Three-dimensional full-focusing ultrasound imaging method based on frequency wavenumber domain row and column addressing array

Abstract

This invention provides a three-dimensional full-focusing ultrasound imaging method based on a frequency-wavenumber domain row-column addressable array, belonging to the field of three-dimensional full-focusing ultrasound. The method includes the following steps: using a row-column addressable array with a total of N+N transmitting elements to perform ultrasonic scanning on a medium to obtain acquired signals; based on the acquired signals, performing spatial sampling to obtain a three-dimensional voxel network; using a frequency-wavenumber domain method to beamform the radio frequency data corresponding to the three-dimensional voxel network; and performing envelope processing on the beamformed data to form a three-dimensional image. This invention's beamforming method for three-dimensional full-focusing ultrasound imaging based on a frequency-wavenumber domain row-column addressable array significantly reduces the number of elements and beamforming channels required for three-dimensional imaging by using a row-column addressable array, while providing a larger imaging area. The imaging process employs full-matrix capture to obtain high-resolution images, and the frequency-wavenumber domain beamforming method significantly shortens the imaging time.

Description

Technical Field

[0001] This invention belongs to the field of three-dimensional full-focus ultrasound, specifically relating to a three-dimensional full-focus ultrasound imaging method based on a frequency wavenumber domain row and column addressing array. Background Technology

[0002] Ultrasound imaging is widely used in clinical practice due to its advantages such as convenience, safety, low cost, and non-invasiveness. [1] Traditional ultrasound imaging is primarily used for two-dimensional cross-sections of tissues, while three-dimensional (3D) imaging provides a more comprehensive three-dimensional view, clearly presenting the spatial relationships of organs and structures, and significantly improving diagnostic accuracy. One method to achieve 3D imaging is to perform longitudinal scanning by mechanically moving a one-dimensional array. Although simple to operate, this method is limited in resolution along the direction of movement, making it difficult to achieve rapid 3D imaging. [2] Another approach is to use an array containing N. 2 The channel is a matrix array, where N is the number of array elements in the longitudinal or transverse direction. Each array element is electronically controlled to achieve dynamic focusing in each direction. [3] Compared to one-dimensional arrays using mechanical scanning, matrix arrays offer significant advantages in imaging speed and vertical resolution. However, matrix arrays require a large number of independent electronic channels, increasing hardware complexity and cost, and the fabrication of high-density, independently interconnected piezoelectric elements is challenging. [4] .

[0003] Researchers have proposed several techniques to reduce the number of electronic channels in traditional 3D ultrasound imaging systems. Multiplexers can significantly reduce hardware complexity and cost while saving power. [5] However, this leads to increased noise, decreased temporal resolution, and reduced sampling accuracy. Microwave beamformers offer significant advantages in reducing data transmission load, improving system scalability, and enhancing real-time imaging performance. [6] However, this reduces imaging flexibility and increases probe complexity and cost. Therefore, sparse arrays offer an effective alternative, maintaining a high frame rate while reducing the number of channels. [7] However, increasing the effective spacing between array elements may lead to an increase in sidelobe levels. [8] .

[0004] Row-column-addressed (RCA) arrays have proven to be a reliable strategy for three-dimensional ultrasound imaging. An RCA consists of two orthogonally arranged, slender one-dimensional arrays, reducing the number of channels to 2N, which facilitates three-dimensional ultrasound imaging. Sauvage et al. utilized an orthogonal plane wave composite strategy and row-column addressing to achieve four-dimensional (4D) ultra-high-speed power Doppler imaging. [9]Dong et al. proposed a three-dimensional acoustic radiation force shear wave elastic imaging technique based on a two-dimensional addressable array.

[10] Furthermore, Sauvage et al. were the first to achieve four-dimensional functional in vivo ultrasound imaging of the whole rat brain using row-column addressing arrays.

[11] .

[0005] Frequency-wavenumber imaging algorithms have proven effective in reducing computation time. This method converts the received ultrasonic echo (RF) signal from the spatiotemporal domain to the frequency-wavenumber domain and generates a focused image using a migration factor. Stolt et al. first applied this technique to seismic imaging.

