CN116077099A - Ultrasonic CT (computed tomography) reflection imaging method based on annular array multi-subarray rapid image reconstruction - Google Patents
Ultrasonic CT (computed tomography) reflection imaging method based on annular array multi-subarray rapid image reconstruction Download PDFInfo
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Abstract
The invention belongs to the technical field of medical ultrasonic imaging, and in particular relates to an ultrasonic CT (computed tomography) reflection imaging method based on annular array multi-subarray rapid image reconstruction, which comprises the following steps of: s1, placing a target to be detected in a piezoelectric ultrasonic transducer array of ultrasonic CT, transmitting an ultrasonic pulse signal through a first sub-aperture, and receiving the ultrasonic pulse signal; then transmitting an ultrasonic pulse signal through the second sub-aperture, and receiving a echo signal; repeating the sending and receiving processes until all sub-apertures are sent and received; s2, carrying out beam synthesis processing on echo signals received by array elements of all sub-apertures in the step S1 to form a scanning line, and obtaining a plurality of scanning lines; preprocessing each scanning line; s3, performing scan conversion treatment on each preprocessed scanning line, and then performing ultrasonic image reconstruction according to the corresponding steering angle of each scanning line to obtain an ultrasonic CT image. The invention can realize quick image and improve imaging efficiency.
Description
Technical Field
The invention belongs to the technical field of medical ultrasonic imaging, and particularly relates to an ultrasonic CT (computed tomography) reflection imaging method based on annular array multi-subarray rapid image reconstruction.
Background
Ultrasonic CT imaging refers to a technique that reconstructs internal (cross-sectional) information of an object from data detected from outside the object. Early studies of this technique were entirely mimicking X-rays, i.e., assuming that ultrasound waves, like X-rays, propagate in a straight line inside an object, and then reconstruct sound velocity (refractive index) or absorption characteristic parameters inside the object using time delay or amplitude attenuation between a transmitter to a receiver. In fact, however, the ultrasonic waves have obvious diffraction characteristics, and refraction and diffraction phenomena at the interface of the object to be measured are obvious, so that the propagation path is complex.
On the basis of not damaging the internal structure of the measured object, the ultrasonic CT measures projection data of the object through ultrasonic equipment, and a two-dimensional or three-dimensional ultrasonic image can be reconstructed by using the data. The ultrasonic CT detection technology has the advantages of good directivity, low price, no harm to human body, convenient carrying of equipment and the like. Therefore, irradiation of an object with ultrasonic waves as an emission source instead of X-rays has been one of new targets pursued by researchers in the field of ultrasonic application. There are two modes of ultrasonic CT imaging, reflective imaging and transmissive imaging, and corresponding echo data is selected for image reconstruction according to different imaging modes.
The highest frequency of clinical ultrasound is a one-dimensional linear array ultrasound transducer and a two-dimensional area array ultrasound transducer. The linear array ultrasonic transducer has a simple structure, the configuration cost of equipment is low, the control of ultrasonic sound beams is easier in programming, but the resolution of an image formed by the linear array is anisotropic, and echoes of a deeper region are gradually attenuated in the propagation process, so that the image quality is limited by the imaging position and the depth thereof, and the transverse resolution is obviously lower than the axial resolution. Furthermore, the application of linear array ultrasound transducers to medical imaging requires reliance on the techniques of medical personnel, which can cause unnecessary interference. In the three-dimensional space, the deflection and the focusing of ultrasonic beams are commonly used for an area array ultrasonic transducer, but the area array ultrasonic transducer has more array elements, a sound beam control algorithm is complex, and the application cost is high.
The imaging quality of the traditional linear array-based ultrasonic CT technology is affected by the position and depth of a measured object, so that the imaging resolution is low, and the accuracy of diagnosis depends on the capability of a diagnostician to grasp an instrument and medical knowledge to a certain extent. For the detected body with a curved surface structure, such as breast, neck and the like, when the ultrasonic linear array is used for detection, uncomfortable extrusion is needed to a patient, signals in a gap area of an imaging surface can be lost while the linear array is moved, and interventional therapy is obviously limited by a planar sound image. The array elements based on the area array ultrasonic transducer have more array elements, the acoustic beam control algorithm is complex, and the application cost is high.
