (not shown) and a digital part behind the digital filter 314 , as in 3 shown.
The following will be referred to 4 taken, which is a schematic view of a converter control system 400 represents. The converter control system 400 controls a two-dimensional transducer element array 402 , The two-dimensional transducer element array 402 comprises a plurality of ultrasonic transducer elements, examples of which are denoted by the reference numerals 408 . 412 and 414 are designated. The ultrasound converting elements 408 . 412 and 414 are arranged in rows and columns, examples of which are denoted by the reference numerals 404 respectively. 406 are designated. Such a configuration is sometimes referred to as a matrix array. However, other transducer element configurations are possible.
Although the presentation off 4 It should be noted that the principles of the invention can be applied to any two-dimensional ultrasonic transducer element array configuration, including configurations in which ultrasonic transducer elements are curved in one or both of the two dimensions. For example, two-dimensional transducer element arrays having cylindrical, spherical, annular or other curved surfaces are possible and may utilize beamforming that for the planar two-dimensional transducer element array 402 out 4 used beamforming is slightly modified.
Each of the elements 408 . 412 and 414 of the two-dimensional transducer element array 400 is individually controllable. In particular, each of the transducer elements 408 . 412 and 414 as a transmitting element and as a receiving element, and each receives individual control signals. The ultrasonic transducer element 408 is, for example, electrically via the connection 416 with a transmit / receive switch (S / E switch) 418 connected. The S / E switch 418 is by a signal (not shown) from the central control unit 310 controlled to the transducer element 408 to enable the function in a transmission mode and in a reception mode.
When the transducer element 408 is operated in a transmit mode receives the transducer element 408 about the connection 426 and via the control amplifier 422 about the connection 424 a transmit pulse from the transmit beamformer 304 , The control amplifier 422 is used to determine the characteristics of the transducer element 408 to define supplied transmit pulse, and over the connection 430 through the amplitude control unit 420 controlled. Although this has been omitted for simplicity, each element in the two-dimensional transducer element array includes 302 a similarly controlled variable gain amplifier.
When the transducer element 408 operated in a receive mode, the ultrasonic energy applied to the surface of the transducer element 408 hits, converted into an electrical signal. The electrical signal is transmitted through the connection 416 through the S / E switch 418 (now by the function of a control signal from the central control unit 310 with the connection 444 connected), so that the received signal to the control amplifier 446 is forwarded. The control amplifier 446 amplifies the received electrical signal and passes the signal over the connection 448 the delay element 484 to.
Similarly, the transducer element receives 412 a transmit pulse over the connection 436 and deliver via the connection 438 a receive signal to the control amplifier 442 , The control amplifier 442 delivers the received signal over the connection 458 to the delay element 482 , Similarly, the transducer element receives 414 a transmission signal over the connection 458 , through the switch 456 and the connection 454 while receiving signal over the connection 454 , by switch 456 and connection 462 to the control amplifier 464 is forwarded. The control amplifier 464 provides the amplified received signal over the connection 466 to the delay element 478 , Each element in the two-dimensional transducer element array 402 is controlled in this manner, thereby providing complete control of each element in the two-dimensional transducer element array 402 is possible.
The control amplifier 462 . 442 and 446 and the delay elements 478 . 482 and 484 are all in the receive beamformer 316 contain. Although the receiving beam shaper 316 is shown to include only three control amplifiers and three delay elements, it includes sufficient amplifiers and delay element circuits (and other processing circuits) for each of the transducer elements in the two-dimensional transducer element array 402 , Further, various multiplexing, partial beam shaping and other signal processing methods by the Empfangsstrahlformer 316 be executed. For ease of illustration, the receive beamformer includes 316 in 2 however, only three delay elements. Each of the amplifiers in the receive beamformer 316 is through an over the connection 480 from the central control unit 310 controlled signal supplied. The signal on the connection 480 determined by each of the control amplifiers 464 . 442 and 446 applied receive gain. The gain applied by each of the amplifiers may be different. Similarly, each delay element becomes 478 . 482 and 484 through one over the connection 474 from the central control unit 310 operated signal supplied. This control signal determines the amount of delay that each of the delay elements 478 . 482 and 484 applies to its respective received signal. In this way, the receiving aperture can be controlled with high accuracy because each transducer element in the two-dimensional transducer element array 402 a respective control amplifier 442 . 446 and 464 and control circuitry.