[12] Treating the reflector in the medium as the explosion source, imaging the reflector in the medium is equivalent to solving the Helmholtz equation, thereby determining the sound field at the time of the explosion.

[13] Subsequently, frequency-wavenumber imaging methods were used in monostatic synthetic aperture radar systems.

[14] Callow et al. further improved it to a bistatic SAR.

[15] Hunter et al. proposed a Fourier full-matrix imaging wavenumber algorithm suitable for ultrasonic nondestructive testing and evaluation, which improves the point spread function to enhance image quality.

[16] Frequency-wavenumber domain-based methods have been extensively studied in the field of medical imaging. Garcia proposed a frequency-plane wave imaging migration method based on an explosion reflection model, which achieves efficient computation using Fast Fourier Transform (FFT) while maintaining a high contrast-to-noise ratio (CNR) and lateral resolution.

[17] Moghimirad et al. introduced a virtual source to realize an efficient Fourier beamforming algorithm for multi-site synthetic aperture ultrasound imaging.

[18] Albulayli et al. modified the Stolt algorithm and the tilt stacking depth migration algorithm under the zero offset constant velocity assumption to make them suitable for plane wave ultrasound imaging.

[19] Although this method improves computational efficiency when applied to linear arrays and fully addressed two-dimensional matrix array probes, it has not yet been applied to three-dimensional ultrasound imaging of row and column addressed arrays.

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[0015]

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[0022]

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[0023]

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[0024]

[19] M.Albulayli and D.Rakhmatov, "Fourier domain depth migration for plane-wave ultrasound imaging," IEEE Trans.Ultrason.Ferroelectr.Freq.Control, vol.65, no.8, pp.1321-1333, 2018. Summary of the Invention

[0025] This invention is made to solve the above-mentioned problems, and aims to provide a three-dimensional full-focus ultrasound imaging method based on a frequency wavenumber domain row and column addressing array.

[0026] This invention provides a three-dimensional full-focus ultrasound imaging method based on a frequency wavenumber domain row-column addressable array, which is characterized by shortening the computation time of three-dimensional full-focus ultrasound imaging. The method includes the following steps: S10, using a row-column addressable array with a total of N+N transmitting elements to perform ultrasonic scanning on the medium to obtain the acquired signal; S20, performing spatial sampling based on the acquired signal to obtain a three-dimensional voxel network; S30, using a frequency wavenumber domain method to form the radio frequency data beam corresponding to the three-dimensional voxel network; S40, performing envelope processing on the data after beamforming in step S30 to form a three-dimensional image.

[0027] The three-dimensional full-focus ultrasound imaging method based on frequency wavenumber domain row and column addressing array provided by the present invention may also have the following features: wherein step S10 includes the following sub-steps: S11, a single element of the row array emits an ultrasonic signal into the medium at a predetermined center frequency, and acquires the acquisition signal corresponding to the emitting element of the row array through N receiving elements of the column array; S12, a single element of the column array emits an ultrasonic signal into the medium at the same center frequency as in step S11, and acquires the acquisition signal corresponding to the emitting element of the column array through N receiving elements of the row array.

[0028] The three-dimensional full-focus ultrasound imaging method based on frequency wavenumber domain row and column addressing array provided by the present invention may also have the following features: in step S11, the N transmitting elements of the row array are emitted sequentially in a cyclic manner, and in step S12, the N transmitting elements of the column array are emitted sequentially in a cyclic manner, and the N elements of the row array and the column array are all effective elements.

[0029] The three-dimensional full-focus ultrasound imaging method based on frequency wavenumber domain row and column addressing array provided by the present invention may also have the following features: in step S20, the imaging region is spatially discretized into a three-dimensional voxel grid M×N×H, and the voxel grid is used as the voxel discrete points for imaging to determine the target region.

[0030] The three-dimensional full-focus ultrasound imaging method based on frequency wavenumber domain row and column addressing array provided by the present invention may also have the following features: in step S20, the resolution of the discretized three-dimensional voxel grid is determined according to the probe settings of the row and column addressing array, the axial space between continuous nodes of the three-dimensional voxel grid is set to λ / 4, the transverse and longitudinal scanning is set to λ / 2, and λ is the ultrasound length.

