An ultrasonic contrast imaging method, apparatus, ultrasonic device and storage medium

Abstract

The application discloses an ultrasonic contrast imaging method and device, an ultrasonic equipment and a readable storage medium. The method comprises the following steps: determining a plurality of transmission frequencies in the effective bandwidth range of an ultrasonic probe, generating a pulse sequence containing a plurality of ultrasonic signal groups based on the plurality of transmission frequencies; the ultrasonic signal group comprises a plurality of ultrasonic signals, and the ultrasonic signal comprises at least two ultrasonic sub-signals with different transmission frequencies in different periods; different ultrasonic signals in different ultrasonic signal groups in the pulse sequence are transmitted in sequence, and echo signals generated by contrast agent microbubbles to the transmitted ultrasonic signals are received; the echo signal comprises fundamental wave signals and harmonic signals corresponding to different imaging frequencies; the echo signal is processed to obtain contrast signals corresponding to a plurality of different imaging frequencies, and a corresponding contrast image is generated based on the contrast signals; and the contrast images are fused to obtain a target contrast image. The application simultaneously meets the requirements of penetration, sensitivity and resolution through one-time contrast imaging.

Description

Technical Field

[0001] This application relates to the field of ultrasound imaging technology, and more specifically, to an ultrasound contrast imaging method, apparatus, ultrasound device, and computer-readable storage medium. Background Technology

[0002] Currently, ultrasound contrast imaging systems from various manufacturers offer three imaging modes: Pen (penetration / sensitivity), Gen (general), and Res (resolution). Users can only choose from the manufacturer-provided modes. However, due to individual differences in physical conditions and varying ultrasound attenuation, doctors will initially select an imaging mode based on experience, depending on the characteristics of the lesion, such as its depth, size, or the presence of multiple lesions of different shapes in the same section. If the contrast image does not meet expectations (e.g., insufficient resolution, sensitivity, or penetration), a second imaging mode may be selected. This is especially true when the same section contains both small and deep lesions; in most cases, multiple contrast imaging sessions are required to observe the perfusion of multiple lesions effectively. Therefore, in some special scenarios, it is impossible to simultaneously meet the requirements of penetration, sensitivity, and resolution in a single contrast imaging session, leading to increased clinical time and contrast agent costs.

[0003] Therefore, how to simultaneously meet the requirements of penetration, sensitivity, and resolution through a single imaging procedure is a technical problem that needs to be solved by those skilled in the art. Summary of the Invention

[0004] The purpose of this application is to provide an ultrasound contrast imaging method, apparatus, ultrasound device, and computer-readable storage medium that simultaneously meet the requirements of penetration, sensitivity, and resolution through a single contrast imaging session.

[0005] To achieve the above objectives, this application provides an ultrasound contrast imaging method, comprising:

[0006] Multiple transmission frequencies are determined within the effective bandwidth of the ultrasonic probe, and a pulse sequence comprising multiple ultrasonic signal groups is generated based on the multiple transmission frequencies; wherein each ultrasonic signal group includes multiple ultrasonic signals, each ultrasonic signal includes at least two ultrasonic sub-signals with different periodic transmission frequencies, the transmission frequencies of corresponding periods are the same between different ultrasonic signals in the same ultrasonic signal group, and the transmission frequencies of corresponding periods are different between different ultrasonic signals in different ultrasonic signal groups.

[0007] Different ultrasound signals from different ultrasound signal groups in the pulse sequence are transmitted sequentially, and echo signals generated by contrast agent microbubbles on the transmitted ultrasound signals are received; wherein, the echo signals include fundamental signals and harmonic signals corresponding to different imaging frequencies;

[0008] The echo signal is processed to obtain multiple contrast signals corresponding to different imaging frequencies, and a corresponding contrast image is generated based on the contrast signals.

[0009] The contrast images are fused to obtain the target contrast image.

[0010] The step of determining multiple transmission frequencies within the effective bandwidth of the ultrasonic probe and generating a pulse sequence containing multiple ultrasonic signal groups based on the multiple transmission frequencies includes:

[0011] A reference transmission frequency and a target coefficient are determined. The product of the reference transmission frequency and the target coefficient is determined as the first transmission frequency. Twice the first transmission frequency is determined as the second transmission frequency. Three times the first transmission frequency is determined as the third transmission frequency. Four times the first transmission frequency is determined as the fourth transmission frequency. The first transmission frequency, the second transmission frequency, the third transmission frequency, and the fourth transmission frequency are all within the effective bandwidth of the ultrasonic probe.

[0012] A pulse sequence comprising a first ultrasonic signal group and a second ultrasonic signal group is generated; wherein the first ultrasonic signal group is generated based on the first transmission frequency and the second transmission frequency, and the second ultrasonic signal group is generated based on the third transmission frequency and the fourth transmission frequency.

[0013] The step of sequentially transmitting different ultrasound signals from different ultrasound signal groups in the pulse sequence includes:

[0014] Different voltage amplitudes are determined for ultrasound sub-signals of corresponding periods in different ultrasound signals within the same ultrasound signal group;

[0015] Determine the same number of emission aperture elements for ultrasonic sub-signals in different ultrasonic signals within the same ultrasonic signal group.

[0016] Based on the transmission frequency, voltage amplitude, and number of transmission aperture elements of different ultrasonic sub-signals in different ultrasonic signals, different ultrasonic signals in different ultrasonic signal groups in the pulse sequence are transmitted sequentially.

[0017] Each ultrasound signal group includes a first ultrasound signal and a second ultrasound signal. Correspondingly, determining different voltage amplitudes for ultrasound sub-signals of corresponding periods within different ultrasound signals of the same ultrasound signal group includes:

[0018] A first voltage amplitude is determined for the ultrasound sub-signal in the first ultrasound signal, and a second voltage amplitude is determined for the ultrasound sub-signal in the second ultrasound signal; wherein the second voltage amplitude is a preset multiple of the first voltage amplitude.

[0019] The second voltage amplitude is twice the first voltage amplitude.

[0020] Each ultrasound signal group includes a first ultrasound signal, a second ultrasound signal, and a third ultrasound signal. Correspondingly, determining different voltage amplitudes for ultrasound sub-signals of corresponding periods within different ultrasound signals of the same ultrasound signal group includes:

[0021] A third voltage amplitude is determined for the ultrasound sub-signal in the first ultrasound signal and the third ultrasound signal, and a fourth voltage amplitude is determined for the ultrasound sub-signal in the second ultrasound signal; wherein the fourth voltage amplitude is a preset multiple of the third voltage amplitude.

[0022] The fourth voltage amplitude is twice the third voltage amplitude.

[0023] The step of sequentially transmitting different ultrasound signals from different ultrasound signal groups in the pulse sequence includes:

[0024] To determine the same voltage amplitude for ultrasound sub-signals of corresponding periods in different ultrasound signals within the same ultrasound signal group;

[0025] To determine the number of different emission aperture elements for ultrasonic sub-signals in different ultrasonic signals within the same ultrasonic signal group;

[0026] Based on the transmission frequency, voltage amplitude, and number of transmission aperture elements of different ultrasonic sub-signals in different ultrasonic signals, different ultrasonic signals in different ultrasonic signal groups in the pulse sequence are transmitted sequentially.

[0027] Each ultrasonic signal group includes a first ultrasonic signal and a second ultrasonic signal. Correspondingly, determining different numbers of emission aperture array elements for ultrasonic sub-signals within the same ultrasonic signal group includes:

[0028] The number of first emission aperture elements is determined for the ultrasonic sub-signals in the first ultrasonic signal, and the number of second emission aperture elements is determined for the ultrasonic sub-signals in the second ultrasonic signal; wherein the number of second emission aperture elements is a preset multiple of the number of first emission aperture elements.

[0029] The number of the second emission aperture array elements is twice the number of the first emission aperture array elements.

[0030] Each ultrasonic signal group includes a first ultrasonic signal, a second ultrasonic signal, and a third ultrasonic signal. Correspondingly, determining different numbers of emission aperture array elements for ultrasonic sub-signals within the same ultrasonic signal group includes:

[0031] The emission aperture of the ultrasonic sub-signal in the first ultrasonic signal is determined to be either an odd aperture or an even aperture; the emission aperture of the ultrasonic sub-signal in the second ultrasonic signal is determined to be the full aperture; and the emission aperture of the ultrasonic sub-signal in the third ultrasonic signal is determined to be either an odd aperture or an even aperture.

[0032] The echo signal is processed to obtain multiple contrast signals corresponding to different imaging frequencies, including:

[0033] The echo signals of different ultrasound signals in each ultrasound signal group are weighted based on the voltage amplitude and phase relationship between different ultrasound signals in each ultrasound signal group to obtain the angiography signal corresponding to each ultrasound signal group.

[0034] The contrast signal corresponding to each ultrasound signal group is demodulated using demodulation circuits corresponding to different imaging frequencies to obtain contrast signals corresponding to different imaging frequencies.

[0035] The step of weighting the echo signals of different ultrasound signals in each ultrasound signal group based on the voltage amplitude and phase relationships between different ultrasound signals in each ultrasound signal group to obtain the contrast signal corresponding to each ultrasound signal group includes:

[0036] The weighting coefficients of the corresponding echo signals are determined based on the voltage amplitude relationship between different ultrasound signals in each ultrasound signal group.

[0037] The operational relationship of the corresponding echo signals is determined based on the phase relationship between different ultrasound signals in each ultrasound signal group; wherein, if the phase relationship is opposite, the operational relationship is addition, and if the phase relationship is the same, the operational relationship is subtraction.

[0038] Weighting is performed based on the weighting coefficients and operational relationships of the echo signals of different ultrasound signals in each ultrasound signal group to obtain the angiography signal corresponding to each ultrasound signal group.

[0039] The step of sequentially transmitting different ultrasound signals from different ultrasound signal groups in the pulse sequence and receiving echo signals generated by contrast agent microbubbles in response to the transmitted ultrasound signals includes:

[0040] Different ultrasound signals from different ultrasound signal groups in the pulse sequence are sequentially transmitted so that the contrast agent microbubbles generate fundamental wave signals corresponding to different first imaging frequencies, and generate multiple harmonic signals corresponding to second imaging frequencies based on the fundamental wave signals corresponding to the first imaging frequencies, and generate differential harmonic signals corresponding to third imaging frequencies based on the fundamental wave signals corresponding to different first imaging frequencies; wherein, the second imaging frequency is an integer multiple of the first imaging frequency, and the third imaging frequency is at least one of the difference or sum of different first imaging frequencies;

[0041] The system receives the fundamental signal corresponding to the first imaging frequency, the multiple harmonic signals corresponding to the second imaging frequency, and the differential harmonic signal corresponding to the third imaging frequency.

[0042] The process of fusing the contrast images to obtain the target contrast image includes:

[0043] The weighting coefficients of each contrast image corresponding to different imaging modes are determined, and the different contrast images are weighted and fused based on the weighting coefficients of each contrast image to obtain the target contrast images corresponding to different imaging modes.

[0044] The imaging modes include a penetration mode and / or a resolution mode. The weighting coefficient of the contrast image corresponding to the penetration mode is negatively correlated with the imaging frequency corresponding to the contrast image, while the weighting coefficient of the contrast image corresponding to the resolution mode is positively correlated with the imaging frequency corresponding to the contrast image.