The output signal of the delay elements 478 . 482 and 484 is about the connections in question 486 . 488 and 492 a summing element 494 fed. The summing element 494 combines the output signals of the individual delay elements and carries a beamformed signal over the connection 496 additional processing elements, for example the image processor 318 (not illustrated). In alternative configurations, the control amplifiers may 464 . 442 and 446 behind the delay elements 478 . 482 respectively. 484 are located. Furthermore, the output signals of the delay elements 478 . 482 and 484 can be combined into subarrays, and variable gains can be applied to each subarray, either before the subarray signal has its respective delay before the summing element 494 goes through or after.
Importantly, the two-dimensional transducer element array 402 with individually controllable transducer elements 408 . 412 and 414 makes the emitted ultrasonic pulse pattern variable in two dimensions. In particular, the two-dimensional transducer element array 402 be controlled in relation to the position of each element within the array. Full control over the entire aperture is provided by the 2D transducer element array control system 400 the control of the radiation characteristic of the aperture with high accuracy.
The calculation of the delays for the transmit beamformer 304 and the receive beamformer 316 is with reference to 10 comprehensible, whereby it is desirable to focus the picture on a target 1002 to focus, for example, the structure within the body to be imaged 30 can be. In this case, the emitted acoustic energy from the two-dimensional transducer element array 402 to focus on the goal 1002 brought, and the Empfangsstrahlformer 316 Focuses the received acoustic energy to the receiving sensitivity at the target 1002 to maximize. To the on the goal 1002 Focused acoustic energy can be sent out to the central control unit 310 the transmit beamformer 304 for each element of the two-dimensional transducer element array 402 about the connection 468 Provide delay control signals and a synchronization signal as a time reference for the delays. The transmit beamformer 304 causes each element of the two-dimensional transducer element array 402 Transmission signals with a beam-forming delay T BF after the synchronization pulse, for example via connection 426 , Control amplifier 422 , Connection 424 , S / E switch 418 and connection 416 be supplied. The transmit beamforming delays T BF are generally for each element of the two-dimensional transducer element array 402 different and can be calculated as described below. The emitted acoustic energy travels in a time T p , given by
to the target, where v b is the acoustic propagation velocity in the body, the transducer element of the two-dimensional array is at the coordinates (x 0 , y 0 , z 0 ) and the target 1002 is located at the coordinates (x, y, z). The total time T from the synchronization pulse to the arrival of the transmitted acoustic energy at the target 1002 can be calculated as follows: T = T BF + T p , Eq. 2
To get the acoustic energy to the target 1002 In order to focus, the transmit beamforming delays T BF must be chosen such that the total delays T are the same for each element, causing the ultrasound energy of all transducer elements of the two-dimensional array to be simultaneously at the target 1002 arrives. Any group of transmit beamforming delays T BF satisfying the condition that all the total times T from the synchronization pulse to the arrival of the transmitted acoustic energy from the individual elements at the target 1002 are the same, is enough. From the above explanation, it can be seen that the differences in the transmit beamforming delays T BF are completely specified by the geometry to focus on the target 1002 to reach.
In the receive cycle, each element of the two-dimensional transducer element array receives 402 the acoustic energy reflected from the target after a propagation delay T p corresponding to the propagation delay for that element in transmission. To focus on the goal, the receive beamformer delays 316 the received signal from each element by a receive beamforming delay T BF corresponding to the transmission beamforming delay. As with transmit beamforming, any group of beamforming delays may be used, provided that the differences in beamforming delays between any two elements are correct.
As the time after the sync pulse increases, the two-diodes increase dimensional transducer element array 402 incoming acoustic signals due to the finite propagation velocity of the acoustic energy to reflections of targets in increasing depth. The receive beamforming delays T BF can be changed depending on the depth to provide a receive focus at different target depths. This is called dynamic receive focus.
The insertion of a protective cover 206 between the two-dimensional transducer element array 402 and the body to be imaged 30 modifies the propagation delays T p by one with the acoustic velocities of the protective cover 206 , the body to be imaged 30 and the thickness of the protective cover 206 related amount. In particular, the protective cover adds 206 add another guard coverage delay T c , approximated by the following expression:
where h is the thickness of the protective cover 206 and v c is the acoustic velocity within the protective cover 206 is. If the protective cover 206 is an acoustically matched material, v c is approximately equal to v b and the guard coverage delay T c is approximately zero and no changes are required for the beamforming delays T BF . If the thickness h of the protective cover 206 is the same for all elements, also the protective cover delay T c for all transducer elements is the same, irrespective of the speed v c . Since only the differences in beam-forming delays are important, it is easy to see that a protective cover 206 of uniform thickness, the required beam-forming delays T BF not changed.
