CN110974293B - Synthetic aperture imaging method based on C-type probe - Google Patents
Synthetic aperture imaging method based on C-type probe Download PDFInfo
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
- A61B8/4444—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
- A61B8/4455—Features of the external shape of the probe, e.g. ergonomic aspects
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/48—Diagnostic techniques
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/5207—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of raw data to produce diagnostic data, e.g. for generating an image
Abstract
The invention belongs to the technical field of high-resolution ultrasonic imaging, and discloses a synthetic aperture imaging method based on a C-type probe, wherein the method comprises the following steps: (1) collecting original data; (2) data preprocessing: for original echo data, at most, only the ultrasonic signals received and collected by L receiving array elements at the left and right of a transmitting array element are reserved; (3) filtering; (4) image reconstruction: gridding the imaging area, focusing the filtered signals image point by image point based on the synthetic aperture focusing technical principle, calculating to obtain data values of all image points, and finally reconstructing to obtain an image of a section; and may preferably comprise the steps of: (5) and (5) reconstructing a three-dimensional image. The invention can effectively solve the problem of reconstructing the ultrasonic image of the C-type probe by improving the whole flow design of the ultrasonic imaging method of the C-type probe, particularly the key echo preprocessing step, the composition of each functional module of the corresponding imaging system, the matching working mode of the functional modules and the like.
Description
Technical Field
The invention belongs to the technical field of high-resolution ultrasonic imaging, and particularly relates to a synthetic aperture imaging method based on a C-shaped probe, which can be directly applied to two-dimensional imaging to obtain a two-dimensional ultrasonic image of a section, for example, and can also be applied to three-dimensional imaging, for example, the obtained ultrasonic images of a plurality of sections are further used for three-dimensional image reconstruction, and the like.
Background
Ultrasonic detection has the advantages of good directivity, low price, no harm to human body, portability of equipment and the like, so that a detection technology using ultrasonic waves as an emission source instead of rays to irradiate an object has gradually become one of new targets pursued by researchers in the field of ultrasonic application.
The main disadvantages of ultrasound imaging are the low resolution and poor contrast of ultrasound images. The ultrasonic tomography system usually adopts a ring probe, compared with a linear array probe, the ring probe has more array elements, can provide 360-degree echo data, processes the data, can further improve the resolution of images, improves the imaging quality, and is beneficial to the diagnosis and treatment of diseases clinically by doctors. The shape of the ultrasonic probe is closely related to the detected part, and the annular probe is suitable for mammary gland detection, but for pregnant women, the annular probe is not suitable for moving in the abdomen to perform fetal detection, so that the C-shaped probe can be selected for detection, and echo data can be acquired for image reconstruction.
At present, no ultrasonic enterprise and research unit for mastering the technology exist in China. The main reason is that several difficulties of the technology are not overcome at home: in order to improve the image quality, the designed C-type probe has large array element number, multiple channels and large data volume, and the high-resolution image is difficult to realize by selecting a proper reconstruction algorithm.
Disclosure of Invention
In view of the above defects or improvement requirements of the prior art, an object of the present invention is to provide a method for forming a synthetic aperture image based on a C-type probe, wherein the problem of reconstructing an ultrasound image of the C-type probe can be effectively solved compared with the prior art by improving the overall process design of the C-type probe ultrasound imaging method, particularly the key echo preprocessing step, and the composition of each functional module of the corresponding imaging system and their cooperating working modes; in addition, the imaging method and the imaging system have high imaging resolution.