[0031] The three-dimensional full-focus ultrasound imaging method based on a frequency-wavenumber domain row-column addressing array provided by this invention may also have the following feature: Step S30 includes the following sub-steps: S31, using a 3D fast Fourier transform, the backscattered signal RF(u,v,t) in the time-space domain corresponding to the three-dimensional voxel network is converted into a discrete signal RF(k) in the frequency-wavenumber domain. u ,k v ,ω), u is ultrasonic emission, v is backscattering, t is time, k u k is the wavenumber of the ultrasonic emission. v ω is the wavenumber of the backscattered signal, and ω is the frequency; S32, obtain the discrete signal RF(k u ,k v A one-dimensional slice of ω, according to k X =k u k Y =k v , Calculate k for each wavenumber sampling point u and k v wave number k, k X k Y and k Z These are the wavenumbers of the scattering points in three directions; S33, in a one-dimensional slice RF(k u ,k v ,ω) ku，kv＝const Performing the Stolt mapping yields the wavenumber function f(k). X ,k Y ,k Z The ultrasound image is then transformed into the spatial domain using a three-dimensional inverse Fourier transform.

[0032] The role and effect of invention

[0033] The three-dimensional full-focus ultrasound imaging method based on a frequency wavenumber domain row and column addressing array according to the present invention includes the following steps: S10, using a row and column addressing array with a total number of N+N transmitting elements to perform ultrasonic scanning on the medium to obtain the acquired signal; S20, performing spatial sampling based on the acquired signal to obtain a three-dimensional voxel network; S30, using a frequency wavenumber domain method to form a radio frequency data beam for the three-dimensional voxel network; S40, performing envelope processing on the data after beamforming in step S30 to form a three-dimensional image.

[0034] Therefore, the three-dimensional full-focusing ultrasound imaging method based on frequency-wavenumber domain row and column addressing array of the present invention significantly reduces the number of components and beamforming channels required for three-dimensional imaging through row and column addressing array, while providing a larger imaging area. The imaging process uses full matrix capture to obtain high-resolution images, and the imaging time is greatly shortened through frequency-wavenumber domain beamforming method. Attached Figure Description

[0035] Figure 1 This is a flowchart of a three-dimensional full-focus ultrasound imaging method based on a frequency wavenumber domain row and column addressing array according to an embodiment of the present invention;

[0036] Figure 2 This is a schematic diagram of the receiving of a transducer row-column addressing array according to an embodiment of the present invention;

[0037] Figure 3 This is a flowchart illustrating the frequency wavenumber domain method according to an embodiment of the present invention;

[0038] Figure 4 This is a reconstructed simulation point target image according to an embodiment of the present invention;

[0039] Figure 5 This is a reconstruction experimental phantom point target image according to an embodiment of the present invention;

[0040] Figure 6 This is a reconstruction experimental phantom cyst target image according to an embodiment of the present invention;

[0041] Figure 7 This is a reconstructed in vivo carotid artery image according to an embodiment of the present invention. Detailed Implementation

[0042] To make the technical means, creative features, objectives and effects of the present invention easy to understand, the following embodiments, in conjunction with the accompanying drawings, provide a detailed description of a three-dimensional full-focus ultrasound imaging method based on a frequency wavenumber domain row and column addressing array.

[0043] <Example>

[0044] Figure 1This is a flowchart of a three-dimensional full-focus ultrasound imaging method based on a frequency wavenumber domain row and column addressing array, according to an embodiment of the present invention.

[0045] like Figure 1 As shown, this embodiment provides a three-dimensional full-focus ultrasound imaging method based on a frequency wavenumber domain row and column addressing array, including the following steps:

[0046] Figure 2 This is a schematic diagram of the transducer row and column addressing array according to an embodiment of the present invention.

[0047] S10, adopts as follows Figure 2 The N+N row-column addressable array shown performs ultrasonic scanning on the medium to obtain the acquired signal, specifically including the following sub-steps:

[0048] S11, a single element of the row array transmits an ultrasonic signal into the medium at a predetermined center frequency, and acquires the corresponding acquisition signal of the transmitting element of the row array through the N receiving elements of the column array. The N transmitting elements of the row array transmit in sequence, and all N elements of the row array are effective elements.