However, when the thickness h is over the two-dimensional transducer element array 402 is not uniform and the velocity v c deviates from the velocity v b , the delay T c for each in 12 illustrated element be different. This results in distortion of the protective cover during the transmission cycle 206 exiting and during the reception cycle in the protective cover 206 incoming wavefronts and causes a loss of focus and blurring of the image. The in the transmit beamformer 304 and the receive beamformer 316 delays used may be modified from the nominal values obtained from the distance calculation, so that the uneven thickness of the protective cover 206 caused by delay fluctuations, thereby maintaining focus and image quality. In other words, the new beamformer delays are equal to the beamformer delays minus the guard coverage delays or T New = T BF - T c , Eq. 4
In the event that one of the resulting new beamformer delays is negative, a constant delay can be added to all beamformer channels to make all delays positive. For example, in 12 the two-dimensional transducer element array 402 through a protective cover 206 covered by uneven thickness, so that the thickness is above the representative element 1204 h is 1204 and the thickness is above the representative element 1206 equal to h 1206 . Then the total delay time is from the representative element 1204 to the reference plane 1202
and the total delay time from the representative element 1206 to the reference plane 1202 is
The procedure for calculating beamformer delays described above is sufficient to produce a good focus under the most prevalent operating conditions. The implicit procedure, however, is the approximation that is provided by the protective cover 206 generated variation in the delay across the aperture is the same for all steering angles and focal lengths.
This approximation may not be sufficiently accurate if the beam steering angle with respect to the transducer face is greater than about 45 degrees or if the active aperture of the transducer 202 is greater than the distance to the desired focus point, or if the protective cover 206 a has greater thickness than about three wavelengths of incident ultrasonic energy, or if the protective cover 206 Has areas where the radius of curvature is less than about three times the width of the area over which it occurs.
An example of this effect is in 11 shown. In this regard, acoustic energy wanders from element 1102 on a ray path 1103 to the goal 1120 and from element 1112 on a ray path 1113 and a broken beam path 1114 to the goal 1120 , Acoustic energy can also be from element 1102 on the beam path 1104 and the broken beam path 1105 to a second destination 1140 wander and by element 1112 on the beam path 1115 and the broken beam path 1116 to the second destination 1140 hike. Although the illustration is not to scale, it can be seen that the length of the transmission path through the protective cover 206 and through the body to be imaged 30 may be different for the two goals, and that these differences for the two transducer elements 1102 and 1112 can be different. As a result, the delays T c through the protective cover 206 not just a function of the element position, but also the target position. The skilled person will recognize that the representation in 11 for the sake of simple explanation. Individual transducer elements can not focus on their own. There may be a plurality of active transducer elements that are collectively under the control of the image processing system 204 be brought to focus an acoustic beam passing through the aperture.
Now again consider the two-dimensional matrix of controllable transducer elements 4 , In the 4 The arrangement shown enables the application of a fully sampled, controllable and arbitrary (without limitation specified) two-dimensional delay profile to the two-dimensional transducer element array 402 , The term "fully scanned" refers to each transducer element 404 . 412 and 414 is controlled individually. In preferred embodiments of such an arrangement, each individual transducer element of the two-dimensional transducer element array receives 402 a type of control signal from the central control unit 310 ,
The delay profile of the aperture of the two-dimensional transducer element array is any fully sampled controllable function of both dimensions of the aperture. The delay profile can thus be adjusted so that any form of protective cover 206 which makes it possible to change the shape of the protective cover 206 to specify that optimal contact with the body to be imaged 30 , desirable ergonomic textures or other attributes as described above can be achieved without degrading the image quality.
