CN1518670A - Ultrasonic diagnostic system for selectively generating ultrasonic diagnostic data - Google Patents

Abstract

An ultrasound imaging system (100) in which a user determines a desired ultrasound image (306) to view and communicates that desired view to the ultrasound imaging system (100) is disclosed. The ultrasound imaging system (100) analyzes the request and determines the appropriate scan slices (302, 304) to project to obtain the desired image (306). The desired image (306) approximates a three dimensional view, but is developed without the necessity of obtaining a three dimensional volume set of data.

Description

Ultrasonic diagnostic system for selectively generating ultrasonic diagnostic data

The present invention relates generally to ultrasonic diagnostic systems, and more particularly to an ultrasonic diagnostic system that can receive user input with respect to a specific image desired and that can automatically generate ultrasound data related only to the desired image.

Ultrasound transducers and imaging systems have been used for quite some time and are especially useful in the field of non-invasive medical diagnostic imaging. Ultrasonic transducers are usually formed from piezoelectric elements or micromachined ultrasonic transducer elements. When used in transmit mode, the transducer elements are excited by electrical pulses, and ultrasonic energy is emitted in response. When used in receive mode, acoustic energy impinging on the transducer elements is converted into a receive signal and transmitted to processing circuitry associated with the transducer. The transducer is typically connected to an ultrasound imaging system that includes processing electronics, one or more input devices, and a suitable display on which ultrasound images can be viewed. The processing electronics typically include a transmit beamformer, which is used to generate the appropriate transmit pulses for each transducer element, and a receive beamformer, which is used to process Received signal received.

Ultrasound transducers are usually combined with associated electronics in a housing. This component is often called an ultrasound probe. In general, ultrasound probes can be classified as one-dimensional (1D) probes having an array of elements of a single element width or two-dimensional (2D) probes having an array of multiple element widths. In addition, probes known as "dual plane" probes include two orthogonally arranged 1D arrays, which may or may not be intersecting. Relatively new 2D probes known as "matrix probes" consist of transducer elements arranged in two dimensions, where each element is independently controllable, with the result that the scan lines of an ultrasound probe can be electronically manipulate. Each dimension of the matrix probe can be thought of as a contiguous stack of linear arrays.

Ultrasound data is typically acquired in multiple frames, where each frame represents one scan of the ultrasound beam emanating from the transducer surface. Such a scan is usually formed by a large number of individual scan lines generated along a scan plane. When the scanlines are displayed together, the set of scanlines forms what is commonly referred to as a "slice". One slice usually corresponds to one frame. For example, in biplanar imaging, two slices make up a frame, while in volume scans, many slices make up a frame.

Typically, 1D probes produce two-dimensional slices of rectangles, disks, trapezoids, or other shapes, while 2D matrix probes form groups of slices (frames) that form three-dimensional shapes. Such three-dimensional frames are sometimes called "volume scans". When conventional ultrasound imaging systems perform such volumetric scans, they typically produce multiple slices in at least two dimensions. These multiple slices generate ultrasound data for the space occupied by the slices. To produce a three-dimensional image, this volumetric data is then processed by an ultrasound imaging system to produce an image displayed on a two-dimensional surface, such as the surface of a CRT-type display, which has the appearance of three dimensions. Such processing is often called rendering.

Disadvantageously, generating this volume data both burdens the ultrasound electronics controlling the transmit beamformer and requires computationally intensive processing of the received signal. A disadvantage of such 3D mapping systems is that, due to the time delay of the acquired data and the processing delays encountered when rendering the acquired data on the display, in order to display the volumetric data with comparable resolution, the frame rate of the acquired data must be decline.

Accordingly, it would be desirable to provide an ultrasound imaging system that is capable of displaying three-dimensional data without requiring all acquired data to be processed for a given space.

The invention comprises a system for displaying a desired ultrasound image on a display, the system comprising a two-dimensional matrix probe, circuitry for determining at least two ultrasound scan slices corresponding to the desired ultrasound image, for Circuitry for generating the desired ultrasound image from data obtained from the ultrasound scan slice, and a display for displaying the desired ultrasound image.

Other systems, methods, features and advantages of the invention will be understood or will be understood by those of ordinary skill in the art by reference to the drawings and detailed description. It is intended that all such additional systems, methods, features and advantages be included within this description, be within the scope of the invention, and be protected by the following claims.