[0049] S12, each element of the column array emits an ultrasonic signal into the medium at the same center frequency as in step S11, and acquires the corresponding acquisition signal of the transmitting element of the column array through the N receiving elements of the row array. The N transmitting elements of the column array emit in sequence, and all N elements of the column array are effective elements.

[0050] Specifically, in this embodiment, simulation is first performed, and the rationality of the method is verified based on the simulation results. Then, experiments are conducted on the phantom and in vivo.

[0051] The simulation experiment used three scattering points, each 0mm wide in both the horizontal and vertical directions, and uniformly distributed axially between 10mm and 30mm, with an amplitude of 1. Echo simulation data was obtained using the Verasonics multi-channel ultrasonic transmitter-receiver system simulation mode. The simulation parameters were as follows: transducer with 128+128 elements (N=128), center transmission frequency 6MHz, element spacing 0.2mm, element length 25.6mm, sound velocity 1540m / s, medium attenuation coefficient 0.5dB / [MHz·cm], and sampling frequency 25MHz.

[0052] In both phantom and in vivo experiments, the same parameters were used. Data were obtained by scanning a commercial phantom (Model 040GSE) using the Verasonics ultrasound experimental platform, and in vivo data were obtained by scanning the carotid arteries of healthy volunteers. Both experiments used the RC6gV row and column addressing probe with volumetric imaging capabilities.

[0053] S20. Based on the acquired signal, spatial sampling is performed to obtain a three-dimensional voxel network. Specifically, the imaging area is spatially discretized into a three-dimensional voxel grid M×N×H, and the voxel grid is used as the voxel discrete points for imaging to determine the target area.

[0054] The resolution of the discretized three-dimensional voxel mesh is determined according to the probe settings of the row and column addressing array. The axial space between continuous nodes of the three-dimensional voxel mesh is set to λ / 4, and the transverse and longitudinal scanning is set to λ / 2, where λ is the ultrasonic wave length.

[0055] Figure 3 This is a flowchart illustrating the frequency wavenumber domain method according to an embodiment of the present invention.

[0056] S30, utilizing such Figure 3 The frequency wavenumber domain method shown for beamforming radio frequency data corresponding to a three-dimensional voxel network specifically includes the following sub-steps:

[0057] S31, using 3D Fast Fourier Transform, the backscattered signal RF(u,v,t) in the time-space domain corresponding to the 3D voxel network is converted into a discrete signal RF(k) in the frequency-wavenumber domain. u ,k v ,ω), u is ultrasonic emission, v is backscattering, t is time, k u k is the wavenumber of the ultrasonic emission. v Let ω be the wavenumber of the backscattered wave and ω be the frequency.

[0058] S32, Obtain the discrete signal RF(k) u ,k v A one-dimensional slice of k, ω), according to the following formula: X =k u k Y =k v as well as Calculate k for each wavenumber sampling point u and k v wave number k,

[0059] Where, k X k Y and k Z These are the wavenumbers of the scattering points in three directions.

[0060] The derivation of Equation 1 in this step is as follows:

[0061] S32-1, According to Weil's identity, the Green's function of the wave field from the origin to a point (x,z) in a two-dimensional (2D) Cartesian coordinate system is expressed as:

[0062] in, The imaginary unit, It is the distance from the origin to any point in the sound field, k = ω / c is the wave number, c is the speed of sound in ultrasound, and k x and These are the wave numbers in the x and z directions, respectively.

[0063] S32-2, In 3D RCA imaging, an ultrasonic pulse emitted from an ultrasonic transducer element in a row-column addressed array located at (u,0,0) is reflected by a scatterer of intensity f(x,y,x), then backscattered, and recorded by a transducer element located at (0,v,0), where the half-space z>0 is defined as the imaging region. This process is described as follows:

[0064]

[0065] S32-3, receiving pulse echo data, is the response of all scattering points in all imaging areas, expressed as the following spatial integral:

[0066]

[0067] Clearly, the ultrasonic response at the scattering point is correlated with the RF data in the frequency-wavenumber domain, as shown in the following equation:

[0068]

[0069] This gives the relationship between RF data and free-space scattering points in the spectral domain, namely:

[0070]

[0071] S33, in a one-dimensional slice RF(k) u ,k v ,ω) ku,kv＝const Performing the Stolt mapping yields the wavenumber function f(k). X ,k Y ,k Z The ultrasound image is then transformed into the spatial domain using a three-dimensional inverse Fourier transform.