Now referring to the 5A and 5B will be some preferred embodiments of the converter 202 described in more detail. As in 5A illustrated, the transducer comprises 202 a body 208 and a shaped two-dimensional transducer element array 502 , As shown, the two-dimensional transducer element array 502 a plurality of transducer elements 408 . 412 (two have been designated by reference numerals for the sake of simplicity). The body 208 is preferably configured to receive one or more different components that facilitate the transmission and / or reception of acoustic energy via the two-dimensional transducer element array 502 needed. It should be noted that in the present illustration the projection 210 and the protective cover 206 were removed to the two-dimensional transducer element array 502 to show. As in the partial section side view 5A can be seen, the two-dimensional transducer element array 502 be cylindrically shaped. It should also be noted that a spherically shaped two-dimensional transducer element array 502 can be selected for applications where a converter 202 must remain in close contact with various surfaces of the human body, as may be required.
Furthermore, the body can 208 ergonomically designed so that it has the appropriate positioning of the transducer 202 facilitates an imaging procedure. The body comprises an intermediate part 504 suitably adapted to be held by an operator by hand. Besides, the body can 208 be covered with a material that not only protects the converter electronics, but also has properties that the converter 202 make it easy for the sonographer to grasp.
At the in 5A illustrated embodiment, the body contains 208 a protective cover mounting part 506 , preferably starting from an intermediate part 504 radially expanding to receive the protective cover (not shown). At the proximal end of the transducer 202 ie the end opposite part 506 , is a tapered or neck-shaped part 512 intended. part 512 defines an aperture for receiving the electrical cables 520 , The cables 520 are designed to handle the electrical communication between the converter 202 and the image processing system 204 (not shown) fold.
There can be different forms of protective covers 206 used to form the underlying shaped two-dimensional transducer element array 502 protect and shield. Preferred shapes co-operate closely with the underlying two-dimensional wandering element array 502 to provide adequate acoustic coupling. Various considerations, for example the desire to have a good patient contact between the protective cover 206 and favoring the patient to maintain image quality and patient comfort, as well as ease of use for the sonographer, may make special shapes even more attractive for certain ultrasound examinations. For example, the protective cover 206 in some embodiments, be physically configured such that proper alignment of the transducer 202 is facilitated on an acoustic window of a patient. In particular, such a protective cover comprises 206 preferably curved surfaces from the transducer 202 run outwards. This configuration tends to provide the proper positioning of the protective cover 206 with respect to an acoustic window, for example an acoustic window defined by adjacent ribs of the patient. In particular, curved surfaces typically conform to the ribs and tend to align the tissue contacting surface with the acoustic window. As described below, the tissue contact surface can be provided in various configurations.
As in 5B illustrated, the transducer comprises 202 a body 208 and a shaped two-dimensional transducer element array 552 , As shown, the two-dimensional array 552 a plurality of transducer elements 408 . 412 (two are designated by reference numerals for purposes of illustration). Here, as in the previous figure, the projection 210 and the protective cover 206 removed to the two-dimensional transducer element array 552 expose. As in the page view
5B shown, the two-dimensional transducer element array 552 be substantially spherical in shape. A spherically shaped two-dimensional transducer element array 552 Can be selected for applications where a converter 202 must remain in close contact with various surfaces of the human body as may be required. It should be noted that two-dimensional transducer element arrays 402 with annular or other curved surfaces (eg a saddle surface) are possible and can use a beam shaping, which compared to the beam shaping of the planar two-dimensional transducer element array 402 out 4 was slightly modified.
It will now be referred to 6 , which illustrates an improved method for ultrasound imaging with a two-dimensional transducer element array. In this regard, the method of ultrasound imaging begins 600 with step 602 , here called "beginning". The procedure for ultrasound imaging 600 provides a series of time delayed transmit signals to the shaped transducer as in step 604 to sonicate a region of interest in the body of a patient. The time delays are based on the in 10 calculated focus geometry and any change in the delay profile resulting from the propagation through the protective cover 206 results.
According to the improved method for ultrasound imaging 600 migrates the generated acoustic energy through a protective cover 206 , which may be configured to take the shape of the two-dimensional transducer element array 502 . 552 etc. exactly as in step 606 illustrated. In alternative embodiments, the two-dimensional transducer element array may be substantially planar with a superimposed protective cover 206 be of uneven thickness.
As described above, the shape of the two-dimensional transducer element array 502 . 552 based on a number of factors including, but not limited to, patient comfort, ergonomic motion patterns for the sonographer, available acoustic window of the patient, and a host of other factors.