The invention as defined by the claims may be better understood by reference to the following drawings. The relative proportions of the elements in the figures are not critical, emphasis instead being placed upon clearly illustrating the principles of the invention.

FIG. 1 is a block diagram illustrating an ultrasound imaging system according to one embodiment of the present invention.

FIG. 2 is a schematic diagram of a series of scanned slices obtained using the matrix probe of FIG. 1 .

3A to 3C are schematic diagrams collectively illustrating one embodiment of the present invention.

FIG. 4 is a diagram of obtaining data scanned by a single frame according to another embodiment of the present invention.

FIG. 5 is a schematic illustration of an image obtained using the scan geometry shown in FIG. 4 .

Fig. 6 is a schematic diagram illustrating another embodiment of the present invention.

FIG. 7 is a schematic diagram showing another embodiment generated by the pattern generator of FIG. 1 .

Figure 8 is a flowchart illustrating the operation of a particular embodiment of the invention.

The invention described next can be applied to any ultrasound imaging system using a probe having a two-dimensional array of independently controllable elements. The following description is in terms of routines and symbolic representations of data bits in memory, an associated processor, and possibly a network or network equipment. These descriptions and characterizations are used by those of ordinary skill in the art to effectively convey the substance of their work to others of ordinary skill in the art. A routine here generally refers to a discrete sequence of steps or actions leading to a desired result. Thus, the term "routine" is generally used to refer to a series of operations stored in memory and executed by a processor. The processor may be a central processor of the ultrasound imaging system, or may be a secondary processor of the ultrasound imaging system. The term "routine" also includes such terms as "program", "object", "function", "subroutine" and "procedure".

Often, the sequence of steps in a routine procedure requires physical manipulations of physical quantities. Usually, though not necessarily, these quantities take the form of electrical or magnetic signals that are stored, transferred, combined, compared, or otherwise manipulated. Those of ordinary skill in the art refer to these signals as "bits," "values," "elements," "characters," "images," "terms," "numbers," and the like. It should be understood that these and similar terms are to be associated with the appropriate physical quantities and are merely convenient labels applied to these quantities.

In this application, routines and operations are machine operations performed with an operator. The present invention generally relates to method steps, software and associated hardware including computer readable media arranged to store and execute electrical or other physical signals to produce other desired physical signals.

The device of the present invention is preferably configured for ultrasound imaging. However, the methods of the present invention may be performed by a general purpose computer or other networked device selectively activated or reconfigured by routines stored in the computer and connected to an ultrasound imaging device. The procedures presented here do not involve any ultrasound imaging system, computer or equipment per se. In particular, different machines may use the routines in accordance with the invention, or it may be more convenient to construct more specialized apparatus to perform the steps of the method. In some cases, when it is desirable for a piece of hardware to possess certain characteristics, those characteristics are described more fully below.

With respect to the routines described below, those of ordinary skill in the art will recognize that a variety of platforms and languages exist for generating sets of instructions to execute the routines described below. Those of ordinary skill in the art will also recognize that the exact choice of platform and language is often determined by the actual system being built, so what works for one type of system may not work for another.

FIG. 1 is a block diagram illustrating an ultrasound imaging system 100 according to an embodiment of the present invention. It should be understood by those of ordinary skill in the art that the ultrasound imaging system 100 shown in FIG. 1 and its operation as described below is generally representative of such systems, and that any particular system may be used in conjunction with the system shown in FIG. The systems are very different. The ultrasound imaging system 100 includes a transmit beamformer 110 connected to a matrix probe 200 through a transmit/receive switch 112 . The matrix probe 200 includes a matrix transducer array having a plurality of transducer elements arranged in two-dimensional directions. The matrix probe 200 can be used to randomly select any point on the array as the point from which ultrasound energy is emitted, and is referred to as a fully sampled array. In a fully sampled array, each element is independently addressable.

The transmit/receive (T/R) switch 112 typically includes one switching element for each transducer element, or the matrix probe 200 may have a multiplex circuit or the like to reduce the number of T/R switches 112 and matrix probes. The number of wires between 200, thereby reducing the number of switches required. The transmit beamformer 110 receives a sequence of pulses from a pulse generator 116 . The matrix probe 200 is excited by a transmit beamformer 110, which transmits ultrasound energy to regions of interest in the patient's body and receives reflected ultrasound energy, generally referred to as echoes, from various structures and organs in the body. Those of ordinary skill in the art know that a focused ultrasound beam can be transmitted from matrix probe 200 by using transmit beamformer 110 to appropriately delay the waveforms applied to each transducer element.