[0045] The determination of the weighting coefficients for each angiographic image corresponding to different imaging modes includes:

[0046] For any target imaging mode, an adjustment window corresponding to the target contrast image is displayed; wherein, the adjustment window includes the adjustment area of ​​each contrast image;

[0047] The system receives adjustment instructions applied to each adjustment region and adjusts the weighting coefficients of the corresponding contrast images based on the adjustment instructions to obtain the weighting coefficients of each contrast image in the target imaging mode.

[0048] To achieve the above objectives, this application provides an ultrasound contrast imaging device, comprising:

[0049] The generation module is used to determine multiple transmission frequencies within the effective bandwidth of the ultrasonic probe and generate a pulse sequence containing multiple ultrasonic signal groups based on the multiple transmission frequencies; wherein each ultrasonic signal group includes multiple ultrasonic signals, each ultrasonic signal includes at least two ultrasonic sub-signals with different periodic transmission frequencies, the transmission frequencies of corresponding periods are the same between different ultrasonic signals in the same ultrasonic signal group, and the transmission frequencies of corresponding periods are different between different ultrasonic signals in different ultrasonic signal groups.

[0050] The transmitting module is used to sequentially transmit different ultrasound signals from different ultrasound signal groups in the pulse sequence, and receive echo signals generated by contrast agent microbubbles on the transmitted ultrasound signals; wherein, the echo signals include fundamental signals and harmonic signals corresponding to different imaging frequencies;

[0051] The processing module is used to process the echo signal to obtain multiple contrast signals corresponding to different imaging frequencies, and to generate corresponding contrast images based on the contrast signals.

[0052] The fusion module is used to fuse the contrast images to obtain the target contrast image.

[0053] To achieve the above objectives, this application provides an ultrasonic device, comprising:

[0054] Memory, used to store computer programs;

[0055] A processor is used to execute the computer program to implement the steps of the ultrasound contrast imaging method described above.

[0056] To achieve the above objectives, this application provides a computer-readable storage medium storing a computer program that, when executed by a processor, implements the steps of the ultrasound contrast imaging method described above.

[0057] As can be seen from the above scheme, the ultrasound contrast imaging method provided in this application includes: determining multiple transmission frequencies within the effective bandwidth of an ultrasound probe, and generating a pulse sequence containing multiple ultrasound signal groups based on the multiple transmission frequencies; wherein each ultrasound signal group includes multiple ultrasound signals, each ultrasound signal includes at least two ultrasound sub-signals with different periodic transmission frequencies, the transmission frequencies of corresponding periods are the same between different ultrasound signals in the same ultrasound signal group, and the transmission frequencies of corresponding periods are different between different ultrasound signals in different ultrasound signal groups; sequentially transmitting different ultrasound signals in different ultrasound signal groups in the pulse sequence, and receiving echo signals generated by contrast agent microbubbles on the transmitted ultrasound signals; wherein the echo signals include fundamental signals and harmonic signals corresponding to different imaging frequencies; processing the echo signals to obtain multiple contrast signals corresponding to different imaging frequencies, and generating corresponding contrast images based on the contrast signals; and fusing the contrast images to obtain a target contrast image.

[0058] The ultrasound contrast imaging method provided in this application allows the ultrasound probe to emit a complete pulse sequence, obtaining multiple contrast signals corresponding to different imaging frequencies. These signals include fundamental and harmonic signals at different imaging frequencies. Fundamental and harmonic signals at the same imaging frequency mutually reinforce each other, resulting in enhanced contrast signals. The generated contrast images based on these enhanced signals meet the requirements for penetration, sensitivity, and resolution. This application also discloses an ultrasound contrast imaging device, an ultrasound equipment, and a computer-readable storage medium, which similarly achieve the aforementioned technical effects.

[0059] It should be understood that the above general description and the following detailed description are merely exemplary and do not limit this application. Attached Figure Description

[0060] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort. The drawings are used to provide a further understanding of this disclosure and constitute a part of the specification. They are used together with the following detailed description to explain this disclosure, but do not constitute a limitation of this disclosure. In the drawings:

[0061] Figure 1 This is an architectural diagram of an ultrasound imaging system according to an exemplary embodiment;

[0062] Figure 2 This is an architectural diagram of another ultrasound imaging system according to an exemplary embodiment;

[0063] Figure 3 This is a flowchart illustrating an ultrasound contrast imaging method according to an exemplary embodiment;

[0064] Figures 4a-4d This is a schematic diagram illustrating a first ultrasonic signal, a second ultrasonic signal, a third ultrasonic signal, and a fourth ultrasonic signal according to an exemplary embodiment;

[0065] Figures 5a-5d This is a schematic diagram illustrating another first ultrasonic signal, a second ultrasonic signal, a third ultrasonic signal, and a fourth ultrasonic signal according to an exemplary embodiment;

[0066] Figures 6a-6d This is a schematic diagram illustrating yet another first ultrasonic signal, a second ultrasonic signal, a third ultrasonic signal, and a fourth ultrasonic signal according to an exemplary embodiment;

[0067] Figures 7a-7fThis is a schematic diagram illustrating a first ultrasonic signal, a second ultrasonic signal, a third ultrasonic signal, a fourth ultrasonic signal, a fifth ultrasonic signal, and a sixth ultrasonic signal according to an exemplary embodiment;

[0068] Figure 8 This is a schematic diagram illustrating the display of an ultrasound contrast image according to an exemplary embodiment;

[0069] Figure 9 This is a schematic diagram of an adjustment frame for a target contrast image according to an exemplary embodiment;

[0070] Figure 10 This is a structural diagram of an ultrasound contrast imaging apparatus according to an exemplary embodiment;

[0071] Figure 11 This is a structural diagram of an ultrasonic device according to an exemplary embodiment. Detailed Implementation

[0072] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only a part of the embodiments of this application, and not all of them. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application. Furthermore, in the embodiments of this application, "first," "second," etc., are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence.

[0073] This application can be applied to, for example... Figure 1The ultrasound imaging system shown includes an ultrasound host, an ultrasound probe, and a host computer. The host computer determines multiple transmission frequencies within the effective bandwidth of the ultrasound probe and generates a pulse sequence (i.e., transmission waveform) containing multiple ultrasound signal groups through scanning timing control. Each ultrasound signal group includes multiple ultrasound signals. Then, beamforming is performed, and the transmitted signal is sent to the ultrasound probe via the transmission circuit. The ultrasound probe then transmits the signal to the tissue to be examined, where contrast agent microbubbles generate echo signals. Beamforming is performed on the echo signals of each ultrasound signal and stored in a line buffer. Weighted summation or subtraction of the echo signals of different ultrasound signals is performed in the line buffer to obtain the contrast signals corresponding to different ultrasound signal groups. The line buffer can be a Block RAM (Random Access Memory) resource within an FPGA (Field Programmable Gate Array), or an external memory such as DDR (Double Data Rate) or a hard disk, etc., without specific limitations here. Furthermore, demodulation circuitry (such as...) is used to... Figure 1 The N-channel demodulation circuit (where N is a natural number greater than 0) demodulates the contrast signal corresponding to the ultrasound signal group to obtain contrast signals corresponding to different imaging frequencies. After signal processing, the signals are sent to the host computer for imaging processing. Specifically, based on the weighting coefficients of each contrast image corresponding to different imaging modes, the different contrast images are weighted and fused to obtain the target contrast images corresponding to different imaging modes, which are then displayed on the display device.

[0074] It can be seen that, in Figure 1 In this process, the weighting, demodulation, and signal processing of echo signals from different ultrasound signals are performed at the front end of the ultrasound equipment. Alternatively, this can be done at the back end of the host computer; a specific architecture diagram is shown below. Figure 2 As shown.

[0075] This application discloses an ultrasound contrast imaging method that simultaneously meets the requirements of penetration, sensitivity, and resolution through a single contrast imaging session.

[0076] See Figure 3 A flowchart illustrating an ultrasound contrast imaging method according to an exemplary embodiment is shown below. Figure 3 As shown, it includes:

[0077] S101: Determine multiple transmission frequencies within the effective bandwidth of the ultrasonic probe, and generate a pulse sequence containing multiple ultrasonic signal groups based on the multiple transmission frequencies; wherein, each ultrasonic signal group includes multiple ultrasonic signals, each ultrasonic signal includes at least two ultrasonic sub-signals with different transmission frequencies for each period, the transmission frequencies of corresponding periods are the same between different ultrasonic signals in the same ultrasonic signal group, and the transmission frequencies of corresponding periods are different between different ultrasonic signals in different ultrasonic signal groups.

[0078] In practice, multiple transmission frequencies are determined within the effective bandwidth of the ultrasonic probe. The effective bandwidth refers to the range of frequencies that the ultrasonic probe can transmit. It should be noted that the multiple transmission frequencies should cover the effective bandwidth of the ultrasonic probe as much as possible. That is, the minimum transmission frequency is close to the minimum effective bandwidth of the ultrasonic probe, which is the minimum frequency that the ultrasonic probe can transmit, and the maximum transmission frequency is close to the maximum effective bandwidth of the ultrasonic probe, which is the maximum frequency that the ultrasonic probe can transmit.

[0079] Furthermore, a pulse sequence of ultrasonic signals emitted by the ultrasonic probe is generated based on the multiple emission frequencies determined above. This pulse sequence includes multiple ultrasonic signal groups, and each ultrasonic signal includes at least two ultrasonic sub-signals with different periodic emission frequencies. The voltage amplitudes of different ultrasonic sub-signals in each ultrasonic signal can be the same or different (unless otherwise specified, this embodiment uses the same voltage amplitude as an example). The emission frequencies of corresponding periods are the same for different ultrasonic signals in the same ultrasonic signal group, and the emission frequencies of corresponding periods are different for different ultrasonic signals in different ultrasonic signal groups. Optionally, the two periods may include a first period and a second period. Further, the ultrasonic signal includes ultrasonic sub-signals of the first period and ultrasonic sub-signals of the second period, and the emission frequencies of the ultrasonic sub-signals of the first period and the ultrasonic sub-signals of the second period are different.

[0080] In a preferred embodiment, this step may include: determining a reference transmission frequency and a target coefficient; determining a first transmission frequency as the product of the reference transmission frequency and the target coefficient; determining a second transmission frequency as twice the first transmission frequency; determining a third transmission frequency as three times the first transmission frequency; and determining a fourth transmission frequency as four times the first transmission frequency; wherein the first, second, third, and fourth transmission frequencies are all within the effective bandwidth of the ultrasonic probe; generating a pulse sequence comprising a first ultrasonic signal group and a second ultrasonic signal group; wherein the first ultrasonic signal group is generated based on the first and second transmission frequencies, and the second ultrasonic signal group is generated based on the third and fourth transmission frequencies. Optionally, an input command for the target coefficient may be received, and the value corresponding to the target coefficient may be determined based on the value carried by the input command; the target coefficient may be a value between 0 and 1.

