High-intensity focused ultrasound multi-phase dynamic transmitter and use method thereof
Through the periodic cyclic emission mode of the high-intensity focused ultrasound multi-phase dynamic transmitter, the problems of ultrasound channel tissue burns and low treatment efficiency under non-anesthesia conditions are solved, and efficient and safe target tissue ablation is achieved.
Patent Information
- Application Number
- CN202511047058.6
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- Filing Date
- 2025-07-29
- Publication Date
- 2025-09-12
AI Technical Summary
Existing high-intensity focused ultrasound treatment equipment is prone to burning tissue in the ultrasound channel without anesthesia and has low treatment efficiency, making it difficult to reach the temperature required for thermal coagulation of lesions.
A high-intensity focused ultrasound multi-phase dynamic transmitter is used, and through multiple independent phase groups of ultrasound transmitting chips and independent circuit modules, a periodic cycle of emission-intermittent action is achieved, and each phase group is driven in time to transmit in turn to avoid overload of ultrasound channel tissue.
It improves treatment efficiency, ensures that the target tissue quickly reaches the ablation threshold, reduces the risk of tissue burns in the ultrasound channel, enhances patient tolerance, and optimizes energy output.
Smart Images
Figure CN120617857A_ABST
Abstract
Description
Technical Field
[0001] The present invention belongs to the technical field of medical equipment, and in particular relates to a high-intensity focused ultrasound multi-phase dynamic transmitter and a method for using the same. Background Art
[0002] High-intensity focused ultrasound (HIFU) therapy has been used clinically in Chinese hospitals for nearly 30 years and is widely used to treat conditions such as tumors, uterine fibroids, and benign prostatic hyperplasia. HIFU therapy utilizes the excellent penetration and focusability of ultrasound in human tissue. High-intensity ultrasound waves are emitted from outside the body and focused internally to form a controlled, transient, high-temperature (65-100°C) focal zone. This focal zone, located using ultrasound and controlled by the machine's operating system, precisely and irreversibly inactivates the target tissue, causing coagulative necrosis without causing damage or side effects to surrounding normal tissue. This allows for painless tumor removal without anesthesia or surgery.
[0003] At present, the ultrasonic transmitters that realize this technical principle can be divided into unit transmitters and multi-element transmitters based on the number of transmitting chips; and can be divided into upper and lower types based on the installation position. The upper transmitter is located above the treatment bed, and the patient takes a supine position during treatment; the lower transmitter is located below the treatment bed, and the patient takes a prone position during treatment.
[0004] While the aforementioned technical solutions differ in the number of chips and their installation locations, they all employ a single-phase ultrasound transmission mode: that is, all transmitting chips transmit (discharge) and pause (charge) synchronously. This mode suffers from a common drawback: when the HIFU focal zone irradiates and heats the lesion area, the normal tissue through which the ultrasound channel passes is also heated by the ultrasound. Specifically, increasing the power to 6,000-15,000 W / cm² under anesthesia or analgesia can easily cause burns to the channel tissue. In the non-anesthetized state, the ultrasound power output is typically controlled below 3,000 W / cm² due to the patient's pain threshold. This makes it difficult for the ultrasound focal zone to reach the temperature required for thermal coagulation of the lesion, making it impossible to guarantee coagulative necrosis and therapeutic efficacy. Summary of the Invention
[0005] To overcome the above technical problems, the present invention provides a high-intensity focused ultrasound multi-phase dynamic transmitter and a method for using the same. By dynamically switching the emission and energy distribution of high-intensity focused ultrasound multi-phase, the limitations of existing HIFU technology can be broken through, and precise and effective ablation of the target area can be achieved without anesthesia.
[0006] The present invention adopts the following technical solutions: High-intensity focused ultrasound multi-phase dynamic transmitter, the transmitter has multiple ultrasonic transmitting chips on the transmitting surface, and the ultrasonic transmitting chips are evenly divided into N independent phase groups. Each group of chips has an independent circuit module. The chips in each phase group perform the transmission-intermittent action synchronously. Different phase groups are not synchronized, and the energy output parameters of all phase groups are consistent.