To achieve the above object, according to the present invention, there is provided a method for forming a synthetic aperture based on a C-type probe, comprising the steps of:
(1) collecting original data:
numbering array elements in the C-shaped probe from 1 to H in a clockwise direction or a counterclockwise direction, wherein the array elements in the C-shaped probe are uniformly distributed on a C-shaped circular arc or a C-shaped elliptical arc, and H is the total number of the array elements in the C-shaped probe; then, starting to transmit ultrasonic signals from the array element numbered as 1 until the array element numbered as H; when each array element transmits an ultrasonic signal, each array element in the C-shaped probe receives and acquires the ultrasonic signal to obtain original echo data;
and, the space position of the C-type probe is kept stable when transmitting and receiving signals;
(2) data preprocessing:
for the original echo data obtained in the step (1), as the transmitting array elements are sequentially changed from the array element numbered 1 to the array element numbered H, for each transmission, the array element number of the transmitting array element at the time of the transmission is recorded as i,
if i satisfies 1 and L, intercepting and preprocessing corresponding echo data, and only reserving ultrasonic signals with serial numbers received and collected by (2i-1) array elements in total of 1, 2, … …, i, (i +1), … … and (2 i-1);
if i satisfies L < i < (H-L +1), intercepting and preprocessing corresponding echo data, and only reserving ultrasonic signals received and collected by (i-L), (i-L +1), … …, (i-1), i, (i +1), … …, (i + L-1) array elements in total (2L +1) in number;
if i is more than or equal to (H-L +1) and less than or equal to i, intercepting and preprocessing corresponding echo data, and only reserving ultrasonic signals received and collected by (2H-2i +1) array elements with serial numbers of (2i-H), (2i-H +1), … …, i, … … and H;
therefore, the interception preprocessing is completed on the whole original echo data; wherein, L is a preset positive integer;
(3) and (3) filtering treatment:
filtering the echo data obtained in the step (2) after the interception preprocessing is completed to obtain a filtered signal;
(4) image reconstruction:
firstly, gridding an imaging area, wherein the plane of the imaging area coincides with the plane of a C-shaped circular arc or a C-shaped elliptical arc of the C-shaped probe, and the imaging area is gridded according to a rectangular coordinate to be divided into M multiplied by N grids; m, N are preset positive integers;
then, focusing the filtered signals obtained in the step (3) by imaging points based on the synthetic aperture focusing technical principle, namely, respectively taking each grid area as an imaging point, and calculating the influence of all transmitting array elements on the imaging point; specifically, for the influence of a certain transmitting array element on the imaging point, the echo data corresponding to the imaging point is selected from the echo data corresponding to the transmitting array element according to the delay time; thus, for all transmitting array elements, all the obtained echo data corresponding to the imaging point are superposed, and then the data value of the imaging point can be obtained through calculation;
after the data value calculation is completed for all the grid areas, the matrix data value of M multiplied by N can be obtained, and then the matrix data value is subjected to envelope detection, logarithmic compression and gray mapping, so that an image of a section can be reconstructed.
As a further preferred of the present invention, the method further comprises the steps of:
(5) three-dimensional image reconstruction:
translating the C-shaped probe, updating the spatial position of the C-shaped probe, and repeating the operations from the step (1) to the step (4) to reconstruct an image of a new section; the translation-repeated operation is carried out for multiple times, and images of multiple sections can be obtained; based on the images of the sections, a three-dimensional image can be reconstructed.
As a further preferred aspect of the present invention, in the step (4), the data value calculation of any one imaging point satisfies:
wherein, I (t) is the data value of the imaging point; i corresponds to the transmitting array element and numbers the transmitting array element(ii) a j corresponds to the receiving array element and is the number of the receiving array element; the plane of the imaging area is the XZ plane of the rectangular space coordinate system, and (x, z) are the space coordinates of the imaging point, and (x)i,zi) Is the space coordinate of the transmitting array element with array element number i, (x)j,zj) Is the spatial coordinate of the receiving array element with array element number j; c is the speed of sound; t is ti,jCalculating delay time when the array element with the array element number i is used as a transmitting array element and the array element with the array element number j is used as a receiving array element;
preferably, c is 1540 m/s.
In a further preferred embodiment of the present invention, in the step (5), the translation length of each translation is 1-5 mm, and preferably, the direction of translation is perpendicular to the plane of the C-shaped arc or C-shaped elliptical arc of the C-shaped probe.
As a further preferred aspect of the present invention, in the step (1), the receiving and acquiring an ultrasound signal is specifically receiving and acquiring a signal of ultrasound reflection.
More preferably, H is an integer of 1024 or more; the arc length of the C-shaped arc or the C-shaped elliptic arc of the C-shaped probe is 300 mm to 350 mm, and the curvature radius is 350 mm to 400 mm.
As a further preferable aspect of the present invention, in said step (2), L satisfies H/9. ltoreq. L. ltoreq.H/7; preferably, L is equal to the integer resulting from the rounding of H/8.