[0081] Understandably, for a typical ultrasound probe, four transmission frequencies can cover the effective bandwidth of the probe. Preferably, if the reference transmission frequency is f and the target coefficient is 0.5, then the first transmission frequency is 0.5f, the second transmission frequency is f, the third transmission frequency is 1.5f, and the fourth transmission frequency is 2f. If the voltage amplitude of the first ultrasound signal in the first ultrasound signal group is V1 and the phase is - (i.e., negative phase), the voltage amplitude of the second ultrasound signal is V2 and the phase is + (i.e., positive phase), the voltage amplitude of the third ultrasound signal in the second ultrasound signal group is V3 and the phase is -, and the voltage amplitude of the fourth ultrasound signal is V4 and the phase is +, then the first ultrasound signal in the first ultrasound signal group is as follows: Figure 4a As shown in the figure (the horizontal axis represents frequency, and the vertical axis represents voltage), the second ultrasonic signal in the first ultrasonic signal group is as follows: Figure 4b As shown, the third ultrasound signal in the second ultrasound signal group is as follows: Figure 4c As shown, the fourth ultrasound signal in the second ultrasound signal group is as follows: Figure 4d As shown. For example, for an ultrasound probe with a center frequency of 3.375MHz and an effective bandwidth of 120%, the effective bandwidth range is 1.35MHz-5.4MHz. Therefore, a reference transmission frequency f of 2.7MHz can be selected, and the target coefficient is 0.5. Then, the four transmission frequencies are 1.35MHz, 2.7MHz, 4.05MHz, and 5.4MHz, which correspond to 0.5f, f, 1.5f, and 2f respectively, which can cover the effective bandwidth range of the ultrasound probe.

[0082] Furthermore, if the effective bandwidth of an ultrasonic probe is narrow, given a fixed reference transmission frequency and target coefficient, selecting a smaller number of transmission frequencies can cover the effective bandwidth. For example, for an ultrasonic probe with a center frequency of 3.0 MHz and an effective bandwidth of 70%, the effective bandwidth range is 1.95 MHz - 4.05 MHz. The reference transmission frequency f is 2.0 MHz, and the target coefficient is 0.5. 0.5f = 1.0 MHz, f = 2.0 MHz, 1.5f = 3.0 MHz, and 2f = 4.0 MHz. It is evident that 0.5f exceeds the effective bandwidth of the ultrasonic probe. Selecting transmission frequencies f, 1.5f, and 2f can cover the effective bandwidth. Therefore, the transmission frequencies of the first and second ultrasonic signals, which contain two-cycle ultrasonic sub-signals, can be set to f and f', respectively. The first, second, third, and fourth ultrasonic signals are respectively as follows: Figures 5a-5dAs shown. It should be noted that within the effective bandwidth of the ultrasound probe, f and f' can be equal or unequal, and no specific limitation is made here. If f' ≠ f, then f' can be selected around f or 1.95MHz.

[0083] S102: Sequentially transmit different ultrasound signals from different ultrasound signal groups in the pulse sequence, and receive the echo signals generated by the contrast agent microbubbles on the transmitted ultrasound signals; wherein, the echo signals include fundamental signals and harmonic signals corresponding to different imaging frequencies;

[0084] In this step, the ultrasound probe emits the pulse sequence generated in the previous step, that is, it emits different ultrasound signals from different ultrasound signal groups in sequence, and receives the echo signals generated by the contrast agent microbubbles on the emitted ultrasound signals. The imaging frequency in this step is the frequency of the echo signal.

[0085] It is understood that the voltage amplitudes of different ultrasound signals within the same ultrasound signal group received by the contrast agent microbubbles can be different. As a feasible implementation, this step may include: determining different voltage amplitudes for ultrasound sub-signals of corresponding periods within different ultrasound signals in the same ultrasound signal group; determining the same number of transmitting aperture elements for ultrasound sub-signals within different ultrasound signals in the same ultrasound signal group; and sequentially transmitting different ultrasound signals from different ultrasound signal groups in the pulse sequence based on the transmission frequency, voltage amplitude, and number of transmitting aperture elements for different ultrasound sub-signals within different ultrasound signals. That is, the voltage amplitudes of corresponding periods between different ultrasound signals within the same ultrasound signal group are different, but the number of transmitting aperture elements is the same when transmitting different ultrasound signals from the same ultrasound signal group.

[0086] It should be noted that this embodiment does not limit the number of ultrasound signals in each ultrasound signal group. Each ultrasound signal group may contain two ultrasound signals or three ultrasound signals.

[0087] If each ultrasound signal group includes two ultrasound signals, that is, each ultrasound signal group includes a first ultrasound signal and a second ultrasound signal, then determining different voltage amplitudes for ultrasound sub-signals of corresponding periods in different ultrasound signals within the same ultrasound signal group includes: determining a first voltage amplitude for the ultrasound sub-signals in the first ultrasound signal, and determining a second voltage amplitude for the ultrasound sub-signals in the second ultrasound signal; wherein the second voltage amplitude is a preset multiple of the first voltage amplitude. In a specific implementation, the voltage amplitude of the ultrasound sub-signals in the second ultrasound signal is a preset multiple of the voltage amplitude of the ultrasound sub-signals in the first ultrasound signal. The number of emission aperture array elements is the same when transmitting the ultrasound sub-signals in the second ultrasound signal and when transmitting the ultrasound sub-signals in the first ultrasound signal, which can achieve different voltage amplitudes for the first ultrasound signal and the second ultrasound signal received by the contrast agent microbubbles. Optionally, the preset multiple can be a multiple greater than 1, that is, the second voltage amplitude is greater than the first voltage amplitude. In addition, the preset multiple can be an integer multiple or a non-integer multiple.

[0088] It should be noted that, in order to facilitate subsequent processing of the echo signal, preferably, the second voltage amplitude is twice the first voltage amplitude, that is, the voltage amplitude of the ultrasonic sub-signal in the second ultrasonic signal is twice the voltage amplitude of the ultrasonic sub-signal in the first ultrasonic signal.

[0089] For example, the pulse sequence includes two groups of ultrasonic signals: a first ultrasonic signal group and a second ultrasonic signal group. The first ultrasonic signal group includes a first ultrasonic signal and a second ultrasonic signal, while the second ultrasonic signal group includes a third ultrasonic signal and a fourth ultrasonic signal. Each ultrasonic signal includes two cycles of ultrasonic sub-signals. The voltage amplitude of the first ultrasonic signal is V1, where the ultrasonic sub-signal of the first cycle is f1, and the ultrasonic sub-signal of the second cycle is f2. The voltage amplitude of the second ultrasonic signal is V2, where the ultrasonic sub-signal of the first cycle is f1, and the ultrasonic sub-signal of the second cycle is f2. The voltage amplitude of the third ultrasonic signal is V3, where the ultrasonic sub-signal of the first cycle is f3, and the ultrasonic sub-signal of the second cycle is f4. The voltage amplitude of the fourth ultrasonic signal is V4, where the ultrasonic sub-signal of the first cycle is f3, and the ultrasonic sub-signal of the second cycle is f4. When V1≠V2 and V3≠V4, the number of transmitting aperture elements is the same when transmitting each ultrasonic signal. Preferably, V2 = 2 × V1, and V4 = 2 × V3.

[0090] It should be noted that this embodiment does not limit the phase relationship of different ultrasound signals in the same ultrasound signal group; they can be in the same direction or in opposite directions. That is, the phases of the first and second ultrasound signals in the first ultrasound signal group can be in the same direction or in opposite directions, and the phases of the third and fourth ultrasound signals in the second ultrasound signal group can be in the same direction or in opposite directions. For example, the first ultrasound signal is as follows: Figure 6aAs shown, the second ultrasound signal is as follows Figure 6b As shown, the first and second ultrasonic signals are out of phase, and the third ultrasonic signal is as follows: Figure 6c As shown, the fourth ultrasound signal is as follows Figure 6d As shown, the phases of the third and fourth ultrasound signals are also opposite.

[0091] If each ultrasound signal group includes three ultrasound signals, that is, each ultrasound signal group includes a first ultrasound signal, a second ultrasound signal, and a third ultrasound signal, then determining different voltage amplitudes for ultrasound sub-signals of corresponding periods in different ultrasound signals within the same ultrasound signal group includes: determining a third voltage amplitude for ultrasound sub-signals in the first and third ultrasound signals, and determining a fourth voltage amplitude for ultrasound sub-signals in the second ultrasound signal; wherein the fourth voltage amplitude is a preset multiple of the third voltage amplitude. In a specific implementation, the voltage amplitudes of ultrasound sub-signals in the first and third ultrasound signals are the same, the voltage amplitude of ultrasound sub-signals in the second ultrasound signal is a preset multiple of the voltage amplitudes of ultrasound sub-signals in the first and third ultrasound signals, and the number of transmitting aperture array elements is the same when transmitting ultrasound sub-signals in the first, second, and third ultrasound signals, which can achieve different voltage amplitudes for the first and second ultrasound signals received by the contrast agent microbubbles. Optionally, the preset multiple can be a multiple greater than 1, that is, the fourth voltage amplitude is greater than the third voltage amplitude, and the voltage amplitude of the ultrasonic sub-signal in the second ultrasonic signal is greater than the voltage amplitude of the ultrasonic sub-signal in the first and third ultrasonic signals. In addition, the preset multiple can be an integer multiple or a non-integer multiple.

[0092] It should be noted that, for the convenience of subsequent processing of the echo signal, preferably, the fourth voltage amplitude is twice the third voltage amplitude. That is, the voltage amplitude of the ultrasonic sub-signal in the second ultrasonic signal is twice the voltage amplitude of the ultrasonic sub-signal in the first ultrasonic signal and the third ultrasonic signal, and the voltage amplitude of the ultrasonic sub-signal in the second ultrasonic signal is the sum of the voltage amplitudes of the ultrasonic sub-signals in the first ultrasonic signal and the third ultrasonic signal.

[0093] For example, the pulse sequence includes two groups of ultrasound signals, namely the first ultrasound signal group and the second ultrasound signal group. The first ultrasound signal group includes the first ultrasound signal, the second ultrasound signal and the third ultrasound signal, and the second ultrasound signal group includes the fourth ultrasound signal, the fifth ultrasound signal and the sixth ultrasound signal. Each ultrasound signal includes two cycles of ultrasound sub-signals. The voltage amplitude of the first ultrasound signal is V1, where the ultrasound sub-signal of the first cycle is f1 and the ultrasound sub-signal of the second cycle is f2. The voltage amplitude of the second ultrasound signal is V2, where the ultrasound sub-signal of the first cycle is f1 and the ultrasound sub-signal of the second cycle is f2. The voltage amplitude of the third ultrasound signal is V3, where the ultrasound sub-signal of the first cycle is f1 and the ultrasound sub-signal of the second cycle is f2. The voltage amplitude of the fourth ultrasound signal is V4, where the ultrasound sub-signal of the first cycle is f3 and the ultrasound sub-signal of the second cycle is f4. The voltage amplitude of the fifth ultrasound signal is V5, where the ultrasound sub-signal of the first cycle is f3 and the ultrasound sub-signal of the second cycle is f4. The voltage amplitude of the sixth ultrasound signal is V6, where the ultrasound sub-signal of the first cycle is f3 and the ultrasound sub-signal of the second cycle is f4. When V1≠V2≠V3 and V4≠V5≠V6, the number of transmitting aperture elements is the same when transmitting each ultrasonic signal. Preferably, V2=2×V1=2×V3 and V5=2×V4=2×V6.

[0094] It should be noted that the first and third ultrasound signals are in phase, while the second ultrasound signal may or may not be in phase with the first ultrasound signal. Similarly, the fourth and sixth ultrasound signals are in phase, while the fifth ultrasound signal may or may not be in phase with the fourth ultrasound signal; no specific limitations are imposed here. For example, the first ultrasound signal is as follows: Figure 7a As shown, the second ultrasound signal is as follows Figure 7b As shown, the third ultrasound signal is as follows Figure 7c As shown, the fourth ultrasound signal is as follows Figure 7d As shown, the fifth ultrasound signal is as follows Figure 7e As shown, the sixth ultrasound signal is as follows Figure 7f As shown.