[0007] Preferably, the chips within each phase group are evenly distributed in a circular array with the emitter center as the reference, and the chips between each phase group are also evenly distributed in a circular array with the emitter center as the reference, and each phase group contains at least two rows of chips along the radial direction of the emitting surface.
[0008] The present invention also discloses a method for using a high-intensity focused ultrasound multi-phase dynamic transmitter, comprising: driving each phase group in a time-sharing manner through an independent circuit module, so that each group transmits ultrasound in turn according to a preset transmission duration T, and the interval duration of a single phase group within the transmitter transmission period (NT) is (N-1)T, and the switching between the transmission and intermittent states follows the following rules: the current phase stops transmitting and the next group starts transmitting at the same time, thereby forming a periodic dynamic transmission sequence.
[0009] Preferably, the energy and irradiation time of the ultrasound channel tissue are reduced to 3 / (2N) of the single-phase technology, and the interval time of each group of chips is 3(N-1) / N times of the single-phase technology.
[0010] Compared with the prior art, the present invention has the following beneficial effects: 1. Improved treatment efficiency: The focal target can obtain equivalent continuous ultrasound irradiation heating through multi-phase rotation emission, avoiding the blood circulation that carries away the focal energy due to intermittent emission. This significantly improves the target heating efficiency, ensures stable accumulation of focal energy and quickly reaches the target tissue ablation threshold, and guarantees the treatment effect. 2. Ensure treatment safety: The transmitter adopts an intermittent rotation irradiation mode, which greatly reduces the ultrasonic energy and irradiation time borne by the ultrasound channel tissue, effectively avoiding channel tissue burns; 3. Enhance patient tolerance: The irradiation time of the ultrasound channel is greatly shortened, which can improve the patient's tolerance to ultrasound energy, create conditions for further increasing the treatment energy, and thus enhance the efficacy; 4. Optimize energy output: The interval time (i.e., charging time) of the emission chips in all phases is extended, and the charging and energy storage are more sufficient, so that the emission power is greater and more work is done, which accelerates the heating of the focal area and further optimizes the treatment effect. BRIEF DESCRIPTION OF THE DRAWINGS
[0011] Figure 1 Schematic diagram of an embodiment of the present invention.
[0012] Description of reference numerals: 1 Phase group one; 2 Phase group two; 3 Phase group three. DETAILED DESCRIPTION
[0013] The following describes embodiments of the present invention in detail. Examples of the embodiments are shown in the accompanying drawings. The same or similar reference numerals throughout represent the same or similar elements or elements having the same or similar functions. Unless otherwise specified, the raw materials and equipment used are commercially available or commonly used in the art. The methods in the embodiments, unless otherwise specified, are conventional methods in the art. The embodiments described below with reference to the accompanying drawings are exemplary and are intended only to explain the present invention and are not to be construed as limiting the present invention.
[0014] See also Figure 1 The high-intensity focused ultrasound multi-phase dynamic transmitter has 18 ultrasonic transmitting chips on its transmitting surface. These chips are arranged in nine rows of two chips each, along the circular radius of the transmitting surface, with adjacent rows indexed at 40°. Clockwise, rows 1, 4, and 7 constitute phase group 1; rows 2, 5, and 8 constitute phase group 2; and rows 3, 6, and 9 constitute phase group 3. Each phase group chip has an independent circuit module. The chips within each phase group perform the transmit-intermittent operation synchronously, while different phase groups are asynchronous. The energy output parameters of all phase groups are consistent.