Next, in step 608 the received ultrasonic echoes preferably with the same two-dimensional transducer 202 captured and processed for those in the steps 604 and 606 described transmission function has been used. After the received ultrasonic echoes through the transducer 202 into a voltage waveform, the received echoes may be time delayed to the ultrasound imaging system 204 to focus so that the desired patient structures as in step 610 indicated. As in step 604 the time delays are based on the in 10 Focusing geometry shown and any variation of the delay profile due to the propagation through the protective cover 206 calculated. It should be noted that process steps 604 to 610 can be repeated as desired to perform a diagnostic ultrasound examination. Any of several inputs generated by the sonographer may be used to describe the ultrasound imaging procedure 600 to finish, as in step 612 represented here with "end".
As in 7A illustrated, the transducer comprises 700 a body 702 and a protective cover 706 , The protective cover 706 contains a generally spherical tissue contact surface 712 For example, the tissue-contacting surface is generally shaped as part of a sphere.
As in 7A shown is the tissue contact surface 712 or outer surface of the protective cover 206 shaped so that it is comfortable for both the patient and the sonographer. It should be noted that the particular shape selected may depend on the nature of the examination, the dimensions of the patient's anatomy and / or other factors. In this configuration, this embodiment is capable of acoustic energy from the transducer 702 send this energy on a path that is generally coextensive with a long axis 716 of the converter 702 is or extends at an angle thereto. Preferably, a length X 7 of the tissue-contacting surface becomes 712 brought into contact with a suitable cross-sectional area for contact with a body 30 to deliver so that a reasonable amount of acoustic energy from the transducer 702 to the body 30 can be transferred.
As in 7B is shown, the composite geometric structure of a variant of in 7A illustrated embodiment described. In particular, the protective cover comprises 706 , as in 7B shown a tissue contact surface 712 , which is defined primarily by a radius R 1 (in plan view). The surface defined by the radius of curvature R 1 merges at each of its ends into surfaces which are described by the radii of curvature R 2 . Preferably, the radii R 2 are defined by lengths that both allow good acoustic coupling with the patient and maintain a high level of comfort. Radii R 2 are only slightly shorter than the length of radius R 1 , but there is a plethora of possible ratios, including the substantially spherical tissue contact surface defined by the outer surface of the protective cover 706 is formed as in 7A shown.
8A shows an alternative embodiment of a converter 800 , The converter 800 has a body 802 and a protective cover 806 , The protective cover 806 is considered an acoustically non-focusing protective cover 806 configured substantially in the form of an underlying two-dimensional transducer element array (not shown). Preferably, the protective cover 806 a shaped tissue contact surface 812 that resembles a part of a cylinder.
As in 8A illustrates, the converter can 802 be configured to have a tissue contact surface 812 forms with a width X 8 , which has been chosen so that it facilitates the transmission of acoustic energy. As shown, however, the width can also be chosen so that a suitably selected acoustic window is utilized. In particular, the width X 8 , when the protective cover 806 during a thoracic acoustic imaging procedure, for example, be chosen to attempt transducer positioning between adjacent ribs, eg, the ribs 832 and 834 , the body to be imaged 30 to improve. Being positioned, efficient transmission of acoustic energy from the transducer can be 802 from between the ribs and deeper into the body. As in 8A illustrated, the protective cover 806 be substantially cylindrical to efficiently transfer the acoustic energy through the ribs 832 and 834 to transmit formed acoustic windows.
As before with respect to the substantially spherical embodiment of the transducer 702 out 7B described, can be seen from the side ( 8B ) on the outer surface of a protective cover 806 formed fabric contact surface 812 be defined by a radius of curvature R 3 . Each end of the tissue-contact surface junctions can be defined by a radius of curvature R 4 that differs in its length from radius R 3 . In the 8B illustrated protective cover 806 shows a case where R 4 is smaller than R 3 Thus provided, represents the tissue contact surface 812 a relatively flattened surface over the tissue contact area. Thus, the tissue contact surface 812 as an almost optimal transmission medium, while advantageously attempting, inter alia, to exploit the geometry limited rib access points.
The outer surfaces of the protective covers 706 and 806 , as expected, the tissue contact surfaces 712 and 812 are generally curved and can facilitate alignment of the tissue contact surface to an acoustic window. In particular, the outer surfaces of the protective covers tend 706 . 806 if the tissue contact surfaces are adequately dimensioned, then the ribs, eg 832 and 834 , enclosing, thereby allowing the tissue-contacting surface to insert between the ribs. Thus, the surfaces tend to align them with tissue contact surfaces on the acoustic window. The curved surfaces may also improve patient comfort during an imaging procedure, as a non-curved surface may tend to cause localized discomfort.