[0095] As another feasible implementation, this step may include: determining the same voltage amplitude for ultrasound sub-signals of corresponding periods in different ultrasound signals within the same ultrasound signal group; determining different numbers of transmitting aperture elements for ultrasound sub-signals in different ultrasound signals within the same ultrasound signal group; and sequentially transmitting different ultrasound signals from different ultrasound signal groups in the pulse sequence based on the transmission frequency, voltage amplitude, and number of transmitting aperture elements for different ultrasound sub-signals in different ultrasound signals. That is, the voltage amplitude of corresponding periods is the same between different ultrasound signals within the same ultrasound signal group, but the number of transmitting aperture elements is different when transmitting different ultrasound signals from the same ultrasound signal group. By controlling the number of transmitting aperture elements to adjust the transmission energy, it is equivalent to adjusting the transmission voltage amplitude, so that the voltage amplitude of different ultrasound signals in the same ultrasound signal group received by the contrast agent microbubbles is different.

[0096] If each ultrasound signal group includes two ultrasound signals, that is, each ultrasound signal group includes a first ultrasound signal and a second ultrasound signal, then determining different numbers of emission aperture array elements for ultrasound sub-signals in different ultrasound signals within the same ultrasound signal group includes: determining a first number of emission aperture array elements for ultrasound sub-signals in the first ultrasound signal, and determining a second number of emission aperture array elements for ultrasound sub-signals in the second ultrasound signal; wherein the number of second emission aperture array elements is a preset multiple of the number of first emission aperture array elements. In specific implementation, the number of emission aperture array elements for ultrasound sub-signals in the second ultrasound signal is a preset multiple of the number of emission aperture array elements for ultrasound sub-signals in the first ultrasound signal, and the voltage amplitudes of the ultrasound sub-signals in the first and second ultrasound signals are the same, which can also achieve different voltage amplitudes for the first and second ultrasound signals received by the contrast agent microbubbles. Optionally, the preset multiple can be a multiple greater than 1, that is, the number of second emission aperture array elements is greater than the number of first emission aperture array elements. In addition, the preset multiple can be an integer multiple or a non-integer multiple.

[0097] It should be noted that, in order to facilitate subsequent processing of the echo signal, preferably, the number of the second transmitting aperture array elements is twice the number of the first transmitting aperture array elements, that is, the number of transmitting aperture array elements of the ultrasonic sub-signal in the second ultrasonic signal is twice the number of transmitting aperture array elements of the ultrasonic sub-signal in the first ultrasonic signal.

[0098] For example, the pulse sequence includes two groups of ultrasound signals: a first ultrasound signal group and a second ultrasound signal group. The first ultrasound signal group includes a first ultrasound signal and a second ultrasound signal, while the second ultrasound signal group includes a third ultrasound signal and a fourth ultrasound signal. Each ultrasound signal includes two cycles of ultrasound sub-signals. The voltage amplitude of the first ultrasound signal is V1, where the ultrasound sub-signal of the first cycle is f1 and the ultrasound sub-signal of the second cycle is f2. The voltage amplitude of the second ultrasound signal is V2, where the ultrasound sub-signal of the first cycle is f1 and the ultrasound sub-signal of the second cycle is f2. The voltage amplitude of the third ultrasound signal is V3, where the ultrasound sub-signal of the first cycle is f3 and the ultrasound sub-signal of the second cycle is f4. The voltage amplitude of the fourth ultrasound signal is V4, where the ultrasound sub-signal of the first cycle is f3 and the ultrasound sub-signal of the second cycle is f4. When V1 = V2 and V3 = V4, the first and third ultrasound signals can be transmitted using an odd aperture or an even aperture, and the second and fourth ultrasound signals can be transmitted using a full aperture.

[0099] If each ultrasound signal group includes three ultrasound signals, that is, each ultrasound signal group includes a first ultrasound signal, a second ultrasound signal, and a third ultrasound signal, then the determination of different emission aperture array elements for ultrasound sub-signals in different ultrasound signals within the same ultrasound signal group includes: determining that the emission aperture of the ultrasound sub-signal in the first ultrasound signal is either an odd aperture or an even aperture; determining that the emission aperture of the ultrasound sub-signal in the second ultrasound signal is the full aperture; and determining that the emission aperture of the ultrasound sub-signal in the third ultrasound signal is either an odd aperture or an even aperture. In specific implementations, when the voltage amplitudes of corresponding periods of different ultrasound signals within the same ultrasound signal group are the same, the first ultrasound signal can be emitted using either an odd aperture or an even aperture, the second ultrasound signal can be emitted using the full aperture, and the third ultrasound signal can be emitted using either an odd aperture or an even aperture. This also achieves the same result where the voltage amplitudes of the first and second ultrasound signals received by the contrast agent microbubbles are different. Optionally, when the emission aperture of the ultrasonic sub-signal in the first ultrasonic signal is an odd aperture, the emission aperture of the ultrasonic sub-signal in the third ultrasonic signal can be an even aperture.

[0100] Furthermore, the array elements in odd-numbered positions and even-numbered positions can be determined separately according to their arrangement. Determining the emission aperture as an odd aperture means defining the array elements in odd-numbered positions as emission aperture array elements, that is, defining the number of array elements in odd-numbered positions as the number of emission aperture array elements; determining the emission aperture as an even aperture means defining the array elements in even-numbered positions as emission aperture array elements, that is, defining the number of array elements in even-numbered positions as the number of emission aperture array elements; determining the emission aperture as a full aperture means defining all array elements as emission aperture array elements, that is, defining the number of all array elements as the number of emission aperture array elements.

[0101] For example, the pulse sequence includes two groups of ultrasound signals, namely the first ultrasound signal group and the second ultrasound signal group. The first ultrasound signal group includes the first ultrasound signal, the second ultrasound signal and the third ultrasound signal, and the second ultrasound signal group includes the fourth ultrasound signal, the fifth ultrasound signal and the sixth ultrasound signal. Each ultrasound signal includes two cycles of ultrasound sub-signals. The voltage amplitude of the first ultrasound signal is V1, where the ultrasound sub-signal of the first cycle is f1 and the ultrasound sub-signal of the second cycle is f2. The voltage amplitude of the second ultrasound signal is V2, where the ultrasound sub-signal of the first cycle is f1 and the ultrasound sub-signal of the second cycle is f2. The voltage amplitude of the third ultrasound signal is V3, where the ultrasound sub-signal of the first cycle is f1 and the ultrasound sub-signal of the second cycle is f2. The voltage amplitude of the fourth ultrasound signal is V4, where the ultrasound sub-signal of the first cycle is f3 and the ultrasound sub-signal of the second cycle is f4. The voltage amplitude of the fifth ultrasound signal is V5, where the ultrasound sub-signal of the first cycle is f3 and the ultrasound sub-signal of the second cycle is f4. The voltage amplitude of the sixth ultrasound signal is V6, where the ultrasound sub-signal of the first cycle is f3 and the ultrasound sub-signal of the second cycle is f4. When V1 = V2 = V3 and V4 = V5 = V6, the number of aperture array elements for transmitting each ultrasonic signal is different. Preferably, the number of aperture array elements for transmitting the second ultrasonic signal is twice that for transmitting the first and third ultrasonic signals, and the number of aperture array elements for transmitting the fifth ultrasonic signal is twice that for transmitting the fourth and sixth ultrasonic signals. That is, the number of aperture array elements for transmitting the second ultrasonic signal is the sum of the number of aperture array elements for transmitting the first and third ultrasonic signals, and the number of aperture array elements for transmitting the fifth ultrasonic signal is the sum of the number of aperture array elements for transmitting the fourth and sixth ultrasonic signals. In specific implementations, one of the odd aperture or even aperture can be used to transmit the first and fourth ultrasonic signals, the entire aperture can be used to transmit the second and fifth ultrasonic signals, and the other of the odd aperture or even aperture can be used to transmit the third and sixth ultrasonic signals.

[0102] Specifically, the step of sequentially transmitting different ultrasound signals from different ultrasound signal groups in the pulse sequence and receiving echo signals generated by contrast agent microbubbles in response to the transmitted ultrasound signals includes: sequentially transmitting different ultrasound signals from different ultrasound signal groups in the pulse sequence so that the contrast agent microbubbles generate fundamental signals corresponding to different first imaging frequencies, generating multiple harmonic signals corresponding to a second imaging frequency based on the fundamental signals corresponding to the first imaging frequencies, and generating differential harmonic signals corresponding to a third imaging frequency based on the fundamental signals corresponding to different first imaging frequencies; wherein the second imaging frequency is an integer multiple of the first imaging frequency, and the third imaging frequency is at least one of the difference or sum between different first imaging frequencies; receiving the fundamental signal corresponding to the first imaging frequency, the multiple harmonic signals corresponding to the second imaging frequency, and the differential harmonic signals corresponding to the third imaging frequency. Optionally, the difference between different first imaging frequencies can be determined, the sum between different first imaging frequencies can be determined, and the difference and / or sum can be determined as the third imaging frequency.

[0103] In practice, the ultrasound probe emits a pulse sequence, and contrast agent microbubbles generate echo signals. These echo signals can include fundamental and harmonic signals. The imaging frequency of the fundamental signal (i.e., the first imaging frequency) is the transmission frequency. Harmonic signals include differential harmonic signals and multiple harmonic signals. The differential harmonic signal is the difference between different fundamental signals, and its imaging frequency (i.e., the third imaging frequency) is the difference between different transmission frequencies, and / or the sum of different transmission frequencies. Multiple harmonic signals can be understood as multiple superpositions of the same fundamental signal, such as second and third harmonic signals. The imaging frequency of multiple harmonic signals (i.e., the second imaging frequency) is an integer multiple of the transmission frequency. Since third or higher harmonic signals often exceed the effective bandwidth of the ultrasound probe, they are generally not considered.

[0104] by Figures 4a-4d For example, for the first ultrasound signal group, the 0.5f nonlinear fundamental signal and the f nonlinear fundamental signal can be directly obtained. Multiplying and subtracting the 0.5f and f nonlinear fundamental signals yields the 0.5f differential harmonic signal and the 1.5f differential harmonic signal. Optionally, calculating the difference between the 0.5f and f nonlinear fundamental signals yields the 0.5f differential harmonic signal, and calculating the sum of the 0.5f and f nonlinear fundamental signals yields the 1.5f differential harmonic signal.

[0105] Based on the 0.5f nonlinear fundamental wave signals corresponding to the first and second ultrasound signals, respectively, the 0.5f second harmonic signal, i.e., the f harmonic signal, can be obtained. Similarly, based on the f nonlinear fundamental wave signals corresponding to the first and second ultrasound signals, the f second harmonic signal, i.e., the 2f harmonic signal, can be obtained. Therefore, the angiographic signals corresponding to the first ultrasound signal group include the 0.5f nonlinear fundamental wave signal, the f nonlinear fundamental wave signal, the 0.5f differential harmonic signal, the 1.5f differential harmonic signal, the f harmonic signal, and the 2f harmonic signal. Likewise, the angiographic signals corresponding to the second ultrasound signal group include the 1.5f nonlinear fundamental wave signal, the 2f nonlinear fundamental wave signal, the 0.5f differential harmonic signal, the 3.5f differential harmonic signal, the 3f harmonic signal, and the 4f harmonic signal.