The matrix probe 200 is also connected to a receive beamformer 118 through a transmit/receive switch 112 . Ultrasound energy from a given point in the patient's body is received by the transducer elements at different times. This transducer element converts the received ultrasound energy into a transducer signal, which may be amplified, individually delayed, and then summed by the receive beamformer 118 to provide a representative signal along the desired receive line (" beam”) received beamforming signals at the ultrasound level. The receive beamformer 118 may be a digital beamformer including an analog-to-digital converter to convert the transducer signals to digital values, or may be an analog beamformer. It is known to those of ordinary skill in the art that the delay applied to the transducer signal can be varied during ultrasound energy reception to achieve dynamic focusing. This process is repeated for multiple scan lines to generate a frame of data for use in generating an image of the region of interest in the patient's body.

While known systems using matrix probes focus on scanning the entire volume of space, the matrix probe 200 can also provide multiple scan modes, such as sector scan, linear scan, curved scan, and other scan modes, where the scan lines of the sector scan are typically originate from the center of the matrix probe 200 and point at different angles.

The receive beamformed signal is then supplied to a signal processor 124 which processes the beamformed signal to improve the quality of the image. Receive beamformer 118 and signal processor 124 are configured as ultrasound receiver 126 . The output of signal processor 124 is applied to scan converter 128, which converts sector scan and other scan mode signals to conventional raster scan display signals. The output of the scan converter 128 is supplied to a display unit 130 which displays an image of the region of interest in the patient's body.

The system controller 132 performs overall control of the system. The system controller 132 performs timing and control functions and typically includes a microprocessor operating under the control of a pattern generator 136 and control routine 142, both contained in memory 140 . As will be described in further detail below, the control routine 142 and pattern generator 136 cooperate with the system controller 132 and input provided from the user through the input element 138 to cause the ultrasound imaging system 100 to transmit only those The scanlines required for the desired image. In this way, the ultrasound imaging system 100 can generate an approximate three-dimensional image by scanning only those slices corresponding to the image to be displayed, without scanning the entire three-dimensional space. In such systems, as will be described next, better image quality can generally be achieved using fewer system resources, so that an approximate 3D image is displayed using a frame rate comparable to 2D scanning. The system controller 132 also uses the memory 140 to store intermediate values including system variables that describe the operation of the ultrasound imaging system 100 . Although not shown, external storage devices may be used to store data persistently and/or transferably. Examples and devices suitable for use with external storage units include floppy disk drives, CD-ROM drives, video tape units, and the like.

According to an aspect of one embodiment of the present invention, a scan pattern corresponding to and designed to provide a desired ultrasound image may be generated by the matrix probe 200 . A user of the ultrasound imaging system 100 may communicate such desired ultrasound images through the input unit 138 . The scan pattern may include a pair of intersecting scan slices, which allows the system to compose an approximate three-dimensional image without interrogating three-dimensional space. The input unit 138 may include a mouse, a keyboard, a stylus, or may include a combination of input devices, such as keys, sliders, switches, touch screens, trackballs, or other input devices that allow the ultrasound imaging system to A user of 100 may transmit desired ultrasound images to system controller 132 . When the desired ultrasound image is communicated to the system controller 132 via the input unit 138, the system controller 132 cooperates with the control routine 142 in the memory 140 and the pattern generator 136 to determine the appropriate scan line, the scan line The wires should be transmitted by the matrix probe 200 to obtain the desired ultrasound image that is transmitted to the system controller 132 . The system controller 132 then communicates with the pulse generator 116 and transmit beamformer 110 to generate such appropriate scanlines.

In another system configuration, different transducer elements are used for transmitting and receiving. In such a configuration, the transmit/receive switch 112 may not be required, and the transmit beamformer 110 and receive beamformer 118 may be connected directly to the respective transmit and receive transducer elements.