It should be noted that the protective covers 706 ( 7B ) and 806 ( 8B ) are exemplary only. Some embodiments of the improved transducer may require the arrangement of a complex protective cover and two-dimensional transducer element array 502 . 522 , which varies across the dimensions X, Y and Z (see the 5A . 5B and 10 ). All such variants are considered and are within the scope of the improved ultrasonic transducer.
As in 9 is a preferred embodiment of the converter 202 shown in operable contact with a representative acoustic window. For example, the transducer is suitably at an acoustic window 902 or rib access point of a representative thoracic section 904 positioned to, for example, an acoustic imaging of the heart 906 to enable. As in 9 imaged, intercostal access points are slightly geometry-limited structures, ie rib access points provide a limited area through which acoustic energy can be transmitted (acoustic energy can not penetrate bones to be useful for imaging). Due to the shape of protective covers 706 . 806 the ability to utilize the rib access points for acoustic imaging of tissue within the bony thorax may increase. In addition, the material of the protective cover tends 706 . 806 whose impedance is very similar to that of the body, to improve the amount of acoustic energy transmitted through a rib access point. As described above, the acoustic energy can be electronically focused in both the lateral and elevational directions in both the transmit and receive modes to properly map the structures of the heart.
It It should be emphasized that the above-described embodiments of the improved Ultrasonic transducer, in particular any "preferred" embodiments, only possible examples of implementations are and only for a clear understanding of Transducer principles explained were. There can be many Variations and Modifications to the Embodiments Described Above be made of the improved ultrasonic transducer, without significant to depart from the invention as defined in the appended claims is.
Although the converter 202 here in terms of an ultrasound imaging system 204 For use in medical applications, for example, for a patient, such systems may also be used in various other applications. In addition, various were added to the protective cover 206 associated surfaces here as a suitable positioning of a transducer 202 described relative to an acoustic window. In other embodiments, one or more of these surfaces may be formed as part of the transducer body, for example on the projection of the transducer, to provide similar functionality. All such modifications and variations are to be considered included within the scope of the following claims.
FIG. 2 Image processing system Image processing system
FIG. 3 T / R switch T / R switch A / D converter A / D converter Digital filter Digital filter Receive beamformer Receive beamformer Transmit beamformer Transmit beamformer Transmit waveform modulator Transmit waveform modulator Central controller central control unit Display device display device Video processor video processor Image processor image processor
FIG. 4 Two-dimensional matrix of controllable transducer elements Two-dimensional matrix of controllable transducer elements Transmit beamformer Transmit beamformer Transmit waveform modulator Transmit waveform modulator Central controller central control unit Receive beamformer Receive beamformer delay delay Sum total
FIG. 6 begin Beginning Provide time delayed transmit signal (s) to transducer Providing time-delayed transmit signal (s) for transducers Propagate acoustic energy through shaped cover shape is selected for patient comfort, to maximize patient contact, sonographer ergonomics, reliability, manufacturability, or other factors Transmitting acoustic energy through molded cover, with the shape chosen for patient comfort, to maximize patient contact, ergonomics for the sonographer, reliability, manufacturability or other factors. Receive ultrasound echoes propagated through shaped protective cover Receive ultrasonic echoes transmitted through the molded protective cover Time delay received image to desired patient structures Time delay of the received echoes to focus the resulting image on desired patient structures end The End
Acoustic imaging system ( 200 ), comprising: a transducer ( 02 ) with a two-dimensional transducer element matrix array ( 402 , 502 . 552 ), wherein the transducer has a protective cover ( 206 ) which is configured to be connected to a transducer body ( 208 ), wherein the transducer element matrix array is enclosed by the protective cover and the transducer body is characterized in that: the protective cover of the two-dimensional transducer element matrix is superimposed so that the acoustic energy impinging on the protective cover is mechanically guided by the protective cover according to a focusing characteristic wherein the two-dimensional transducer element matrix array and the protective cover are shaped to reduce patient discomfort and in that the acoustic imaging system comprises: an image processing system (10); 204 ), which is coupled to the converter and configured to over time a plurality of individual excitation signals for the transducer elements ( 408 . 412 . 414 ), so that the two-dimensional transducer element matrix array generates and transmits acoustic energy through the protective cover over time while compensating for the focusing property of the protective cover so that the acoustic energy transmitted through the protective cover is electronically focused.
