Ultrasonic surgical system

Abstract

The present application discloses an ultrasonic surgical system, comprising: a host, which generates an electrical signal for generating ultrasonic vibrations; a transducer, which receives the electrical signal and generates ultrasonic vibrations in response to the electrical signal; an axis assembly, which comprises a waveguide rod, a first end of the waveguide rod being connected to the transducer to conduct the ultrasonic vibrations generated by the transducer; and an action portion, at the second end of the waveguide rod, for receiving the ultrasonic vibrations generated by the transducer and conducted via the waveguide rod, and outputting the received ultrasonic vibrations to the contacted tissue, wherein the host is configured to adjust the electrical signal to drive the transducer to generate ultrasonic vibrations within a first frequency range and ultrasonic vibrations within a second frequency range, the upper frequency limit and the lower frequency limit of the first frequency range being twice the upper frequency limit and the lower frequency limit of the second frequency range, respectively, wherein the axis assembly has a first resonant frequency in the first frequency range and a second resonant frequency in the second frequency range, and the first resonant frequency is the second resonant frequency multiplied by two.

Description

Technical Field

[0001] The present application relates to an ultrasonic surgical system, and more particularly, to an ultrasonic surgical system capable of performing sterilization while performing routine operations. Background Art

[0002] As a commonly used surgical device, ultrasonic surgical systems, such as ultrasonic scalpels, are widely used during surgical procedures for tissue mobilization, cutting, hemostasis, and small blood vessel severing and sealing. Compared to electrocautery, ultrasonic scalpels offer advantages such as improved hemostasis, minimal thermal effects, lack of smoke, and improved visibility. However, similar to traditional scalpels and electrocautery, these procedures can cause mucosal damage, thereby disrupting the mucosal barrier and increasing the risk of intraoperative microbial invasion. Therefore, clinically, large doses of antibiotics are often required after surgeries using ultrasonic scalpels. Even so, the risk of postoperative infection remains.

[0003] It can be seen that there is a demand in the art for an ultrasonic scalpel that can achieve a sterilization effect while performing conventional operations such as freeing, cutting, hemostasis, small blood vessel severing and closing. Summary of the Invention

[0004] The present application relates to an ultrasonic surgical system comprising a main unit, a transducer, a shaft assembly, and an action unit. The main unit generates an electrical signal for generating ultrasonic vibrations, and the transducer receives the electrical signal and generates ultrasonic vibrations in response to the electrical signal. The shaft assembly includes a horn, the first end of which is connected to the transducer to transmit the ultrasonic vibrations generated by the transducer. The action unit is located at the second end of the horn and is configured to receive the ultrasonic vibrations generated by the transducer transmitted via the horn and output the received ultrasonic vibrations. The main unit is configured to modulate the electrical signal to drive the transducer to generate ultrasonic vibrations within a first frequency range or a second frequency range, where the upper and lower frequency limits of the first frequency range are twice the upper and lower frequency limits of the second frequency range, respectively. The horn has a first resonant frequency within the first frequency range and a second resonant frequency within the second frequency range, where the first resonant frequency is twice the second resonant frequency. The ultrasonic scalpel according to the present application can output ultrasonic vibrations at two frequencies without having to replace the horn, for tissue cutting and sterilization, respectively.

[0005] In some embodiments, the host is configured to drive the transducer by adjusting the frequency of the host's electrical signal, the transducer generates a resonant signal, the host detects the resonant signal and sweeps within a second frequency range, thereby first locking the horn at the second resonant frequency and then locking the first resonant frequency to twice the second resonant frequency. In some other embodiments, the host is configured to drive the transducer by adjusting the frequency of the host's electrical signal, the transducer generates a resonant signal, the host detects the resonant signal and sweeps within a first frequency range, thereby first locking the horn at the first resonant frequency and then locking the second resonant frequency to half the first resonant frequency. By sweeping within the frequency range to lock the resonant frequency, it is possible to take into account the situation where the actual resonant frequency of the horn deviates from the designed resonant frequency within a certain range.

[0006] In some embodiments, the waveguide rod is used to provide a conductive path for ultrasonic vibrations, and the shaft assembly further includes a sleeve disposed around the waveguide rod and a plurality of support portions. The support portions are disposed on the waveguide rod at intervals along the length of the waveguide rod and flexibly support the waveguide rod within the sleeve.

[0007] In some embodiments, the position of the support portion along the length direction of the waveguide rod corresponds to at least some of the node positions generated by the waveguide rod at the second resonant frequency, so that the vibration energy at the first resonant frequency and the second resonant frequency can be absorbed as little as possible, thereby enhancing the vibration energy output to the action portion.

[0008] In some embodiments, the first frequency range is 54.5 kHz to 56.5 kHz to facilitate cutting of tissue, and the second frequency range is 27.25 kHz to 28.25 kHz to facilitate local sterilization near the tissue.

[0009] In some embodiments, the host device is configured to, when the active portion contacts tissue, drive the transducer to first generate ultrasonic vibrations at a second resonant frequency for a first duration and then continuously generate ultrasonic vibrations at the first resonant frequency by changing the frequency of the electrical signal. The ultrasonic vibrations at the second resonant frequency for the first duration can be used to locally sterilize the surrounding tissue before the ultrasonic vibrations at the first resonant frequency are used to cut the tissue, thereby reducing the possibility of infection.