As a further preferable aspect of the present invention, in the step (4), M is a value obtained by dividing the length of the imaging region by Δ, and N is a value obtained by dividing the width of the imaging region by Δ, where Δ is a preset side length of a square imaging point; preferably, Δ is 0.1 mm.
Compared with the prior art, the technical scheme of the invention has the advantages that the ultrasonic echo is specially preprocessed, so that the ultrasonic imaging method and the ultrasonic imaging system based on the C-shaped probe can be obtained, the original echo data is collected, and the high-resolution image reconstruction is carried out. Based on the technical principle of synthetic aperture focusing, for a transmitting array element i in the middle area of a C-shaped probe, L < i < (H-L +1), selecting the transmitting array element as a center, and taking L array elements (2L +1 array elements in total) to the left and the right as receiving array elements in an aperture corresponding to the transmitting array element; for the transmitting array element i in the two end areas, i is more than or equal to 1 and less than or equal to L or (H-L +1) is more than or equal to i and less than or equal to H, the (2i-1) or (2H-2i +1) array elements which are from the transmitting array element i as the center to the array element at the nearest end point and are symmetrical left and right are selected as the array elements in the aperture corresponding to the transmitting array element, so that based on the principle of a synthetic aperture focusing technology, on one hand, the operation speed can be improved, and on the other hand, the higher resolution of the image can be ensured.
Taking a C-type probe with an array element number of 1024 as an example, a large amount of original data can be obtained and an image of a section can be reconstructed by collecting once because the array element number is large; in order to obtain a three-dimensional image, the probe can be translated and data acquisition can be carried out again; after the three-dimensional ultrasonic image is obtained by translating for many times and acquiring for many times, the resolution of the image can be improved by carrying out synthetic aperture imaging processing on a large amount of original data.
The invention can adopt the data received by ultrasonic reflection to reconstruct the image. Supposing that the ultrasound propagates in an ideal medium, the sound velocity does not change greatly, the acquired original data needs to be preprocessed firstly, only the received data of L array elements around the transmitting array element are reserved, and other data are cut off; l is a pre-selected positive integer, and the larger L is selected, the larger the receiving aperture is, and the higher the resolution of the image is theoretically, but if L exceeds a certain value, a large artifact is caused, and therefore, a reasonable value of L needs to be calculated according to the size and position of the array element. The preferable value range of L can be a value in an interval from one seventh of H to one ninth of H, and more preferably one eighth of H (since L is a positive integer, L can be obtained by rounding when one eighth of H is not an integer), and at this time, not only can a higher resolution of an image be ensured, but also a negative influence of a larger artifact can be avoided. For the retained original data, a zero-phase band-pass filter and the like can be selected for filtering processing, signals near the center frequency of the probe are retained (for example, signals from 2MHZ to 3MHZ are retained if the center frequency is 2.5 MHZ), and other low-frequency direct-current bias signals and high-frequency noise signals are filtered (for example, signals below 2MHZ and above 3MHZ are filtered). Then, the preprocessed data is used for image reconstruction, and a method of SAFT (Synthetic aperture focusing technique) is adopted, which is equivalent to performing point-by-point focusing on the received echo signals. Specifically, the imaging region is first divided into M × N grids, M and N being integers. And taking the area in each grid as an imaging point, and calculating the influence of each transmitting array element on the imaging point, namely for the signal sent by each transmitting array element, receiving the echo data of the array element at the point. And aligning and superposing all the calculated echo data according to the receiving aperture, and finally obtaining the data value of the point. After the calculation of the region in each grid is completed, M × N matrix data can be obtained, and the data is subjected to logarithmic compression and gray mapping to obtain a reconstructed image of a section.
In order to obtain a three-dimensional image, a C-shaped probe is translated for 1-5 mm, and data are collected again; and performing similar processing calculation on the data acquired again to reconstruct an image of a new section. Through multiple translations, images of a plurality of sections can be obtained; three-dimensional reconstruction software and the like can be used, for example, all section data are imported into the three-dimensional reconstruction software, and then a three-dimensional image can be obtained.
Drawings
FIG. 1 is a schematic illustration of a type C probe synthetic aperture imaging; in the figure, E (x)i,zi) For transmitting array elements, R (x)j,zj) To receive the array elements, P (x, z) is the imaging dot schematic.
Fig. 2 is a schematic view of a C-probe translation.