FIG. 2 is a schematic diagram of a series of scan slices obtained using the matrix probe 200 of FIG. 1 . The matrix probe 200 shown in FIG. 2 acquires three slices 202 , 204 and 206 . Typically, each slice 202, 204, and 206 includes a series of individual scan lines 208-1 to 208-n, 210-1 to 210-n, and 212-1 to 212-n, respectively. In this case, each slice is fan-shaped, and the apex of the fan is located in the middle of the matrix probe 200 . In effect, each slice 202, 204, and 206 represents a conventional two-dimensional scan, with each scan displaced in elevation from adjacent scans. Those of ordinary skill in the art know that a trapezoid or a parallelogram may be generated for each slice instead of a sector. Furthermore, a large number of such slices slightly shifted in elevation can be used to interrogate a volume of space. Disadvantageously, interrogating a spatial volume requires significant processing resources due to the large number of scan slices required to interrogate a spatial volume, and typically produces much more data than is required to display the desired image. According to an embodiment of the present invention, and described in detail below, the ultrasound imaging system 100 allows user input to determine a desired image and then instructs the matrix probe 200 to transmit only the individual scans necessary to display the desired image slice.

In the example shown in FIG. 2, there are only three slices 202, 204 and 206 joined at a vertex, but separated in elevation. Each scanline 208-n, 210-n, and 212-n in each slice 202, 204, and 206, respectively, has a matching (or "corresponding") scanline in the other slice. For example, scan line 210 - 1 in slice 204 matches scan line 212 - 1 in slice 206 . Preferably each matching scanline is at the same lateral position. To render an approximate three-dimensional image, the system controller determines the appropriate set of matching scanlines and emits only the scanlines necessary to display the desired image. According to an embodiment of the present invention, the system controller 132, along with the pattern generator 136 and control routine 142, instructs the matrix probe 200 to emit only the scanlines required to display the desired image.

3A to 3C are schematic diagrams collectively showing one embodiment of the present invention. FIG. 3A includes two sector scan slices 302 and 304 . Sector scan slices 302 and 304 are shown to be perpendicular to each other, but this is not required as sector scan slices 302 and 304 may be separated by any angle, referred to herein as Θ. The angle θ represents the angle of inclination between the sector scan slice 304 and the sector scan slice 302 . The sector scan slice 302 includes a centerline 305 and the sector scan slice 304 includes a centerline 307 . Image 306 is a generally pear-shaped hollow image, meant to represent a simplified left ventricle.

As shown in FIG. 3A, the system controller 132 generates only two sector scan slices 302 and 304, rather than interrogating the entire space. The two fan-shaped slices 302 and 304 are formed according to user input communicated to the ultrasound imaging system 100 . The user input defines the desired ultrasound image, and the system controller determines the sector scan slices (sector scan slices 302 and 304 in this example) corresponding to the desired images.

One of the scan sector slices (in this case, the scan sector slice 302) is a fixed reference slice (or a fixed reference plane), while the position of the scan sector slice 304 can vary in elevation and can be relative to the scan sector slice 302 Rotate position. According to the input applied by the user to the ultrasound imaging system 100 through the input unit 138, the position of the sector scan slice 304 relative to the sector scan slice 302 can be adjusted in the form of elevation angle, and the position can be rotated so that the desired image pair (as shown in FIG. 3B and 3C) is generated by sector scanning slices 302 and 304. To communicate a desired image to system controller 132 ( FIG. 1 ), a user of ultrasound imaging system 100 may use, but is not limited to, a control knob provided, for example, on input unit 138 to rotate relative to sector scan slice 302 Slice 304 is sector scanned. This control knob can be labeled, for example, "2nd Slice Rotation Angle". The desired image is the image set by the user by adjusting the control knob during scanning. The image slices (fan slices 302 and 304 in this example) can be displayed in parallel as shown in FIGS. 3B and 3C , or overlapped as shown in FIG. 5 .

Figures 3B and 3C collectively illustrate images acquired using sector scan slices 302 and 304 in Figure 3A. As shown in FIGS. 3B and 3C , an ultrasound image 306 is displayed in relation to each scan slice 302 and 304 . As shown, the image 306 associated with the scan slice 302 and the image 306 associated with the scan slice 304 look different. Images 306 in FIGS. 3B and 3C are two perpendicular sections of a roughly pear-shaped hollow image meant to represent a simplified left ventricle and correspond to image 306 in FIG. 3A . The two images 306 in FIGS. 3B and 3C appear different because scan slices 302 and 304 are perpendicular to each other and form different cross-sections of element 306 . Considering another approach, an acoustic acquisition oriented to accommodate a sector scan slice 302 is shown in FIG. 3B , while an acoustic acquisition oriented to accommodate a sector scan slice 304 is shown in FIG. 3C . In this way, an approximate three-dimensional composition can be obtained by only transmitting two independent scan slices based on user input. The resolution of the images in Figures 3B and 3C represent improvements in image resolution obtained by systems that need to scan three-dimensional space in order to render a three-dimensional image. For example, the images in Figures 3B and 3C may be 90 degree wide views with a frame rate of 50 Hz and a resolution of 3/4 degree. A wide field of view combined with a high frame rate is achievable since the entire space does not need to be scanned.