[0072] S40, the ultrasound image in step S33 is enveloped to form a three-dimensional image.

[0073] Figure 4 Figure 1 shows a reconstructed simulation point target image according to an embodiment of the present invention. Figure 2(a) is a three-dimensional image of the reconstructed simulation point target; Figure 3(b) is an axial two-dimensional slice with a depth of z = 25 mm; Figure 4(c) is a longitudinal two-dimensional section with y = 0 mm; and Figure 5(d) is a transverse two-dimensional section with x = 0 mm.

[0074] like Figure 4As shown, the frequency wavenumber domain method (RCA-FMC-fk) of this embodiment of the invention reconstructs a simulated 3D image of a point target, exhibiting small sidelobes. It also demonstrates excellent performance in artifact and sidelobe suppression. On a 2D cross-section with an axial z = 25 mm, the point target forms a cross shape, primarily due to the transmit-receive mode of the row-column addressing array. Clutter-induced artifacts are still present in Figures (b) and (c). The average full width at half maximum (FWHM) of the simulated point target is 0.34 ± 0.08 mm.

[0075] Figure 5 Figure 1 shows the reconstructed experimental phantom point target image according to an embodiment of the present invention. Figure 2(a) is a three-dimensional image of the reconstructed experimental phantom point target; Figure 3(b) is an axial two-dimensional cross-section with a depth of z = 20.5 mm; Figure 4(c) is a longitudinal two-dimensional cross-section with y = 0 mm; and Figure 5(d) is a transverse two-dimensional slice with x = 0 mm.

[0076] like Figure 5 As shown, the frequency wavenumber domain method (RCA-FMC-fk) of this invention clearly displays the line and cylinder in the three-dimensional image. The speckle background in the two-dimensional cross-sectional image is brighter and smoother, showing strong speckle preservation ability and effectively alleviating excessive speckle suppression. The average full width at half maximum (FWHM) of the phantom point target is 0.48 ± 0.08 mm.

[0077] Figure 6 Figure 1 shows a target image of a reconstructed experimental phantom cyst according to an embodiment of the present invention. Figure 2(a) is a three-dimensional image of the reconstructed experimental phantom cyst target; Figure 3(b) is an axial two-dimensional cross-section with a depth of z = 17 mm; Figure 4(c) is a longitudinal two-dimensional cross-section with y = 0 mm; and Figure 5(d) is a transverse two-dimensional cross-section with x = 0 mm.

[0078] like Figure 6 As shown, the frequency wavenumber domain method (RCA-FMC-fk) of this invention can clearly display the cyst target region when reconstructing a three-dimensional image. In Figure (a), noise and clutter interference are present inside the anechoic cyst, indicating that RCA-FMC-fk has limited ability to suppress artifacts. Although the method can detect the cyst target, its effect on reducing clutter is weak. The contrast ratio of the cyst target is 13.67, the contrast-to-noise ratio is 1.53, the speckle signal-to-noise ratio is 1.99, and the generalized contrast-to-noise ratio is 0.8371.

[0079] Figure 7 These are reconstructed in vivo carotid artery images according to an embodiment of the present invention. Figure (a) is a reconstructed three-dimensional image of the in vivo carotid artery; Figure (b) is a longitudinal two-dimensional cross-section with y = 0 mm; and Figure (c) is a transverse two-dimensional cross-section with x = 0 mm.

[0080] like Figure 7As shown, the three-dimensional reconstruction of the carotid artery using the frequency wavenumber domain method (RCA-FMC-fk) of an embodiment of the present invention displays the complete morphology of the carotid artery. In Figures (a) and (b), the cross-sections and longitudinal sections of the carotid artery are visible, indicating that RCA-FMC-fk is capable of generating ultrasound images of the target. However, the carotid artery is overwhelmed by noise, and its boundary with surrounding tissues is blurred, demonstrating its inadequacy in noise and clutter suppression. The contrast ratio of the carotid artery target is 13.26, the contrast-to-noise ratio is 1.00, the speckle signal-to-noise ratio is 1.30, and the generalized contrast-to-noise ratio is 0.7302.