Acoustic imaging system according to claim 1, wherein the protective cover ( 206 ) comprises an acoustic material having an acoustic impedance corresponding to the acoustic impedance of a body to be imaged.
Acoustic imaging system according to claim 1, wherein at least one of the dimensions of the two-dimensional transducer element matrix array ( 502 . 552 ) is curved.
Acoustic imaging system according to claim 1, wherein the protective cover ( 206 ) is constructed with a non-uniform thickness.
Acoustic imaging system according to claim 1, wherein the protective cover ( 206 ) has an acoustic impedance between about 1.3 MRayl and 1.7 MRayl.
Acoustic imaging system according to claim 1, wherein the protective cover ( 206 ) has a transducer contact with a transducer contact surface, the transducer contact having an end configured to engage with the transducer body (10). 208 ), wherein the tissue-contacting surface forms part of a substantially cylindrical surface.
Acoustic imaging system according to claim 6, the tissue contact surface forms part of a substantially spherical surface.
Acoustic imaging system according to claim 1, wherein the transducer body ( 208 ) is ergonomically adapted to be held by the hand of an operator.
Acoustic imaging system according to claim 1, wherein the protective cover ( 206 ) has a shape that reduces the likelihood of injury to the sonographer due to repetitive motion.
Acoustic imaging system according to claim 1, wherein the compensation is a function of the position of a target point ( 1002 ).
Acoustic imaging system according to claim 1, wherein the image processing system ( 204 ) a plurality of individual receive mode signals from a plurality of transducer elements ( 408 . 412 . 414 ), the received mode signals being representative of the plurality of transducer elements of the two-dimensional transducer element matrix array (10). 402 . 502 . 552 ) are incoming acoustic energy that the protective cover ( 206 ).
Acoustic imaging system according to claim 11, wherein the image processing system ( 204 ) through the protective cover ( 206 ) electronically focused acoustic energy while compensating for the focusing property of the protective cover.
Acoustic imaging system according to claim 12, wherein the compensation is a function of the position of the target point (Fig. 1002 ).
A method of acoustic imaging of a patient, comprising the steps of: creating a transducer ( 202 ) with a two-dimensional transducer element matrix array ( 402 . 502 . 552 ), wherein the transducer has a protective cover ( 206 ) which is configured to be connected to a transducer body ( 208 ), wherein the protective cover of the two-dimensional transducer element matrix is superimposed such that the acoustic energy transmitted from the protective cover into the patient is mechanically guided by the protective cover according to a focusing characteristic, wherein the two-dimensional transducer element matrix array and the protective cover are shaped such that they reduce the discomfort of the patient; Generating a plurality of time-delayed transmission signals to the individual transducer elements ( 408 . 412 . 414 ) of the two-dimensional transducer element array array to electronically focus emitted acoustic waves traversing the protective cover, and at the same time focusing property of the protective cover; and receiving a plurality of delayed response echoes on the separately controllable individual transducer elements of the two-dimensional transducer element matrix array to electronically focus received acoustic echoes traversing the protective cover while compensating for the focusing characteristic of the protective cover.
The method of claim 14, further comprising the step processing the reflected acoustic echoes to create an image.
The method of claim 14, further comprising the steps of: accessing an audible window ( 902 ) of the patient; and acoustic energy through the protective cover ( 206 ) and send it out to the patient via the acoustic window.
The method of claim 14, wherein the steps of Generating and receiving further comprise: electronic Focusing the acoustic energy in an elevation direction; and electronically focusing the acoustic energy in one lateral direction.
The method of claim 16, wherein the step of establishing access to an acoustic window (16) 902 ) comprises an acoustic window formed between juxtaposed ribs of the patient.