Compared with a linear array probe, the circular array probe can provide echo data of 360-degree omnibearing detection, and the resolution of images can be further improved and the imaging quality can be improved by processing the data. In addition, due to the special arrangement mode of the annular transducer array, any area inside the array is provided with detection array elements close to a medium, an isotropic high-resolution image of 360 degrees can be obtained by controlling beam forming, and the beam can be self-focused on a certain point, so that the imaging depth and the imaging position have little influence on the image quality, the technology of operators is not depended, and the diagnosis and treatment of diseases in clinic by doctors are facilitated. And the number of the ultrasonic transducer array elements needed by the ring array is smaller than that of the area array in a certain detection range, and the needed cost is low.
However, in the prior art, the data processing process of the ring array probe is complex, so that the imaging speed is low, and the application of the ring array probe in specific practice is greatly limited.
Disclosure of Invention
The invention overcomes the defects existing in the prior art, and solves the technical problems that: the ultrasonic CT reflection imaging method based on the annular array Multi-subarray rapid image reconstruction (Multi-Subarray of Circular Array and Fast Image Reconstruction, MS-CAFIR) is provided, and on the premise of improving the ultrasonic signal data processing efficiency, the power and the signal-to-noise ratio of ultrasonic signals are improved at the same time, so that the rapid image reconstruction of ultrasonic CT is realized.
In order to solve the technical problems, the invention adopts the following technical scheme: an ultrasonic CT reflection imaging method based on annular array multi-subarray rapid image reconstruction comprises the following steps:
s1, placing a target to be detected in a piezoelectric ultrasonic transducer array of ultrasonic CT, wherein the piezoelectric ultrasonic transducer array comprises a plurality of array elements which are uniformly distributed in a ring shape, transmitting ultrasonic pulse signals through a first sub-aperture, and receiving the ultrasonic pulse signals through the same sub-aperture; then transmitting ultrasonic pulse signals through the second sub-aperture, and receiving echo signals through the same sub-aperture; repeating the sending and receiving processes until all sub-apertures are sent and received; the sub-apertures comprise a plurality of adjacent array elements, and the number of the array elements included in each sub-aperture is the same;
s2, carrying out beam synthesis processing on echo signals received by array elements of all sub-apertures in the step S1 to form a scanning line, and obtaining a plurality of scanning lines; preprocessing each scanning line;
s3, performing scan conversion treatment on each preprocessed scanning line, and then performing ultrasonic image reconstruction according to the corresponding steering angle of each scanning line to obtain an ultrasonic CT image.
An array element is arranged between two adjacent sub-apertures.
In the step S1, when the ultrasonic pulse signal is transmitted through each sub-aperture, the ultrasonic pulse signal is performed in a clockwise or counterclockwise direction.
In the step S2, the specific steps of preprocessing each scan line are as follows:
s201, windowing is carried out on the beginning part of each scanning line;
s202, performing time gain compensation on each windowed scanning line;
s203, performing Gaussian filtering processing on the data subjected to time gain compensation in a frequency domain;
s204, performing Hilbert transform on the Gaussian filtered data;
s205, compressing the data after Hilbert transformation.
In the step S202, the formula of the time gain compensation is:
p＝p 0 e -αfd ；
wherein p is the sound pressure value after TGC compensation, p 0 Is the initial sound pressure value, α is the attenuation coefficient, f is the transmission frequency, and d is the total distance.
In the step S2, when beam synthesis is performed, delay and weight are calculated according to the focusing distance and amplitude apodization setting of the ultrasonic probe.
The object to be measured is placed in a tank containing medium water.