Furthermore, according to another embodiment of the present invention, a graphical reference related to the two images may be provided. For example, the line labeled 312 in FIG. 3B refers to the location of the sector scan slice 304 and corresponds to the centerline 307 of the sector scan slice 304 . Likewise, the line labeled 314 in FIG. 3C is associated with the sector scan slice 302 in FIG. 3B and corresponds to the centerline 305 of the sector scan slice 302 .

The image in FIG. 3C can be generated in a different plane by moving line 312 of FIG. 3B relative to the fixed reference slice 302 and the position of the sector scan slice 304 determined by user input. Such a graphic display may be provided by graphic generator 136 in FIG. 1 and may control the orientation of sector scan slice 304 .

In addition, effectively acquiring two images is useful when performing cardiac stress echo testing on a patient. In such tests, the application of such tests to a patient and the need to provide an adequate diagnosis requires rapid acquisition and imaging of the heart. The system of the present invention allows such imaging due to the increased frame rate obtainable by projecting only two sector scan slices. In addition, the images depicted in Figures 3A and 3B can provide automatic border detection and can display colored flow velocity information and ultrasound ANGIO information. Automatic border detection refers to the ability of the system to automatically detect and display the border between tissue and blood. The term "ANGIO" refers to a form of color fluid imaging that exchanges fluid orientation information for fluid sensitivity information. This mode of operation is also known as "color Doppler power" imaging.

FIG. 4 is a diagram of a single frame scan of data obtained according to another embodiment of the present invention. FIG. 4 includes a matrix probe 400 used to obtain a slice 402 comprising two sub-slices 404 and 406 . The first sub-slice 404 is taken planarly, and the second sub-slice 406 is perpendicular to the first sub-slice 404 . The two sub-slices 404 and 406 are joined at a centerline 408 . Such a scan sequence draws what is known as an "angular view". Since only a single folded slice is scanned and no other slices or planes are scanned, the frame rate can be as high as standard 2D scans in the 50 Hz range. The scan shown in Figure 4 can be visualized as two connected halves of a target, revealing a vertical tissue structure that moves relative to each other in real time.

FIG. 5 is a schematic diagram showing an image obtained using the scanning geometry shown in FIG. 4 . An example of how such a geometry may be displayed is shown by display 500, where the two scan halves 502 and 504 are shown as two side-by-side and foreshortened sectors, sometimes referred to as a "half-planar" image. Structural wire frames 506 and 508 enclose the scan plane of the half-slice. Display 500 is similar to the perspective of the corner of the box, with a half-fan image drawn on the side walls.

Fig. 6 is a schematic diagram illustrating another embodiment of the present invention. Display image 600 may be generated on display 602 through use of graphics generator 136 in conjunction with system controller 132 . The display 602 includes a displayed ultrasound image 606 , also illustrating that the shape of the probe 604 may be applied to the display 602 . In this way, a user of the ultrasound imaging system 100 can observe the position of the probe 604 directly on the display 602, thereby enabling more precise alignment and positioning of the probe 604 on the body of the patient being imaged.

FIG. 7 is a schematic diagram showing another implementation generated by pattern generator 136 of FIG. 1 . Image 700 of FIG. 7 includes a first scan slice 702 and a second scan slice 704 depicted by dashed lines. The second scan slice 704 is displayed rotated relative to the scan slice 702 . The scan slice 704 is rotated about the cursor line 706 relative to the scan slice 702 . Dashed line 704 is a depiction of a rotating sector rotating around cursor line 706 . For example, as shown in FIG. 7 , there is a rotational offset of 78 degrees between slices 702 and 704 . When the angle is 90 degrees, slice 704 disappears. Additionally, image 700 may show the tilt of scan slice 704 relative to scan slice 702 .