Fig. 3 is a signal processing flow diagram of the synthetic aperture three-dimensional imaging method of the present invention, in which TGC (Time Gain compensation) may be implemented by conventional processing in the prior art.
Fig. 4 is a sectional view of the body membrane obtained by collecting body membrane data and reconstructing the body membrane data by the acoustic system of the C-type probe based on the method provided by the invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the present invention is described in further detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention. In addition, the technical features involved in the embodiments of the present invention described below may be combined with each other as long as they do not conflict with each other.
The synthetic aperture imaging method based on the C-shaped probe can be directly applied to two-dimensional imaging to obtain a two-dimensional ultrasonic image of a section, for example, and can also be applied to three-dimensional imaging to reconstruct three-dimensional images of a plurality of obtained section ultrasonic images (of course, the distance between the sections needs to meet certain requirements, for example, the distance between adjacent sections does not exceed 5mm, even does not exceed 1mm, and the like). The method for the three-dimensional imaging of the synthetic aperture based on the C-type probe is mainly realized by repeatedly performing the method for the two-dimensional imaging of the synthetic aperture based on the C-type probe and reconstructing three-dimensional images of a plurality of obtained section ultrasonic images, so that the method for the three-dimensional imaging of the synthetic aperture based on the C-type probe is taken as an example below to describe the invention in detail, and if only two-dimensional imaging needs to be obtained, the reconstruction can be stopped when the image of one section is obtained.
Example 1:
in the synthetic aperture three-dimensional imaging method based on the C-shaped probe, generally, the original data acquired by an ultrasonic system of the C-shaped probe is properly processed, and finally, an ultrasonic image is obtained through reconstruction; the specific steps can include data acquisition by translating the C-type probe, data preprocessing, area subdivision, time delay superposition, weighted average, envelope detection, logarithmic compression, gray level mapping and display. The C-shaped probe can be a circular arc or an elliptical arc.
The data acquisition adopts the mode of single shot full connection, and the transmitting array element is in proper order transmission signal, and all array elements receive the signal. Because the data volume is huge, in order to improve the imaging speed, in the embodiment, only L array elements at the left and right of the transmitting array element are selected as the receiving aperture, L is a positive integer obtained after the eighth rounding of the total number H of the array elements (the rounding can be upward rounding, downward rounding or rounding), the data of the receiving aperture is reserved, other data are truncated, and the data are collected again after the probe is translated by 1-5 mm.
After data acquisition is finished, a zero-phase band-pass filter is selected to filter the data, signals near the ultrasonic center frequency are reserved, low-frequency direct-current bias signals and high-frequency noise signals are filtered, and the signals after pretreatment can be used for ultrasonic image reconstruction. Of course, besides zero-phase band-pass filtering, other filtering processing modes can be adopted, as long as signals near the ultrasonic center frequency are reserved, and low-frequency direct-current bias signals and high-frequency noise signals are filtered.
Imaging by using the acquired raw data, and firstly, dividing an imaging area. And selecting a proper size to subdivide the grids according to the size of an imaging area, and then calculating the influence of the transmitting array elements in each grid on the grids by using the acquired original echo data. Theoretically, the more the number of the meshes to be subdivided is, the higher the resolution is, but due to the influence of diffraction limit, if the number of the meshes to be subdivided is too large, the calculation amount is increased, but the imaging effect is not effectively improved, so that a proper mesh size needs to be selected. The values of M and N are related to the size of the imaging area, where M is the length of the imaging area divided by Δ, N is the width of the imaging area divided by Δ, and Δ is the preset side length of the square imaging point; for example, when the size of the imaging range is 100mm × 100mm, the size of each imaging point is set to 0.1mm, and M and N each take the value of 100/0.1 — 1000.
Every net is as an imaging point, adopts synthetic aperture's mode to calculate the value of imaging point, adds the distance of launching array element to the imaging point and the distance of receiving array element to the imaging point, divides by the sound velocity again, can obtain the time of sound wave signal transmission, can find the position of the sampling point that corresponds on the corresponding scan line according to this time. Assuming that the C-type probe has H array elements in total, the transmitting array elements and L array elements on the left and right of the transmitting array elements are selected as receiving apertures, for each transmitting array element, the echo data of the receiving array element has 2L +1 scanning lines in total, the position of data for 2L +1 times needs to be calculated, and for data acquired at one time, namely data transmitted by H array elements in sequence, the position of data for (2L +1) x H times needs to be calculated. And aligning and adding (2L +1) multiplied by H scanning lines according to the calculated data position to obtain final one-line data, and finding the position of a final imaging point in the line data to obtain the value of the point. The calculation process can be expressed by formula (1) and formula (2).