DE60222476T 2001-06-27 2002-06-26 ultrasound transducer Active DE60222476T2 (en)
US301282P 2001-06-27
US919232 2001-07-31
DE60222476D1 DE60222476D1 (en) 2007-10-25
DE60222476T2 true DE60222476T2 (en) 2008-06-05
DE60222476T Active DE60222476T2 (en) 2001-06-27 2002-06-26 ultrasound transducer
JP2006524531A (en) * 2003-04-15 2006-11-02 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｅｌｅｃｔｒｏｎｉｃｓ Ｎ．Ｖ． Two-dimensional (2D) array capable of generating harmonics for ultrasound imaging
CN100583234C (en) * 2003-06-09 2010-01-20 皇家飞利浦电子股份有限公司 Method for designing ultrasonic transducers with acoustically active integrated electronics
JP2007526785A (en) 2003-06-30 2007-09-20 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ Two-dimensional transducer array using beam control for view area improvement
FR2875695B1 (en) * 2004-09-28 2006-12-01 Echosens Sa Instrument for measuring the elasticity of an organ of the type comprising a means of centering
WO2006055960A2 (en) * 2004-11-20 2006-05-26 Scenterra, Inc. Device for emission of high frequency signals
EP1890606A1 (en) * 2005-04-25 2008-02-27 Philips Electronics N.V. Method and apparatus for continuous imaging by ultrasound transducer system
JP5137832B2 (en) * 2005-08-05 2013-02-06 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ Curved two-dimensional array ultrasonic transducer and method for volumetric imaging
JP2009510889A (en) * 2005-09-27 2009-03-12 株式会社 メディソンＭｅｄｉｓｏｎ Ｃｏ．，Ｌｔｄ． Ultrasonic diagnostic probe and ultrasonic diagnostic system using the same
JP4839099B2 (en) * 2006-03-03 2011-12-14 オリンパスメディカルシステムズ株式会社 Ultrasonic transducer manufactured by micromachine process, ultrasonic transducer device, ultrasonic diagnostic device in body cavity, and control method thereof
US7569975B2 (en) * 2006-11-07 2009-08-04 Olympus Ndt Cable direct interconnection (CDI) method for phased array transducers
WO2008083520A1 (en) * 2007-01-10 2008-07-17 Yufeng Zhou A shock wave lithotripter system and a method of performing shock wave calculus fragmentation using the same
JP5075665B2 (en) * 2008-02-18 2012-11-21 株式会社東芝 Two-dimensional array ultrasonic probe
DE102008015156A1 (en) * 2008-03-20 2009-09-24 Biotronik Crm Patent Ag Brain stimulation electrode lead and brain stimulation lead insertion device
JP5684083B2 (en) 2011-09-29 2015-03-11 ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー Probe cover, ultrasonic probe, and ultrasonic image display device
SG11201706953YA (en) * 2015-02-25 2017-09-28 Decision Sciences Medical Company Llc Acoustic signal transmission couplants and coupling mediums
JPS586132B2 (en) * 1978-04-25 1983-02-03 Tokyo Shibaura Electric Co
FR2553521B1 (en) * 1983-10-18 1986-04-11 Cgr Ultrasonic Ultrasound probe, manufacturing method thereof and ultrasound apparatus incorporating such probe
AT57112T (en) * 1987-03-20 1990-10-15 Siemens Ag Device for the production and radiation of ultrasonic, in particular for ultrasonic therapy.
FI87048C (en) 1990-04-05 1992-11-25 Anturilaakso Oy Acoustic viewfinder
JP3090718B2 (en) * 1990-07-11 2000-09-25 株式会社東芝 Ultrasound diagnostic equipment
CN1189217A (en) * 1995-06-29 1998-07-29 垓技术公司 Portable ultrasound imaging system
EP1218115B1 (en) * 1999-07-02 2005-02-16 Steve Douglas Ultrasonic linear or curvilinear transducer and connection technique therefore
2002-06-26 CN CNB028128826A patent/CN100354651C/en active IP Right Grant
US7135809B2 (en) 2006-11-14
US10653392B2 (en) 2020-05-19 Ultrasound imaging using apparent point-source transmit transducer
US20140316275A1 (en) 2014-10-23 High frequency ultrasonic convex array transducers and tissue imaging
DE60308495T2 (en) 2007-06-06 Portable 3d ultrasonic system
JP2013039388A (en) 2013-02-28 Broad-beam imaging
US20180310913A9 (en) 2018-11-01 Portable ultrasound imaging system
JP4958348B2 (en) 2012-06-20 Ultrasonic imaging device
JP4783571B2 (en) 2011-09-28 Apparatus and method for controlling an ultrasound probe
US7789831B2 (en) 2010-09-07 Synthetic elevation aperture for ultrasound systems and methods
2008-02-21 8320 Willingness to grant licences declared (paragraph 23)