[0106] S103: The echo signal is processed to obtain multiple contrast signals corresponding to different imaging frequencies, and a corresponding contrast image is generated based on the contrast signals.

[0107] In this step, the echo signals of different ultrasound signals are processed to obtain multiple contrast signals corresponding to different imaging frequencies. The imaging frequency can be the transmission frequency or an integer multiple of the transmission frequency. The contrast signal includes fundamental and harmonic signals of multiple imaging frequencies. The fundamental and harmonic signals corresponding to multiple imaging frequencies enhance each other to obtain an enhanced contrast signal. The enhanced contrast signal is then processed to generate the corresponding contrast image and stored.

[0108] As a feasible implementation method, the echo signal is processed to obtain multiple contrast signals corresponding to different transmission frequencies, including: weighting the echo signals of different ultrasound signals in each ultrasound signal group based on the voltage amplitude and phase relationship between different ultrasound signals in each ultrasound signal group to obtain the contrast signal corresponding to each ultrasound signal group; and demodulating the contrast signal corresponding to each ultrasound signal group using demodulation circuits corresponding to different imaging frequencies to obtain contrast signals corresponding to different imaging frequencies.

[0109] In specific implementation, the weighting coefficients of the corresponding echo signals are determined based on the voltage amplitude relationship between different ultrasound signals in each ultrasound signal group. For Figures 6a-6d For example, if V2 = Weight_Path1 × V1, then the weight corresponding to the first ultrasound signal is Weight_Path1, and the weight corresponding to the second ultrasound signal is 1. If V4 = Weight_Path2 × V3, then the weight corresponding to the third ultrasound signal is Weight_Path2, and the weight corresponding to the fourth ultrasound signal is 1. Figures 7a-7fFor example, if V1 = V3 = V2 / Weight_Path1, then the weights of the first and third ultrasound signals are 1, and the weight of the second ultrasound signal is 2 / Weight_Path1. If V4 = V6 = V5 / Weight_Path2, then the weights of the fourth and sixth ultrasound signals are 1, and the weight of the fifth ultrasound signal is 2 / Weight_Path2.

[0110] In specific implementation, if there are cases where the voltage amplitudes of different ultrasound sub-signals in the ultrasound signal are different, weights can be set for different ultrasound sub-signals in the ultrasound signal according to the proportional relationship of voltage amplitudes, and then superimposed with the weights of the ultrasound signal determined in the aforementioned embodiment and weighted to obtain the contrast signal corresponding to the corresponding ultrasound signal group.

[0111] Furthermore, the operational relationship of the corresponding echo signals is determined based on the phase relationship between different ultrasound signals in each ultrasound signal group; wherein, if the phase relationship is opposite, the operational relationship is addition, and if the phase relationship is the same, the operational relationship is subtraction. That is, if the phase relationship between different ultrasound signals in the ultrasound signal group is opposite, then during weighting processing, the echo signals corresponding to different ultrasound signals in the ultrasound signal group are weighted and added together; if the phase relationship between different ultrasound signals in the ultrasound signal group is the same, then during weighting processing, the echo signals corresponding to different ultrasound signals in the ultrasound signal group are weighted and subtracted together.

[0112] Based on the weights and operational relationships determined above, the echo signals of different ultrasound signals in each ultrasound signal group are weighted to obtain the angiography signal corresponding to each ultrasound signal group. For Figures 6a-6d For example, if the first and second ultrasound signals in the first ultrasound signal group are out of phase, then when calculating the angiography signal corresponding to the first ultrasound signal group, the first and second ultrasound signals are weighted and added together. Similarly, if the first and second ultrasound signals in the second ultrasound signal group are out of phase, then when calculating the angiography signal corresponding to the second ultrasound signal group, the first and second ultrasound signals are weighted and added together. The angiography signal Dataout1 corresponding to the first ultrasound signal group and the angiography signal Dataout2 corresponding to the second ultrasound signal group are as follows:

[0113] Dataout1=Weight_Path1×Data_1stTX+Data_2ndTX;

[0114] Dataout2=Weight_Path2×Data_3rdTX+Data_4thTX;

[0115] Wherein, Data_1stTX is the echo signal of the first ultrasound signal, Data_2ndTX is the echo signal of the second ultrasound signal, Data_3rdTX is the echo signal of the third ultrasound signal, and Data_4thTX is the echo signal of the fourth ultrasound signal.

[0116] Furthermore, if the first and second ultrasound signals in the first ultrasound signal group have the same phase, then when calculating the angiography signal corresponding to the first ultrasound signal group, the first and second ultrasound signals are weighted and subtracted; if the first and second ultrasound signals in the second ultrasound signal group have the same phase, then when calculating the angiography signal corresponding to the second ultrasound signal group, the first and second ultrasound signals are weighted and subtracted. Therefore:

[0117] Dataout1=Weight_Path1×Data_1stTX﹣Data_2ndTX;

[0118] Dataout2=Weight_Path2×Data_3rdTX﹣Data_4thTX.

[0119] If the first and second ultrasound signals in the first ultrasound signal group are out of phase, then when calculating the corresponding contrast signal for the first ultrasound signal group, the first and second ultrasound signals are weighted and added together. If the first and second ultrasound signals in the second ultrasound signal group are in phase, then when calculating the corresponding contrast signal for the second ultrasound signal group, the first and second ultrasound signals are weighted and subtracted together. Therefore:

[0120] Dataout1=Weight_Path1×Data_1stTX+Data_2ndTX;

[0121] Dataout2=Weight_Path2×Data_3rdTX﹣Data_4thTX.

[0122] If the first and second ultrasound signals in the first ultrasound signal group are in phase, then when calculating the corresponding contrast signal for the first ultrasound signal group, the first and second ultrasound signals are weighted and subtracted. If the first and second ultrasound signals in the second ultrasound signal group are out of phase, then when calculating the corresponding contrast signal for the first ultrasound signal group, the first and second ultrasound signals are weighted and added. Therefore:

[0123] Dataout1=Weight_Path1×Data_1stTX﹣Data_2ndTX;

[0124] Dataout2=Weight_Path2×Data_3rdTX+Data_4thTX.

[0125] When an ultrasound signal group contains three ultrasound signals, if the first and third ultrasound signals are in phase, and the first and third ultrasound signals are in phase or out of phase with the second ultrasound signal, then the sum of the first and third ultrasound signals (which can be a weighted sum) can be performed and then weighted with the second ultrasound signal. Specifically, when the first and third ultrasound signals are in phase with the second ultrasound signal, a weighted subtraction is performed; when the first and third ultrasound signals are out of phase with the second ultrasound signal, a weighted addition is performed.

[0126] for Figures 7a-7f For example, in the first ultrasound signal group, the first and third ultrasound signals have the same phase, but the phase is opposite to that of the second ultrasound signal. Therefore, when calculating the angiography signal corresponding to the first ultrasound signal group, the first and second ultrasound signals are summed and then weighted and added to the third ultrasound signal. Similarly, in the second ultrasound signal group, the fourth and sixth ultrasound signals have the same phase, but the phase is opposite to that of the fifth ultrasound signal. Therefore, when calculating the angiography signal corresponding to the second ultrasound signal group, the fourth and fifth ultrasound signals are summed and then weighted and added to the sixth ultrasound signal. The angiography signal Dataout1 corresponding to the first ultrasound signal group and the angiography signal Dataout2 corresponding to the second ultrasound signal group are as follows:

[0127] Dataout1=Data_1stTX+2 / Weight_Path1×Data_2ndTX+Data_3rdTX;

[0128] Dataout2=Data_4thTX+2 / Weight_Path2×Data_5thTX+Data_6thTX;

[0129] Wherein, Data_1stTX is the echo signal of the first ultrasound signal, Data_2ndTX is the echo signal of the second ultrasound signal, Data_3rdTX is the echo signal of the third ultrasound signal, Data_4thTX is the echo signal of the fourth ultrasound signal, Data_5thTX is the echo signal of the fifth ultrasound signal, and Data_6thTX is the echo signal of the sixth ultrasound signal.

[0130] Furthermore, if the first, second, and third ultrasound signals in the first ultrasound signal group have the same phase, then when calculating the angiography signal corresponding to the first ultrasound signal group, the first ultrasound signal and the second ultrasound signal are summed and then subtracted from the third ultrasound signal using a weighted summation. If the fourth and sixth ultrasound signals in the second ultrasound signal group have the same phase, but the phase is opposite to that of the fifth ultrasound signal, then when calculating the angiography signal corresponding to the second ultrasound signal group, the fourth and fifth ultrasound signals are summed and then added to the sixth ultrasound signal using a weighted summation. The angiography signal Dataout1 corresponding to the first ultrasound signal group and the angiography signal Dataout2 corresponding to the second ultrasound signal group are as follows:

[0131] Dataout1=Data_1stTX-2 / Weight_Path1×Data_2ndTX+Data_3rdTX;

[0132] Dataout2=Data_4thTX+2 / Weight_Path2×Data_5thTX+Data_6thTX.

[0133] Furthermore, demodulation circuits corresponding to different imaging frequencies are needed to demodulate the contrast signal corresponding to each ultrasound signal group to obtain contrast signals corresponding to different imaging frequencies. Figures 4a-4d For example, the demodulation circuits corresponding to 0.5f, f, 1.5f, and 2f are used to demodulate the contrast signal corresponding to the first ultrasound signal group, respectively, to obtain the first contrast signal of 0.5f (including the nonlinear fundamental signal of 0.5f and the differential harmonic signal of 0.5f), the second contrast signal of f (including the nonlinear fundamental signal of f and the harmonic signal of f), the third contrast signal of 1.5f (including the differential harmonic signal of 1.5f and the third harmonic of 1.5f), and the fourth contrast signal of 2f (including the harmonic signal of 2f). Furthermore, since 3f, 3.5f, and 4f exceed the effective bandwidth of the ultrasound probe, demodulation circuits corresponding to 0.5f, 1.5f, and 2f are used to demodulate the contrast signals corresponding to the second ultrasound signal group, respectively, to obtain the fifth contrast signal of 0.5f (including the differential harmonic signal of 0.5f), the sixth contrast signal of 1.5f (including the nonlinear fundamental signal of 1.5f), and the seventh contrast signal of 2f (including the nonlinear fundamental signal of 2f). It can be seen that by using four demodulation circuits to demodulate the contrast signals and performing subsequent signal processing, seven contrast images corresponding to the seven contrast signals are generated, as shown in Table 1.

[0134] Table 1

[0135]

[0136]

[0137] by Figures 5a-5d For example, if f = f', then the angiography signal corresponding to the first ultrasound signal group includes the nonlinear fundamental wave signal of f and the harmonic signal of 2f. The angiography signal corresponding to the second ultrasound signal group includes the nonlinear fundamental wave signal of 1.5f, the nonlinear fundamental wave signal of 2f, the differential harmonic signal of 0.5f, the differential harmonic signal of 3.5f, the harmonic signal of 3f, and the harmonic signal of 4f. Since 3f, 3.5f, and 4f exceed the effective bandwidth of the ultrasound probe, demodulation circuits corresponding to f and 2f are used to demodulate the contrast signals corresponding to the first ultrasound signal group, resulting in the first contrast signal of f (including the nonlinear fundamental wave signal of f) and the second contrast signal of 2f (including the harmonic signals of 2f). Similarly, demodulation circuits corresponding to 0.5f, 1.5f, and 2f are used to demodulate the contrast signals corresponding to the second ultrasound signal group, resulting in the third contrast signal of 0.5f (including the differential harmonic signals of 0.5f), the fourth contrast signal of 1.5f (including the nonlinear fundamental wave signal of 1.5f), and the fifth contrast signal of 2f (including the nonlinear fundamental wave signal of 2f). Therefore, using four demodulation circuits to demodulate the contrast signals and performing subsequent signal processing generates five contrast images corresponding to the five contrast signals, as shown in Table 2.