[0015] A method for using a high-intensity focused ultrasound multi-phase dynamic transmitter, using the transmitter, further comprising: Independent circuit modules drive each phase group in a time-sharing manner, allowing each group to transmit ultrasound in turn according to a preset transmission duration, T. The switching between transmit and pause states follows the principle of stopping transmission in the current phase and starting the next group simultaneously, forming a cyclical dynamic transmission sequence. This multi-phase rotation achieves equivalent continuous heating of the focal target, reducing the energy and irradiation time of the ultrasound channel tissue to half that of single-phase technology. Furthermore, the pause / recharge time of each chip group is twice that of single-phase technology.
[0016] Timing control: The transmission and intermittent states of each phase follow a strict sequential logic. When one phase is transmitting, the remaining N-1 phases are in intermittent (charging or standby). After the current phase completes its set transmission duration, it immediately switches to intermittent mode, and the next phase starts transmitting, repeating this cycle until a transmission cycle is complete. A complete transmission cycle begins with the transmission of the first group of chips and ends with the transmission of the third group of chips. If the transmission time of each phase is T, the transmitter's transmission cycle is 3T.
[0017] Periodic characteristics: The entire emission process repeats the above switching logic in a fixed period. The cycle length can be dynamically adjusted according to treatment requirements (such as target tissue type and lesion size) to ensure that each group of chips can fully output energy during the cyclic emission and obtain sufficient intermittent charging time.
[0018] Dynamic Adjustment: Based on real-time treatment feedback from the focal target (e.g., through ultrasound imaging or temperature monitoring), the system dynamically adjusts parameters such as the transmit power and duration of each phase to achieve "precise energy control." For example, for target areas with high energy requirements, the transmit cycle can be appropriately extended or the output power increased to further optimize the focal energy distribution and enhance treatment effectiveness.
[0019] This dynamic emission mode not only avoids the overload of ultrasound channel tissue caused by single-phase continuous emission, but also enables each group of chips to fully store energy during the interval by operating in rotation, ensuring power stability and energy effectiveness during emission, and ultimately achieving the dual goals of "safe temperature control" and "efficient ablation".
[0020] Although the present invention has been shown and described in detail, case For example, those skilled in the art will appreciate that various changes, modifications, substitutions and variations may be made to the above embodiments without departing from the principles and purpose of the present invention, and that the scope of the present invention is defined by the claims and their equivalents.
Claims
1. High-intensity focused ultrasound multi-phase dynamic transmitter, the transmitter has multiple ultrasound transmitting chips on the transmitting surface, characterized in that: The ultrasonic transmitting chips are evenly divided into N independent phase groups. Each group of chips has an independent circuit module. The chips in each phase group perform the emission-intermittent action synchronously. Different phase groups are not synchronized. The energy output parameters of all phase groups are consistent.
2. The high-intensity focused ultrasound multi-phase dynamic transmitter according to claim 1, characterized in that: The chips within each phase group are evenly distributed in a circular array with the emitter center as the reference, and the chips between each phase group are also evenly distributed in a circular array with the emitter center as the reference. Each phase group contains at least two rows of chips along the radial direction of the emitting surface.
3. The method for using the high-intensity focused ultrasound multi-phase dynamic transmitter according to claim 1 or 2, characterized in that: include: Each phase group is driven by an independent circuit module in a time-sharing manner, so that each group transmits ultrasound in turn according to the preset transmission time length T. The time length of one transmission circle is the transmission cycle of the transmitter, which is NT. The interval length of a single phase group is (N-1)T, and the switching between the transmission and intermittent states follows the following principle: the current phase stops transmitting and the next group starts transmitting at the same time; A dynamic emission sequence with a periodic cycle is formed.
4. The method of use according to claim 3, characterized in that By emitting in turns in multiple phases, equivalent continuous heating of the focal target is achieved, reducing the energy and irradiation time of the ultrasound channel tissue to 3 / (2N) of that of the single-phase technology, and the interval time of each group of chips is 3(N-1) / N times that of the single-phase technology (Note: To facilitate calculation and comparative analysis, it is assumed that in the single-phase technology, the emission time (t1) and the interval time (t2) are allocated according to the most commonly used ratio of 2:1, the same below.).