The step S3 further includes a step of converting the scan line from polar coordinates to cartesian coordinates and performing interpolation processing.
Compared with the prior art, the invention has the following beneficial effects:
1. the invention provides an ultrasonic CT (computed tomography) reflection imaging method based on annular array multi-subarray rapid image reconstruction, which has obvious improvement in the aspects of sound wave power and image signal-to-noise ratio compared with other ultrasonic reflection reconstruction algorithms (such as SAFT and the like). Because the annular array has self-focusing property, the imaging method of the invention avoids beam defocusing on the premise of transmitting and receiving a plurality of array elements simultaneously, and obtains the advantages of short image reconstruction time and high reconstruction resolution on the basis of reducing the complexity of the system.
2. The invention combines the receiving and transmitting control mode of multi-array element subarray simultaneous receiving and transmitting to furthest exert the benefit of short image reconstruction time, and can clearly image only half of all data after collecting ultrasonic echo signals, and reconstruct a high-resolution reflection image within 10 seconds.
3. The capability of reconstructing high-quality images of the invention is proved by research and experimental verification through simulation experiments on mammary gland bionic body models. The bionic body model is derived from KS105 series mammary gland ultrasonic tomography simulated tissue ultrasonic body models which are specially used for circular array scanning imaging and are developed and produced by acoustic research institute of China academy of sciences. The statistical information of the radio frequency data of the bionic breast phantom is obtained from a 256-channel Verasonics acquisition system (Verasonics Inc., kirkland, WA, USA), so that a good imaging effect is achieved.
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Fig. 1 is a schematic flow chart of an ultrasonic CT reflection imaging method based on a ring array multi-subarray rapid image reconstruction according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of the principle of ultrasonic emission in an embodiment of the present invention;
fig. 3 is a diagram of experimental results of a simulation experiment, including a breast biomimetic phantom (left), a schematic view of the size and distribution of targets in the breast biomimetic phantom (middle) and an ultrasonic CT reconstructed image of the present invention (right).
Detailed Description
For the purpose of making the objects, technical solutions and advantages of the embodiments of the present invention more clear, the technical solutions in the embodiments of the present invention will be clearly and completely described below, and it is apparent that the described embodiments are some embodiments of the present invention, but not all embodiments; all other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
As shown in fig. 1, the embodiment of the invention provides an ultrasonic CT reflection imaging method based on ring array multi-subarray rapid image reconstruction, which comprises the following steps:
s1, placing a target to be detected in a piezoelectric ultrasonic transducer array of ultrasonic CT, wherein the piezoelectric ultrasonic transducer array comprises a plurality of array elements which are uniformly distributed in a ring shape, transmitting ultrasonic pulse signals through a first sub-aperture, and receiving the ultrasonic pulse signals through the same sub-aperture; then transmitting ultrasonic pulse signals through the second sub-aperture, and receiving echo signals through the same sub-aperture; repeating the sending and receiving processes until all sub-apertures are sent and received; the sub-apertures comprise a plurality of adjacent array elements, and each sub-aperture comprises the same number of array elements.
Further, in this embodiment, the preferred emission method is: an array element is arranged between two adjacent sub-apertures. Assuming that the piezoelectric ultrasonic transducer array comprises 256 piezoelectric ultrasonic transducer array elements, which are respectively named as 1-256 array elements in the clockwise direction, assuming that each sub-aperture comprises 5 array elements, the first sub-aperture comprises 1-5 array elements, the second sub-aperture comprises 2-6 array elements, the third sub-aperture comprises 2-7 array elements, and so on, and the 256 th sub-aperture comprises 256 and 1-4 array elements.
Specifically, in the step S1, when the ultrasonic pulse signal is transmitted through each sub-aperture, the ultrasonic pulse signal is performed in a clockwise or counterclockwise direction.
Specifically, the object to be measured is disposed in a water tank containing medium water.
S2, carrying out beam synthesis processing on echo signals received by array elements of all sub-apertures in the step S1 to form a scanning line, and obtaining a plurality of scanning lines; each scan line is preprocessed.