[0138] Table 2

[0139]

[0140] If f' is slightly greater than f, then the angiography signals corresponding to the first ultrasound signal group include the nonlinear fundamental wave signal of f, the nonlinear fundamental wave signal of f', the differential harmonic signal of f'-f, the differential harmonic signal of f'+f, the harmonic signal of 2f, and the harmonic signal of 2f'. The angiography signals corresponding to the second ultrasound signal group include the nonlinear fundamental wave signal of 1.5f, the nonlinear fundamental wave signal of 2f, the differential harmonic signal of 0.5f, the differential harmonic signal of 3.5f, the harmonic signal of 3f, and the harmonic signal of 4f. Since f'-f, 3f, 3.5f, and 4f exceed the effective bandwidth of the ultrasound probe, and f'+f is close to 2f, the demodulation circuits corresponding to f, 2f, f', and 2f' are used to demodulate the contrast signals corresponding to the first ultrasound signal group, respectively, to obtain the first contrast signal of f (including the nonlinear fundamental wave signal of f), the second contrast signal of 2f (including the harmonic signal of 2f), the third contrast signal of f' (including the nonlinear fundamental wave signal of f'), and the fourth contrast signal of 2f' (including the harmonic signal of 2f'). The demodulation circuits corresponding to 0.5f, 1.5f, and 2f are used to demodulate the contrast signals corresponding to the second ultrasound signal group, respectively, to obtain the fifth contrast signal of 0.5f (including the differential harmonic signal of 0.5f), the sixth contrast signal of 1.5f (including the nonlinear fundamental wave signal of 1.5f), and the seventh contrast signal of 2f (including the nonlinear fundamental wave signal of 2f). As can be seen, a 6-channel demodulation circuit is used to demodulate the contrast signal and perform subsequent signal processing to generate seven contrast images corresponding to the seven contrast signals, as shown in Table 3:

[0141] Table 3

[0142]

[0143]

[0144] S104: The contrast images are fused to obtain the target contrast image.

[0145] In this step, different contrast images are fused to obtain the target contrast image. As a possible implementation, this step may include: determining the weighting coefficients of each contrast image corresponding to different imaging modes, and performing weighted fusion of the different contrast images based on these weighting coefficients to obtain the target contrast images corresponding to different imaging modes. In a specific implementation, the weighted fusion of each contrast image is performed based on its weighting coefficients to obtain the output target contrast image. The fusion formula is:

[0146]

[0147] Where Sub_imagei is the i-th contrast image, coefi is the weighting coefficient of the i-th contrast image, and ContrastImage is the target contrast image.

[0148] It should be noted that the weighting coefficients for each contrast image corresponding to different imaging modes are different, with weighting coefficients ∈ [0,1]. By weighting and fusing different contrast images based on the weighting coefficients corresponding to each contrast image of different imaging modes, target contrast images corresponding to different imaging modes can be obtained. Imaging modes can include general mode, penetration mode, and resolution mode, etc., while simultaneously meeting the requirements of penetration, sensitivity, and resolution.

[0149] For the general mode, contrast images with moderate frequency components can be used for fusion. Taking Table 1 as an example, the second and sixth contrast images can be fused, that is, contrast images with f and 1.5f can be fused; the second, fourth, and seventh contrast images can be fused, that is, contrast images with f and 2f can be fused; and the second, fourth, sixth, and seventh contrast images can be fused, that is, contrast images with f, 1.5f, and 2f can be fused. Of course, other fusion methods exist, but this embodiment does not specifically limit them.

[0150] For the penetration mode, the contrast image requires high penetration and sensitivity. Therefore, contrast images with lower frequency components can be used for fusion. That is, the weighting coefficient of the contrast image corresponding to the penetration mode is negatively correlated with the imaging frequency of the contrast image. Taking Table 1 as an example, the first contrast image can be used alone as the target contrast image, i.e., a 0.5f contrast image can be used alone; the second contrast image can be used alone as the target contrast image, i.e., a f contrast image can be used alone; or the first and second contrast images can be fused, i.e., fusion of 0.5f and f contrast images. Of course, other fusion methods exist, but this embodiment does not specifically limit them.

[0151] For resolution mode, high resolution of the contrast images is required. Therefore, contrast images with higher frequency components can be used for fusion. That is, the weighting coefficient of the contrast image corresponding to the resolution mode is positively correlated with the imaging frequency of the contrast image. Taking Table 1 as an example, the fourth, sixth, and seventh contrast images can be fused, that is, fused using 1.5f and 2f contrast images. Alternatively, the fourth and seventh contrast images can be fused, that is, fused using the 2f contrast image. Of course, other fusion methods exist, but this embodiment does not specifically limit them.

[0152] Understandably, users can select one or more imaging modes to display the target contrast signal. A typical ultrasound contrast image display is shown below. Figure 8 As shown, it can simultaneously display ultrasound grayscale images of tissues, general mode, penetration mode, and resolution mode of the target ultrasound image.

[0153] Furthermore, since the contrast images corresponding to each contrast signal are generated and stored, this embodiment can also support users to manually adjust the weighting coefficients of each contrast image. As a feasible implementation method, determining the weighting coefficients of each contrast image corresponding to different imaging modes includes: for any target imaging mode, displaying an adjustment window corresponding to the target contrast image; wherein, the adjustment window includes adjustment areas for each contrast image; receiving adjustment instructions acting on each adjustment area, and adjusting the weighting coefficients of the corresponding contrast images based on the adjustment instructions to obtain the weighting coefficients of each contrast image under the target imaging mode. In a specific implementation, the user can click on a displayed target contrast image to display the adjustment window of that target contrast image (e.g., ...). Figure 9 As shown, users can adjust the weighting coefficients by dragging the corresponding black dots in the adjustment areas of each contrast image up and down, thereby meeting the needs of different scenarios. A vertical adjustment bar and its corresponding black dot constitute an adjustment control for a contrast image. This embodiment achieves personalized settings for the weighting coefficients by adjusting the control, enabling personalized adjustments to image fusion to meet the needs of different scenarios.

[0154] Optionally, the ultrasound device may include a display screen and a touch screen. The display screen is used to output and display ultrasound images, while the touch screen is used to receive input signals, such as keystrokes entered by the user on a virtual keyboard. Adjustment windows can be displayed on both the display screen and the touch screen, allowing users to adjust the weight of each contrast image by sliding the corresponding black dot. For ultrasound devices without a touch screen, the adjustment window can be displayed as a pop-up on the display screen. In this case, users can adjust the weight of the corresponding contrast image by sliding the black dot in the adjustment window using knobs or levers on the ultrasound device.

[0155] Optionally, different areas of the ultrasound device's display screen can be used as display windows for contrast images under different imaging modes. When a display window is selected, the corresponding target imaging mode is determined to be selected, and the adjustment window for the target contrast image corresponding to the target imaging mode is displayed. For ultrasound devices with touchscreens, the adjustment window can be displayed directly on the touchscreen; for ultrasound devices without touchscreens, the adjustment window can pop up in the main display interface of the contrast images. The weighting coefficients of each contrast image are determined based on the adjustment commands applied to the adjustment window, and then weighted fusion processing is performed to obtain the target contrast image.

[0156] The ultrasound contrast imaging method provided in this application embodiment can obtain multiple contrast signals corresponding to different imaging frequencies by transmitting a complete pulse sequence once. These signals include fundamental and harmonic signals of different imaging frequencies. The fundamental and harmonic signals corresponding to the same imaging frequency enhance each other to obtain enhanced contrast signals. The corresponding contrast images generated based on the enhanced contrast signals can meet the requirements of penetration, sensitivity, and resolution.

[0157] The following describes an ultrasound contrast imaging device provided in the embodiments of this application. The ultrasound contrast imaging device described below and the ultrasound contrast imaging method described above can be referred to each other.

[0158] See Figure 10 A structural diagram of an ultrasound contrast imaging apparatus is shown according to an exemplary embodiment, as follows: Figure 10 As shown, it includes:

[0159] The generation module 100 is used to determine multiple transmission frequencies within the effective bandwidth of the ultrasonic probe and generate a pulse sequence containing multiple ultrasonic signal groups based on the multiple transmission frequencies; wherein each ultrasonic signal group includes multiple ultrasonic signals, each ultrasonic signal includes at least two ultrasonic sub-signals with different periodic transmission frequencies, the transmission frequencies of corresponding periods are the same between different ultrasonic signals in the same ultrasonic signal group, and the transmission frequencies of corresponding periods are different between different ultrasonic signals in different ultrasonic signal groups.

[0160] The transmitting module 200 is used to sequentially transmit different ultrasound signals from different ultrasound signal groups in the pulse sequence, and receive echo signals generated by contrast agent microbubbles on the transmitted ultrasound signals; wherein, the echo signals include fundamental signals and harmonic signals corresponding to different imaging frequencies;

[0161] The processing module 300 is used to process the echo signal to obtain multiple contrast signals corresponding to different imaging frequencies, and to generate corresponding contrast images based on the contrast signals.

[0162] The fusion module 400 is used to fuse the contrast images to obtain the target contrast image.

[0163] The ultrasound contrast imaging device provided in this application embodiment can obtain multiple contrast signals corresponding to different imaging frequencies by emitting a complete pulse sequence. These signals include fundamental and harmonic signals of different imaging frequencies. The fundamental and harmonic signals corresponding to the same imaging frequency enhance each other to obtain enhanced contrast signals. The corresponding contrast images generated based on the enhanced contrast signals can meet the requirements of penetration, sensitivity, and resolution.

[0164] Based on the above embodiments, as a preferred implementation, the generation module 100 is specifically used for: determining a reference transmission frequency and a target coefficient; determining the product of the reference transmission frequency and the target coefficient as a first transmission frequency; determining twice the first transmission frequency as a second transmission frequency; determining three times the first transmission frequency as a third transmission frequency; and determining four times the first transmission frequency as a fourth transmission frequency; wherein the first transmission frequency, the second transmission frequency, the third transmission frequency, and the fourth transmission frequency are all within the effective bandwidth of the ultrasonic probe; generating a pulse sequence containing a first ultrasonic signal group and a second ultrasonic signal group; wherein the first ultrasonic signal group is generated based on the first transmission frequency and the second transmission frequency, and the second ultrasonic signal group is generated based on the third transmission frequency and the fourth transmission frequency.

[0165] Based on the above embodiments, as a preferred embodiment, the transmitting module 200 includes:

[0166] The second determining unit is used to determine different voltage amplitudes for ultrasound sub-signals of corresponding periods in different ultrasound signals within the same ultrasound signal group;

[0167] The third determining unit is used to determine the same number of emission aperture array elements for ultrasonic sub-signals in different ultrasonic signals in the same ultrasonic signal group;

[0168] The first transmitting unit is used to sequentially transmit different ultrasonic signals from different ultrasonic signal groups in the pulse sequence based on the transmission frequency, voltage amplitude, and transmission aperture of different ultrasonic sub-signals in different ultrasonic signals.