[0081] Those skilled in the art should understand that this invention is not limited to the above embodiments. The embodiments and descriptions in the specification are merely illustrative of the principles of the invention. Various changes and modifications can be made to this invention without departing from its spirit and scope, and all such changes and modifications fall within the scope of the invention as claimed. The scope of protection of this invention is defined by the appended claims and their equivalents.

Claims

1. A three-dimensional full-focus ultrasound imaging method based on a frequency-wavenumber domain row-column addressing array, characterized in that, To shorten the computation time for three-dimensional full-focus ultrasound imaging, the following steps are included: S10 uses a row and column addressing array with a total of N+N transmitting elements to perform ultrasonic scanning on the medium to obtain the acquired signal; S20, Based on the acquired signal, spatial sampling is performed to obtain a three-dimensional voxel network; S30, the radio frequency data beam corresponding to the three-dimensional voxel network is formed using the frequency wavenumber domain method; S40, the data after beamforming in step S30 is enveloped to form a three-dimensional image.

2. The three-dimensional full-focus ultrasound imaging method based on a frequency wavenumber domain row and column addressing array as described in claim 1, Its features are: Step S10 includes the following sub-steps: S11, a single element of the row array transmits an ultrasonic signal into the medium at a predetermined center frequency, and acquires the acquisition signal corresponding to the transmitting element of the row array through N receiving elements of the column array. S12, each element of the column array emits an ultrasonic signal into the medium at the same center frequency as in step S11, and acquires the acquisition signal corresponding to the emitting element of the column array through the N receiving elements of the row array.

3. The three-dimensional full-focus ultrasound imaging method based on frequency wavenumber domain row and column addressing array according to claim 2, characterized in that: in, In step S11, the N transmitting elements of the row array transmit sequentially in a cyclical manner. In step S12, the N transmitting elements of the column array transmit sequentially in a cyclical manner. All N elements of the row array and the column array are valid elements.

4. The three-dimensional full-focus ultrasound imaging method based on frequency wavenumber domain row and column addressing array according to claim 1, characterized in that: in, In step S20, the imaging region is spatially discretized into a three-dimensional voxel grid M×N×H, and the voxel grid is used as the voxel discrete points for imaging to determine the target region.

5. The three-dimensional full-focus ultrasound imaging method based on frequency wavenumber domain row and column addressing array according to claim 4, characterized in that: in, In step S20, the resolution of the discretized three-dimensional voxel mesh is determined according to the probe settings of the row and column addressing array. The axial space between the continuous nodes of the three-dimensional voxel mesh is set to λ / 4, and the transverse and longitudinal scans are set to λ / 2, where λ is the ultrasonic wave length.

6. The three-dimensional full-focus ultrasound imaging method based on frequency wavenumber domain row and column addressing array according to claim 1, characterized in that: in, Step S30 includes the following sub-steps: S31, using 3D Fast Fourier Transform, the backscattered signal RF(u,v,t) in the time-space domain corresponding to the three-dimensional voxel network is converted into a discrete signal RF(k) in the frequency-wavenumber domain. u ,k v ,ω), u is ultrasonic emission, v is backscattering, t is time, k u k is the wavenumber of the ultrasonic emission. v Let ω be the wavenumber of the backscattered signal, and ω be the frequency. S32, Obtain the discrete signal RF(k) u ,k v A one-dimensional slice of ω, according to k X =k u k Y =k v , Calculate k for each wavenumber sampling point u and k v wave number k, k X k Y and k Z These are the wavenumbers of the scattering points in three directions; S33, in a one-dimensional slice RF(k) u ,k v ,ω) ku，kv＝const Performing the Stolt mapping yields the wavenumber function f(k). X ,k Y ,k Z The ultrasound image is then transformed into the spatial domain using a three-dimensional inverse Fourier transform.

Images