FIG. 8 is a flowchart 800 illustrating the operation of a particular embodiment of the invention. In block 802, the operator of the ultrasound imaging system 100 selects the desired graphics for display. In order to determine the appropriate sector scan slice that will result in the desired image, the system controller 132 executes an appropriate control routine 142 to select a new rotation vector or elevation relative to the fixed reference plane (302 of FIG. 3A ) such that The desired ultrasound image can be drawn. In block 802, the system controller 132 communicates with the system controller 132 assuming that the fixed reference plane 302 provides one of the ultrasound images, and in response to a command entered by the operator through the input element 138 that communicates the desired particular ultrasound image to the system. Control routine 142 cooperates with pattern generator 136 (FIG. 1) to determine the proper location and positioning of sector scan slice 304 relative to fixed sector scan slice 302 (ie, fixed reference plane).

In block 804, it is determined whether the angle view option described above with respect to FIGS. 4 and 5 is selected. If the angular view option is not selected, then in block 806 the system controller 132 alters the scan line sequence in order to use the matrix probe 200 to produce the desired full plan image. In such an example, to obtain the desired ultrasound image 306 (FIGS. 3B and 3C), two fan-shaped scan planes 302 and 304 (FIG. 3A) would be projected.

In block 804, if it is determined that the angle view option is activated, then in block 808 the system controller 132 will alter the scan line sequence to produce a semi-planar image using the matrix probe 200 according to the flow described with respect to FIGS. 4 and 5 .

In block 810, scan converter 128 and system controller 132 will use graphics generator 136 to update the graphics to display the image of the second sector scan slice (i.e., sector scan slice 304) relative to the fixed reference plane of sector scan slice 302. orientation. If the angular view option is off, then the orientation of the third, fourth, fifth sector scan slice, etc. may be displayed on the display 130 . In block 812, the ultrasound imaging system 100 scans and displays the desired image.

Those skilled in the art can understand that many modifications and changes can be made to the present invention without departing from the principles of the present invention, as described above. For example, piezoceramic and MUT transducer elements may be used with the present invention. Furthermore, the invention finds application in various ultrasound imaging systems and components. All such modifications and variations are included in the present invention.

Claims (10)

1. system (100) that is used on display (130), presenting desired ultrasonoscopy, it comprises:

The probe matrix (200) of two dimension;

System controller (132), it is used for determining at least two ultrasonic scanning sections (302,304) corresponding to this desired ultrasonoscopy (306);

Scan converter (128), it is used for generating this desired ultrasonoscopy (306) from the data that obtained by described at least two ultrasonic scannings sections (302,304); And

Display (130), it is used to show this desired ultrasonoscopy (306).

2. the system as claimed in claim 1 (100) is characterized in that: the ultrasonoscopy of this demonstration (306) comprises and is oriented the respective image that is adapted to each scan slice in described at least two ultrasonic scannings sections (302,304).

3. the system as claimed in claim 1 (100) is characterized in that: described at least two ultrasonic scannings sections (302,304) can at random be located each other.

4. the system as claimed in claim 1 (100) is characterized in that: described at least two ultrasonic scannings sections (302,304) provide color flow information.

5. the system as claimed in claim 1 (100) is characterized in that: described two ultrasonic scannings sections (302,304) formation angle view (500) at least.

6. one kind is used for going up the method that shows desired ultrasonoscopy (306) at display (130), and it comprises:

Produce at least two ultrasonic scanning sections (302,304) with matrix transducer probe (200), described at least two ultrasonic scannings sections (302,304) are corresponding to desired image (306); And

From described at least two ultrasonic scannings section (302,304) generate this desired image (306) in, this desired image (306) is shown as a plurality of views, and each view is corresponding to a scan slice in described at least two ultrasonic scannings sections (302,304).

7. method as claimed in claim 6 is characterized in that: it also comprises at random locatees described at least two ultrasonic scannings sections (302,304) each other.

8. method as claimed in claim 6 is characterized in that: it also comprises for each ultrasonoscopy (306) and first ultrasonic scanning section (302) is positioned at the position of coordinating mutually.

9. method as claimed in claim 6 is characterized in that: it comprises that also described at least two ultrasonic scannings sections of use (302,304) form angle view (500).

10. method as claimed in claim 6, it is characterized in that: it also comprises and demonstrates figure benchmark (604), this figure benchmark is used for representing with respect to this corresponding image the position of this probe matrix (200), this corresponding image orientation becomes to be adapted to each scan slice in described at least two ultrasonic scannings sections (302,304).

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