[0169] Based on the above embodiments, as a preferred implementation, each ultrasonic signal group includes a first ultrasonic signal and a second ultrasonic signal. Accordingly, the second determining unit is specifically used to: determine a first voltage amplitude for the ultrasonic sub-signal in the first ultrasonic signal, and determine a second voltage amplitude for the ultrasonic sub-signal in the second ultrasonic signal; wherein the second voltage amplitude is a preset multiple of the first voltage amplitude.

[0170] Based on the above embodiments, as a preferred embodiment, the second voltage amplitude is twice the first voltage amplitude.

[0171] Based on the above embodiments, as a preferred implementation, each ultrasonic signal group includes a first ultrasonic signal, a second ultrasonic signal, and a third ultrasonic signal. Correspondingly, the second determining unit is specifically used to: determine a third voltage amplitude for the ultrasonic sub-signals in the first ultrasonic signal and the third ultrasonic signal, and determine a fourth voltage amplitude for the ultrasonic sub-signals in the second ultrasonic signal; wherein the fourth voltage amplitude is a preset multiple of the third voltage amplitude.

[0172] Based on the above embodiments, as a preferred embodiment, the fourth voltage amplitude is twice the third voltage amplitude.

[0173] Based on the above embodiments, as a preferred embodiment, the transmitting module 200 includes:

[0174] The fourth determining unit is used to determine the same voltage amplitude for ultrasound sub-signals of corresponding periods in different ultrasound signals within the same ultrasound signal group;

[0175] The fifth determining unit is used to determine the different number of emission aperture array elements for ultrasonic sub-signals in different ultrasonic signals within the same ultrasonic signal group;

[0176] The second transmitting unit is used to sequentially transmit different ultrasonic signals from different ultrasonic signal groups in the pulse sequence based on the transmission frequency, voltage amplitude, and transmission aperture of different ultrasonic sub-signals in different ultrasonic signals.

[0177] Based on the above embodiments, as a preferred implementation, each ultrasonic signal group includes a first ultrasonic signal and a second ultrasonic signal. Accordingly, the fifth determining unit is specifically used to: determine the number of first emission aperture array elements for the ultrasonic sub-signals in the first ultrasonic signal, and determine the number of second emission aperture array elements for the ultrasonic sub-signals in the second ultrasonic signal; wherein the number of second emission aperture array elements is a preset multiple of the number of first emission aperture array elements.

[0178] Based on the above embodiments, as a preferred embodiment, the number of the second emission aperture array elements is twice the number of the first emission aperture array elements.

[0179] Based on the above embodiments, as a preferred implementation, each ultrasonic signal group includes a first ultrasonic signal, a second ultrasonic signal, and a third ultrasonic signal. Correspondingly, the fifth determining unit is specifically used to: determine that the emission aperture of the ultrasonic sub-signal in the first ultrasonic signal is one of an odd aperture or an even aperture, determine that the emission aperture of the ultrasonic sub-signal in the second ultrasonic signal is the full aperture, and determine that the emission aperture of the ultrasonic sub-signal in the third ultrasonic signal is the other of an odd aperture or an even aperture.

[0180] Based on the above embodiments, as a preferred embodiment, the processing module 300 includes:

[0181] The processing unit is used to perform weighted processing on the echo signals of different ultrasound signals in each ultrasound signal group based on the voltage amplitude relationship and phase relationship between different ultrasound signals in each ultrasound signal group, so as to obtain the contrast signal corresponding to each ultrasound signal group.

[0182] The demodulation unit is used to demodulate the contrast signal corresponding to each ultrasound signal group using demodulation circuits corresponding to different imaging frequencies, so as to obtain the contrast signal corresponding to different imaging frequencies.

[0183] The generation unit is used to generate a corresponding contrast image based on the contrast signal.

[0184] Based on the above embodiments, as a preferred embodiment, the processing unit is specifically used for: determining the weighting coefficients of the corresponding echo signals based on the voltage amplitude relationship between different ultrasound signals in each ultrasound signal group; determining the operational relationship of the corresponding echo signals based on the phase relationship between different ultrasound signals in each ultrasound signal group; wherein, if the phase relationship is opposite, the operational relationship is addition, and if the phase relationship is the same, the operational relationship is subtraction; performing weighted processing based on the weighting coefficients and operational relationships of the echo signals of different ultrasound signals in each ultrasound signal group to obtain the contrast signal corresponding to each ultrasound signal group.

[0185] Based on the above embodiments, as a preferred embodiment, the transmitting module 200 is specifically configured to: sequentially transmit different ultrasound signals from different ultrasound signal groups in the pulse sequence, so that the contrast agent microbubbles generate fundamental wave signals corresponding to different first imaging frequencies, and generate multiple harmonic signals corresponding to a second imaging frequency based on the fundamental wave signals corresponding to the first imaging frequencies, and generate differential harmonic signals corresponding to a third imaging frequency based on the fundamental wave signals corresponding to different first imaging frequencies; wherein, the second imaging frequency is an integer multiple of the first imaging frequency, and the third imaging frequency is at least one of the difference or sum of different first imaging frequencies; and receive the fundamental wave signal corresponding to the first imaging frequency, the multiple harmonic signals corresponding to the second imaging frequency, and the differential harmonic signals corresponding to the third imaging frequency.

[0186] Based on the above embodiments, as a preferred embodiment, the fusion module 400 includes:

[0187] The first determining unit is used to determine the weighting coefficients of each angiographic image corresponding to different imaging modes;

[0188] The fusion unit is used to perform weighted fusion of different contrast images based on the weighting coefficients of each contrast image to obtain target contrast images corresponding to different imaging modes.

[0189] Based on the above embodiments, as a preferred embodiment, the imaging mode includes a penetration mode and / or a resolution mode. The weighting coefficient of the contrast image corresponding to the penetration mode is negatively correlated with the imaging frequency corresponding to the contrast image, and the weighting coefficient of the contrast image corresponding to the resolution mode is positively correlated with the imaging frequency corresponding to the contrast image.

[0190] Based on the above embodiments, as a preferred implementation, the first determining unit is specifically used to display an adjustment window corresponding to the target contrast image for any target imaging mode; wherein, the adjustment window includes an adjustment area for each contrast image; receive adjustment instructions acting on each adjustment area, and adjust the weighting coefficient of the corresponding contrast image based on the adjustment instructions to obtain the weighting coefficient of each contrast image under the target imaging mode.

[0191] Regarding the apparatus in the above embodiments, the specific manner in which each module performs its operation has been described in detail in the embodiments related to the method, and will not be elaborated upon here.

[0192] Based on the hardware implementation of the above program modules, and in order to implement the method of the embodiments of this application, the embodiments of this application also provide an ultrasonic device. Figure 11 This is a structural diagram illustrating an ultrasonic device according to an exemplary embodiment, such as... Figure 11As shown, the ultrasound equipment includes:

[0193] Communication interface 1 enables information exchange with other devices, such as network devices;

[0194] Processor 2 is connected to communication interface 1 to enable information exchange with other devices and, when running a computer program, executes the ultrasound contrast imaging method provided by one or more of the above-mentioned technical solutions. The computer program is stored in memory 3.

[0195] Of course, in practical applications, the various components of the ultrasonic equipment are coupled together through bus system 4. It can be understood that bus system 4 is used to achieve communication and connection between these components. In addition to the data bus, bus system 4 also includes a power bus, a control bus, and a status signal bus. However, for clarity, in... Figure 11 The general will label all buses as Bus System 4.

[0196] The memory 3 in this embodiment is used to store various types of data to support the operation of the ultrasound device. Examples of such data include any computer program used to operate the ultrasound device.

[0197] It is understood that memory 3 can be volatile memory or non-volatile memory, or both. Non-volatile memory can be read-only memory (ROM), programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EEPROM), ferromagnetic random access memory (FRAM), flash memory, magnetic surface memory, optical disc, or compact disc read-only memory (CD-ROM); magnetic surface memory can be disk storage or magnetic tape storage. Volatile memory can be random access memory (RAM), which is used as an external cache. By way of example, but not limitation, many forms of RAM are available, such as Static Random Access Memory (SRAM), Synchronous Static Random Access Memory (SSRAM), Dynamic Random Access Memory (DRAM), Synchronous Dynamic Random Access Memory (SDRAM), Double Data Rate Synchronous Dynamic Random Access Memory (DDRSDRAM), Enhanced Synchronous Dynamic Random Access Memory (ESDRAM), SyncLink Dynamic Random Access Memory (SLDRAM), and Direct Rambus Random Access Memory (DRRAM).The memory 3 described in the embodiments of this application is intended to include, but is not limited to, these and any other suitable types of memory.

[0198] The methods disclosed in the embodiments of this application can be applied to processor 2, or implemented by processor 2. Processor 2 may be an integrated circuit chip with signal processing capabilities. In the implementation process, each step of the above method can be completed by the integrated logic circuit of the hardware in processor 2 or by instructions in the form of software. The processor 2 may be a general-purpose processor, DSP, or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. Processor 2 can implement or execute the methods, steps and logic block diagrams disclosed in the embodiments of this application. The general-purpose processor may be a microprocessor or any conventional processor, etc. The steps of the methods disclosed in the embodiments of this application can be directly manifested as being executed by a hardware decoding processor, or being executed by a combination of hardware and software modules in the decoding processor. The software modules may be located in a storage medium, which is located in memory 3. Processor 2 reads the program in memory 3 and completes the steps of the aforementioned method in combination with its hardware.

[0199] When processor 2 executes the program, it implements the corresponding processes in the various methods of the embodiments of this application. For the sake of brevity, these will not be described in detail here.

[0200] In an exemplary embodiment, this application also provides a storage medium, namely a computer storage medium, specifically a computer-readable storage medium, such as a memory 3 that stores a computer program, which can be executed by a processor 2 to complete the steps described in the aforementioned method. The computer-readable storage medium may be a memory such as FRAM, ROM, PROM, EPROM, EEPROM, Flash Memory, magnetic surface memory, optical disc, or CD-ROM.

[0201] Those skilled in the art will understand that all or part of the steps of the above method embodiments can be implemented by hardware related to program instructions. The aforementioned program can be stored in a computer-readable storage medium. When the program is executed, it performs the steps of the above method embodiments. The aforementioned storage medium includes various media that can store program code, such as mobile storage devices, ROM, RAM, magnetic disks, or optical disks.

[0202] Alternatively, if the integrated units described above are implemented as software functional modules and sold or used as independent products, they can also be stored in a computer-readable storage medium. Based on this understanding, the technical solutions of the embodiments of this application, or the parts that contribute to the prior art, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions to cause an ultrasound device (which may be a personal computer, server, or network device, etc.) to execute all or part of the methods described in the various embodiments of this application. The aforementioned storage medium includes various media capable of storing program code, such as mobile storage devices, ROM, RAM, magnetic disks, or optical disks.

[0203] The above description is merely a specific embodiment of this application, but the scope of protection of this application is not limited thereto. Any variations or substitutions that can be easily conceived by those skilled in the art within the scope of the technology disclosed in this application should be included within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the scope of the claims.