In the step S2, when beam synthesis is performed, delay and weight are calculated according to the focusing distance and amplitude apodization setting of the ultrasonic probe.
The specific calculation formula of the delay is as follows.
When N is an odd number:
when N is an even number, the number,
wherein t is nf The delay time of the nth array element during the focusing of the annular array is represented, F represents the focal length, r represents the radius of curvature of the annular array, d represents the center distance of the array elements, c represents the sound velocity of ultrasonic waves in a medium, and t 0 The time constant is expressed, and the beam deflection angle is expressed. By using the time delay formula, the target to be detected can be accurately determined in the annular array areaBit and focus, thereby enabling high resolution imaging based on a circular array.
The weights are achieved by employing amplitude apodization on the signal using a suitable window function to effectively reduce the main lobe width and suppress the sidelobe levels.
In the step S2, the specific steps of preprocessing each scan line are as follows:
s201, windowing is carried out on the beginning part of each scanning line; since the ultrasonic transducer is allowed to simultaneously transmit and receive signals at any time in the actual data acquisition process, after beam synthesis, windowing processing is performed on the beginning part of each scanning line, so that interference of the input signals on stored echo data can be deleted.
S202, performing Time Gain Compensation (TGC) on each scanning line after windowing; in the step S202, the formula of the time gain compensation is:
p＝p 0 e -αfd ； (3)
wherein p is the sound pressure value after TGC compensation, p 0 Is the initial sound pressure value, α is the attenuation coefficient, f is the transmission frequency, and d is the total distance.
Due to attenuation (absorption and scattering) and focusing effects of the ultrasonic waves, part of the energy is lost when the acoustic waves generated by the ultrasonic transducer propagate in the medium. Thus, reflections from deeper tissue features may appear weaker in the echo signal. Thus, applying TGC compensation to the echo signals may increase the energy of the echo signals.
S203, performing Gaussian filtering processing on the data subjected to time gain compensation in a frequency domain.
In this embodiment, the scanning line is subjected to the filtering process using a gaussian function centered on the transmission frequency. This step filters through the designated center frequency and fractional bandwidth, reducing the effects of noise outside the transmit frequency range.
S204, performing Hilbert transform on the data after Gaussian filtering processing. By extracting the signal envelope using the hilbert transform, high frequency variations in the scan line are eliminated during demodulation of the envelope detection.
S205, compressing the data after Hilbert transformation.
The dynamic range of the processed scan lines typically exceeds the gray scale range that a computer display can display or visually perceive. To reduce this dynamic range, the scan lines are logarithmically compressed using a normalized compression ratio, typically compressing the dynamic range of the echo signal to around the range that the display can receive (40 dB).
S3, performing scan conversion treatment on each preprocessed scanning line, and then performing ultrasonic image reconstruction according to the corresponding steering angle of each scanning line to obtain an ultrasonic CT image.
The processed scan lines may be spatially remapped to provide an image resolution suitable for display. Because the scanning lines are formed under different steering angles, the scanning lines are firstly converted from polar coordinates to Cartesian coordinates and interpolation processing is carried out; then, reconstructing an ultrasonic image, and finally reconstructing an ultrasonic CT image with high contrast, high contrast-to-noise ratio and low side lobe level.
In order to prove the imaging effect of the imaging method, an annular array ultrasonic CT system consisting of 256 piezoelectric ultrasonic transducer array elements is taken as an example, wherein the diameter of the piezoelectric ultrasonic transducer array is 200mm, and the interval between the array elements is 2.454mm. The imaging subject is placed in the center of an annular array immersed in water and then echo data received by ultrasound reflection is acquired. As shown in FIG. 3, the adopted imaging object is a bionic body model, and the bionic body model is derived from KS105 series mammary gland ultrasonic tomography simulated tissue ultrasonic body model which is specially used for circular array scanning imaging and developed and produced by the acoustic research institute of China academy of sciences, and the obtained result proves that the imaging method can quickly reconstruct a high-resolution reflection image and has better imaging effect.