Wherein I (t) is the value of the imaging point. A (t)i,j) I is the data of the scanning line, i is the transmitting array element, and j is the receiving array element. The imaging area is set as an XZ plane, the moving direction of the probe is set as a Y plane, and (x, z) are coordinates of an imaging point (xi,zi) Is the coordinates of the transmitting array element, (x)j,zj) Is the receive array element coordinate, c is the speed of sound (speed of sound c may preferably be soft tissue speed of sound, i.e., 1540m/s), ti,jIs the calculated delay time. And finally obtaining matrix data which can be directly used for reconstructing an image by calculating all imaging points.
If the imaging area is divided into M × N grids, the values of M × N imaging points can be calculated in this manner.
Envelope detection, log compression, grey scale mapping and image display can then be performed in a manner known in the art, for example:
and detecting the upper envelope of the detected signal by envelope detection, and extracting low-frequency components carried in the echo signal, namely the information of the detected object. The envelope detection method used in the system is a Hilbert transform method, the Hilbert transform is a classical method for solving signal envelope, an orthogonal signal of an original signal is obtained by the original signal through the Hilbert transform, the original signal is used as a real part, a signal obtained through the Hilbert transform is used as an imaginary part to construct a complex signal, and the modulus of the complex signal is the envelope of a required real signal.
Log compression takes the log base 10 of the original signal and multiplies it by a multiple of 20 in dB. After taking the logarithm, the dynamic range of the echo can be adjusted to obtain the best real-time imaging effect, and is generally adjusted to 40dB or 60dB, and the smaller the value, the higher the contrast is. In a specific method, taking 60dB as an example, the maximum value of the signals is mapped to 60dB, and signals 60dB smaller than the maximum signal and smaller signals are mapped to 0 dB.
The grayscale mapping uses a simple linear mapping, i.e. proportionally maps the weakest signal to 0 and the strongest signal to 255.
The data after the gray mapping can be directly displayed. For example, a high resolution two dimensional ultrasound image can be obtained by directly calling the imaging function in MATLAB.
Further, the operation can be repeated in a translational manner to perform the ultrasonic imaging of the next section. If the probe is translated K times, K M × N matrix data can be obtained. K high-resolution two-dimensional ultrasound images can be reconstructed. And inputting the K matrix data into three-dimensional image reconstruction software, such as ImageJ software and the like, so that the three-dimensional image can be directly obtained.
It will be understood by those skilled in the art that the foregoing is only a preferred embodiment of the present invention, and is not intended to limit the invention, and that any modification, equivalent replacement, or improvement made within the spirit and principle of the present invention should be included in the scope of the present invention.
Claims (10)
1. A synthetic aperture imaging method based on a C-type probe is characterized by comprising the following steps:
(1) collecting original data:
numbering array elements in the C-shaped probe from 1 to H in a clockwise direction or a counterclockwise direction, wherein the array elements in the C-shaped probe are uniformly distributed on a C-shaped circular arc or a C-shaped elliptical arc, and H is the total number of the array elements in the C-shaped probe; then, starting to transmit ultrasonic signals from the array element numbered as 1 until the array element numbered as H; when each array element transmits an ultrasonic signal, each array element in the C-shaped probe receives and acquires the ultrasonic signal to obtain original echo data;
and, the space position of the C-type probe is kept stable when transmitting and receiving signals;
(2) data preprocessing:
for the original echo data obtained in the step (1), as the transmitting array elements are sequentially changed from the array element numbered 1 to the array element numbered H, for each transmission, the array element number of the transmitting array element at the time of the transmission is recorded as i,
if i satisfies 1 and L, intercepting and preprocessing corresponding echo data, and only reserving ultrasonic signals with serial numbers received and collected by (2i-1) array elements in total of 1, 2, … …, i, (i +1), … … and (2 i-1);
if i satisfies L < i < (H-L +1), intercepting and preprocessing corresponding echo data, and only reserving ultrasonic signals received and collected by (i-L), (i-L +1), … …, (i-1), i, (i +1), … …, (i + L-1) array elements in total (2L +1) in number;