Claims

1. A method for ultrasound contrast imaging, characterized in that, include: Multiple transmission frequencies are determined within the effective bandwidth of the ultrasonic probe, and a pulse sequence comprising multiple ultrasonic signal groups is generated based on the multiple transmission frequencies; wherein, each ultrasonic signal group includes multiple ultrasonic signals, and each ultrasonic signal includes at least a first-cycle ultrasonic sub-signal and a second-cycle ultrasonic sub-signal, the transmission frequencies of the first-cycle ultrasonic sub-signal and the second-cycle ultrasonic sub-signal are different, the transmission frequencies of corresponding cycles of different ultrasonic signals in the same ultrasonic signal group are the same, and the transmission frequencies of corresponding cycles of different ultrasonic signals in different ultrasonic signal groups are different. Different ultrasound signals from different ultrasound signal groups in the pulse sequence are transmitted sequentially, and echo signals generated by contrast agent microbubbles on the transmitted ultrasound signals are received; wherein, the echo signals include fundamental signals and harmonic signals corresponding to different imaging frequencies; The echo signal is processed to obtain multiple contrast signals corresponding to different imaging frequencies, and a corresponding contrast image is generated based on the contrast signals. The contrast images are fused to obtain the target contrast image.

2. The ultrasound contrast imaging method according to claim 1, characterized in that, The step of determining multiple transmission frequencies within the effective bandwidth of the ultrasonic probe and generating a pulse sequence containing multiple ultrasonic signal groups based on the multiple transmission frequencies includes: A reference transmission frequency and a target coefficient are determined. The product of the reference transmission frequency and the target coefficient is determined as the first transmission frequency. Twice the first transmission frequency is determined as the second transmission frequency. Three times the first transmission frequency is determined as the third transmission frequency. Four times the first transmission frequency is determined as the fourth transmission frequency. The first transmission frequency, the second transmission frequency, the third transmission frequency, and the fourth transmission frequency are all within the effective bandwidth of the ultrasonic probe. A pulse sequence comprising a first ultrasonic signal group and a second ultrasonic signal group is generated; wherein the first ultrasonic signal group is generated based on the first transmission frequency and the second transmission frequency, and the second ultrasonic signal group is generated based on the third transmission frequency and the fourth transmission frequency.

3. The ultrasound contrast imaging method according to claim 1, characterized in that, The sequential transmission of different ultrasound signals from different ultrasound signal groups in the pulse sequence includes: Different voltage amplitudes are determined for ultrasound sub-signals of corresponding periods in different ultrasound signals within the same ultrasound signal group; Determine the same number of emission aperture elements for ultrasonic sub-signals in different ultrasonic signals within the same ultrasonic signal group. Based on the transmission frequency, voltage amplitude, and number of transmission aperture elements of different ultrasonic sub-signals in different ultrasonic signals, different ultrasonic signals in different ultrasonic signal groups in the pulse sequence are transmitted sequentially.

4. The ultrasound contrast imaging method according to claim 3, characterized in that, Each ultrasound signal group includes a first ultrasound signal and a second ultrasound signal. Correspondingly, determining different voltage amplitudes for ultrasound sub-signals of corresponding periods within different ultrasound signals of the same ultrasound signal group includes: A first voltage amplitude is determined for the ultrasound sub-signal in the first ultrasound signal, and a second voltage amplitude is determined for the ultrasound sub-signal in the second ultrasound signal; wherein the second voltage amplitude is a preset multiple of the first voltage amplitude.

5. The ultrasound contrast imaging method according to claim 3, characterized in that, Each ultrasound signal group includes a first ultrasound signal, a second ultrasound signal, and a third ultrasound signal. Correspondingly, determining different voltage amplitudes for ultrasound sub-signals of corresponding periods within different ultrasound signals of the same ultrasound signal group includes: A third voltage amplitude is determined for the ultrasound sub-signal in the first ultrasound signal and the third ultrasound signal, and a fourth voltage amplitude is determined for the ultrasound sub-signal in the second ultrasound signal; wherein the fourth voltage amplitude is a preset multiple of the third voltage amplitude.

6. The ultrasound contrast imaging method according to claim 1, characterized in that, The sequential transmission of different ultrasound signals from different ultrasound signal groups in the pulse sequence includes: To determine the same voltage amplitude for ultrasound sub-signals of corresponding periods in different ultrasound signals within the same ultrasound signal group; To determine the number of different emission aperture elements for ultrasonic sub-signals in different ultrasonic signals within the same ultrasonic signal group; Based on the transmission frequency, voltage amplitude, and number of transmission aperture elements of different ultrasonic sub-signals in different ultrasonic signals, different ultrasonic signals in different ultrasonic signal groups in the pulse sequence are transmitted sequentially.

7. The ultrasound contrast imaging method according to claim 6, characterized in that, Each ultrasonic signal group includes a first ultrasonic signal and a second ultrasonic signal. Correspondingly, determining different numbers of emission aperture array elements for ultrasonic sub-signals within different ultrasonic signals of the same ultrasonic signal group includes: The number of first emission aperture elements is determined for the ultrasonic sub-signals in the first ultrasonic signal, and the number of second emission aperture elements is determined for the ultrasonic sub-signals in the second ultrasonic signal; wherein the number of second emission aperture elements is a preset multiple of the number of first emission aperture elements.

8. The ultrasound contrast imaging method according to claim 7, characterized in that, The number of the second emission aperture elements is twice the number of the first emission aperture elements.

9. The ultrasound contrast imaging method according to claim 8, characterized in that, Each ultrasonic signal group includes a first ultrasonic signal, a second ultrasonic signal, and a third ultrasonic signal. Correspondingly, determining different numbers of emission aperture array elements for ultrasonic sub-signals within different ultrasonic signals of the same ultrasonic signal group includes: The emission aperture of the ultrasonic sub-signal in the first ultrasonic signal is determined to be either an odd aperture or an even aperture; the emission aperture of the ultrasonic sub-signal in the second ultrasonic signal is determined to be the full aperture; and the emission aperture of the ultrasonic sub-signal in the third ultrasonic signal is determined to be either an odd aperture or an even aperture.

10. The ultrasound contrast imaging method according to any one of claims 1 to 9, characterized in that, The echo signal is processed to obtain multiple angiographic signals corresponding to different imaging frequencies, including: The echo signals of different ultrasound signals in each ultrasound signal group are weighted based on the voltage amplitude and phase relationship between different ultrasound signals in each ultrasound signal group to obtain the angiography signal corresponding to each ultrasound signal group. The contrast signal corresponding to each ultrasound signal group is demodulated using demodulation circuits corresponding to different imaging frequencies to obtain contrast signals corresponding to different imaging frequencies.

11. The ultrasound contrast imaging method according to claim 10, characterized in that, The weighted processing of echo signals from different ultrasound signals in each ultrasound signal group, based on the voltage amplitude and phase relationships between different ultrasound signals in each ultrasound signal group, yields the contrast signal corresponding to each ultrasound signal group, including: The weighting coefficients of the corresponding echo signals are determined based on the voltage amplitude relationship between different ultrasound signals in each ultrasound signal group. The operational relationship of the corresponding echo signals is determined based on the phase relationship between different ultrasound signals in each ultrasound signal group; wherein, if the phase relationship is opposite, the operational relationship is addition, and if the phase relationship is the same, the operational relationship is subtraction. Weighting is performed based on the weighting coefficients and operational relationships of the echo signals of different ultrasound signals in each ultrasound signal group to obtain the angiography signal corresponding to each ultrasound signal group.

12. The ultrasound contrast imaging method according to any one of claims 1 to 9, characterized in that, The step of sequentially transmitting different ultrasound signals from different ultrasound signal groups in the pulse sequence and receiving echo signals generated by contrast agent microbubbles in response to the transmitted ultrasound signals includes: Different ultrasound signals from different ultrasound signal groups in the pulse sequence are sequentially transmitted so that the contrast agent microbubbles generate fundamental wave signals corresponding to different first imaging frequencies, and generate multiple harmonic signals corresponding to second imaging frequencies based on the fundamental wave signals corresponding to the first imaging frequencies, and generate differential harmonic signals corresponding to third imaging frequencies based on the fundamental wave signals corresponding to different first imaging frequencies; wherein, the second imaging frequency is an integer multiple of the first imaging frequency, and the third imaging frequency is at least one of the difference or sum of different first imaging frequencies; The system receives the fundamental signal corresponding to the first imaging frequency, the multiple harmonic signals corresponding to the second imaging frequency, and the differential harmonic signal corresponding to the third imaging frequency.

13. The ultrasound contrast imaging method according to any one of claims 1 to 9, characterized in that, The target contrast image is obtained by fusing the contrast images, including: The weighting coefficients of each contrast image corresponding to different imaging modes are determined, and the different contrast images are weighted and fused based on the weighting coefficients of each contrast image to obtain the target contrast images corresponding to different imaging modes.

14. The ultrasound contrast imaging method according to claim 13, characterized in that, The imaging modes include a penetration mode and / or a resolution mode. The weighting coefficient of the contrast image corresponding to the penetration mode is negatively correlated with the imaging frequency corresponding to the contrast image, while the weighting coefficient of the contrast image corresponding to the resolution mode is positively correlated with the imaging frequency corresponding to the contrast image.

15. The ultrasound contrast imaging method according to claim 13, characterized in that, The determination of the weighting coefficients for each angiographic image corresponding to different imaging modes includes: For any target imaging mode, an adjustment window corresponding to the target contrast image is displayed; wherein, the adjustment window includes the adjustment area of ​​each contrast image; The system receives adjustment instructions applied to each adjustment region and adjusts the weighting coefficients of the corresponding contrast images based on the adjustment instructions to obtain the weighting coefficients of each contrast image in the target imaging mode.

16. An ultrasound contrast imaging device, characterized in that, include: A generation module is used to determine multiple transmission frequencies within the effective bandwidth of an ultrasonic probe, and generate a pulse sequence containing multiple ultrasonic signal groups based on the multiple transmission frequencies; wherein each ultrasonic signal group includes multiple ultrasonic signals, each ultrasonic signal includes at least a first-cycle ultrasonic sub-signal and a second-cycle ultrasonic sub-signal, the first-cycle ultrasonic sub-signal and the second-cycle ultrasonic sub-signal have different transmission frequencies, the transmission frequencies of corresponding cycles of different ultrasonic signals in the same ultrasonic signal group are the same, and the transmission frequencies of corresponding cycles of different ultrasonic signals in different ultrasonic signal groups are different. The transmitting module is used to sequentially transmit different ultrasound signals from different ultrasound signal groups in the pulse sequence, and receive echo signals generated by contrast agent microbubbles on the transmitted ultrasound signals; wherein, the echo signals include fundamental signals and harmonic signals corresponding to different imaging frequencies; The processing module is used to process the echo signal to obtain multiple contrast signals corresponding to different imaging frequencies, and to generate corresponding contrast images based on the contrast signals. The fusion module is used to fuse the contrast images to obtain the target contrast image.

17. An ultrasonic device, characterized in that, include: Memory, used to store computer programs; A processor for executing the computer program to implement the steps of the ultrasound contrast imaging method as described in any one of claims 1 to 15.

18. A computer-readable storage medium, characterized in that, The computer-readable storage medium stores a computer program that, when executed by a processor, implements the steps of the ultrasound contrast imaging method as described in any one of claims 1 to 15.

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