Finally, it should be noted that: the above embodiments are only for illustrating the technical solution of the present invention, and not for limiting the same; although the invention has been described in detail with reference to the foregoing embodiments, it will be understood by those of ordinary skill in the art that: the technical scheme described in the foregoing embodiments can be modified or some or all of the technical features thereof can be replaced by equivalents; such modifications and substitutions do not depart from the spirit of the invention.
Claims (8)
1. The ultrasonic CT reflection imaging method based on the annular array multi-subarray rapid image reconstruction is characterized by comprising the following steps of:
s1, placing a target to be detected in a piezoelectric ultrasonic transducer array of ultrasonic CT, wherein the piezoelectric ultrasonic transducer array comprises a plurality of array elements which are uniformly distributed in a ring shape, transmitting ultrasonic pulse signals through a first sub-aperture, and receiving the ultrasonic pulse signals through the same sub-aperture; then transmitting ultrasonic pulse signals through the second sub-aperture, and receiving echo signals through the same sub-aperture; repeating the sending and receiving processes until all sub-apertures are sent and received; the sub-apertures comprise a plurality of adjacent array elements, and the number of the array elements included in each sub-aperture is the same;
s2, carrying out beam synthesis processing on echo signals received by array elements of all sub-apertures in the step S1 to form a scanning line, and obtaining a plurality of scanning lines; preprocessing each scanning line;
s3, performing scan conversion treatment on each preprocessed scanning line, and then performing ultrasonic image reconstruction according to the corresponding steering angle of each scanning line to obtain an ultrasonic CT image.
2. The ultrasonic CT reflection imaging method based on the annular array multi-subarray rapid image reconstruction of claim 1, wherein an array element is arranged between two adjacent subarrays.
3. The method according to claim 1, wherein in the step S1, the ultrasonic pulse signal is transmitted through each sub-aperture in a clockwise or counterclockwise direction.
4. The ultrasonic CT reflection imaging method based on the rapid image reconstruction of the annular array multi-subarray according to claim 1, wherein in the step S2, the specific steps of preprocessing each scan line are as follows:
s201, windowing is carried out on the beginning part of each scanning line;
s202, performing time gain compensation on each windowed scanning line;
s203, performing Gaussian filtering processing on the data subjected to time gain compensation in a frequency domain;
s204, performing Hilbert transform on the Gaussian filtered data;
s205, compressing the data after Hilbert transformation.
5. The ultrasonic CT reflectometry imaging method based on the rapid image reconstruction of a plurality of subarrays of the annular array of claim 1, wherein in the step S202, the formula of the time gain compensation is:
p＝p 0 e -αfd ；
wherein p is the sound pressure value after TGC compensation, p 0 Is the initial sound pressure value, α is the attenuation coefficient, f is the transmission frequency, and d is the total distance.
6. The ultrasonic CT reflection imaging method based on the rapid image reconstruction of the annular array multi-subarray according to claim 1, wherein in the step S2, the delay and the weight are calculated according to the focusing distance and the amplitude apodization setting of the ultrasonic probe when the beam synthesis is performed.
7. The ultrasonic CT reflectometry imaging method based on the rapid image reconstruction of a plurality of subarrays of annular arrays according to claim 1, wherein the object to be measured is disposed in a tank containing dielectric water.
8. The method of claim 1, further comprising the step of converting the scan line from polar coordinates to cartesian coordinates and performing interpolation processing in step S3.
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| CN117770870A (en) * | 2024-02-26 | 2024-03-29 | 之江实验室 | Ultrasonic imaging method and device based on double-linear-array ultrasonic field separation |
| CN117770870B (en) * | 2024-02-26 | 2024-05-10 | 之江实验室 | Ultrasonic imaging method and device based on double-linear-array ultrasonic field separation |
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