if i is more than or equal to (H-L +1) and less than or equal to i, intercepting and preprocessing corresponding echo data, and only reserving ultrasonic signals received and collected by (2H-2i +1) array elements with serial numbers of (2i-H), (2i-H +1), … …, i, … … and H;
therefore, the interception preprocessing is completed on the whole original echo data; wherein L is a preset positive integer, and L satisfies that H/9 is more than or equal to L and is less than or equal to H/7;
(3) and (3) filtering treatment:
filtering the echo data obtained in the step (2) after the interception preprocessing is completed to obtain a filtered signal;
(4) image reconstruction:
firstly, gridding an imaging area, wherein the plane of the imaging area coincides with the plane of a C-shaped circular arc or a C-shaped elliptical arc of the C-shaped probe, and the imaging area is gridded according to a rectangular coordinate to be divided into M multiplied by N grids; m, N are preset positive integers;
then, focusing the filtered signals obtained in the step (3) by imaging points based on the synthetic aperture focusing technical principle, namely, respectively taking each grid area as an imaging point, and calculating the influence of all transmitting array elements on the imaging point; specifically, for the influence of a certain transmitting array element on the imaging point, the echo data corresponding to the imaging point is selected from the echo data corresponding to the transmitting array element according to the delay time; thus, for all transmitting array elements, all the obtained echo data corresponding to the imaging point are superposed, and then the data value of the imaging point can be obtained through calculation;
after the data value calculation is completed for all grid areas, an MXN matrix data value can be obtained, and then the matrix data value is subjected to envelope detection, logarithmic compression and gray mapping, so that an image of a section can be reconstructed;
in the step (4), the data value calculation of any imaging point satisfies the following conditions:
wherein, I (t) is the data value of the imaging point; i corresponds to the transmitting array element and is numbered for the transmitting array element; j corresponds to the receiving array element and is the number of the receiving array element; the plane of the imaging area is the XZ plane of the rectangular space coordinate system, and (x, z) are the space coordinates of the imaging point, and (x)i,zi) Is the space coordinate of the transmitting array element with array element number i, (x)j,zj) Is the spatial coordinate of the receiving array element with array element number j; c is the speed of sound; t is ti,jAnd calculating the delay time when the array element with the array element number i is used as a transmitting array element and the array element with the array element number j is used as a receiving array element.
2. A method for type-C probe based synthetic aperture imaging as defined in claim 1 further comprising the steps of:
(5) three-dimensional image reconstruction:
translating the C-shaped probe, updating the spatial position of the C-shaped probe, and repeating the operations from the step (1) to the step (4) to reconstruct an image of a new section; the translation-repeated operation is carried out for multiple times, and images of multiple sections can be obtained; based on the images of the sections, a three-dimensional image can be reconstructed.
3. The method of claim 1, wherein in step (4), C is 1540 m/s.
4. The method for forming synthetic aperture based on C-type probe according to claim 2, wherein in the step (5), the translation length of each translation is 1-5 mm.
5. The method for C-probe-based synthetic aperture imaging according to claim 4, wherein in the step (5), the direction of translation is perpendicular to the plane of the C-arc or C-ellipse of the C-probe.
6. The method for C-probe based synthetic aperture imaging according to claim 1, wherein in step (1), the receiving and acquiring ultrasound signals are in particular receiving and acquiring ultrasound reflected signals.
7. The method of type C probe-based synthetic aperture imaging according to claim 1, wherein H is an integer greater than or equal to 1024; the arc length of the C-shaped arc or the C-shaped elliptic arc of the C-shaped probe is 300 mm to 350 mm, and the curvature radius is 350 mm to 400 mm.
8. The method for forming synthetic aperture based on type-C probe according to claim 1, wherein in step (2), L is equal to an integer rounded by H/8.
9. The method for forming a C-type probe-based synthetic aperture according to claim 1, wherein in the step (4), M is a value obtained by dividing the length of the imaging region by Δ, and N is a value obtained by dividing the width of the imaging region by Δ, where Δ is a preset side length of a square imaging point.
10. The method for forming a synthetic aperture based on a type C probe according to claim 9, wherein in the step (4), Δ ═ 0.1 mm.
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