[0010] In some embodiments, the host device is configured to drive the transducer to generate ultrasonic vibrations at the second resonant frequency for a first duration, alternating between ultrasonic vibrations at the first resonant frequency for a second duration, when the active portion contacts tissue. This allows for continuous local sterilization of new wound surfaces as they are exposed by tissue cutting, further reducing the likelihood of infection.

[0011] In some embodiments, the horn further has an identification tag, and the transducer has a sensor for sensing the identification tag. In some embodiments, the sensor is configured to sense the identification tag when the electrical signal from the host is received for the Nth time (i.e., this time), if the threshold time has passed since the transducer received the electrical signal from the host for the N-1th time (i.e., the last time), and compare it with the identification tag sensed for the N-1th time. If the threshold time has not passed since the transducer received the electrical signal from the host for the N-1th time, the transducer directly generates ultrasonic vibrations based on the first resonant frequency and the second resonant frequency locked for the N-1th time. Since it is unlikely to replace the horn in a very short time, directly using the previously locked resonant frequency for operation can save operating time.

[0012] In some embodiments, if the sensed identification tag is the same as the identification tag sensed for the N-1th time, the transducer directly generates ultrasonic vibrations based on the first and second resonant frequencies locked for the N-1th time. If the sensed identification tag is different from the identification tag sensed for the N-1th time, the transducer reports the change in the identification tag of the waveguide rod to the host. The host is configured to, in response to the report of the change in the identification tag of the horn, adjust the frequency of the electrical signal to drive the transducer to rescan within the second frequency range, thereby locking the horn's new second resonant frequency and locking the new first resonant frequency to twice the new second resonant frequency, or adjust the frequency of the electrical signal to drive the transducer to rescan within the first frequency range, thereby locking the horn's new first resonant frequency and locking the new second resonant frequency to half the new first resonant frequency. Through the above operation, the frequency range can be automatically rescanned to lock the resonant frequency if the horn has been replaced after a period of time, while no time-consuming rescanning is required if the horn has not been replaced after a period of time, thereby facilitating the operation of the doctor and assistant while saving operating time. BRIEF DESCRIPTION OF THE DRAWINGS

[0013] The ultrasonic scalpel disclosed in this application and its operation are described below with reference to the accompanying drawings. It should be understood that the drawings are for illustration and explanation purposes only and are not intended to limit the scope of protection of this application. In addition, each drawing only schematically illustrates the position and combination relationship of each component and is not necessarily drawn to scale, among which:

[0014] Figure 1 is a schematic diagram showing an ultrasonic surgical system according to an embodiment of the present application;

[0015] Figure 2A is a diagram schematically showing a waveguide rod and an action portion of an ultrasonic scalpel according to an embodiment of the present application;

[0016] Figure 2B yes Figure 2A FIG. 1 is a schematic diagram of an enlarged cross section of a portion of the waveguide rod shown in the dotted box;

[0017] Figure 3 is a diagram schematically illustrating the frequency range and resonant frequency of an ultrasonic scalpel according to an embodiment of the present application;

[0018] Figure 4A-4B is a diagram schematically showing how the operating frequency of an ultrasonic scalpel changes over time according to an embodiment of the present application;

[0019] Figure 5 is a flowchart illustrating the operation of an ultrasonic scalpel according to an embodiment of the present application. DETAILED DESCRIPTION

[0020] The structure and operation of an ultrasonic scalpel according to an embodiment of the present application will be described below with reference to the accompanying drawings. Figure 1 FIG1 shows a schematic diagram of the components of the ultrasonic scalpel according to an embodiment of the present application. Figure 1 As shown, in some embodiments, the ultrasonic surgical system includes a host 10, a transducer 20, a handle 30, a shaft assembly 40, an action portion 50, and a foot switch 60. The shaft assembly 40 includes a waveguide rod and a sleeve, as described later. Figure 2A and Figure 2B In some embodiments, the cannula may include an outer cannula and an inner cannula (not shown) for closing and opening the distal end effector of the ultrasonic scalpel.

[0021] The main unit 10 provides an electrical signal to drive the transducer 20 to generate corresponding ultrasonic vibrations. In some embodiments, the main unit 10 includes a power converter, a clock, a processor, an amplifier circuit, and the like to generate the electrical signal required to drive the transducer 20, such as a square wave signal or a sinusoidal signal corresponding to a desired frequency. The transducer 20 includes a vibrating element, such as a piezoelectric element, that generates ultrasonic mechanical vibrations of a corresponding frequency in response to the electrical signal. In some embodiments, the vibration frequency of the vibrating element can substantially correspond to the frequency of the electrical signal from the main unit 10. In this case, by adjusting the frequency of the electrical signal output by the main unit 10, the frequency of the ultrasonic vibrations generated by the transducer 20 can be changed. As used herein, the "frequency of the electrical signal output by the main unit 10" and the "frequency of the ultrasonic vibrations generated by the transducer 20 driven by the electrical signal" are used interchangeably, as the two substantially correspond under normal operation. In some embodiments, one end of the waveguide rod of the shaft assembly 40 is connected to the transducer 20 (within the housing of the handle 30), while the other end of the waveguide rod of the shaft assembly 40 is the active portion 50, which contacts tissue to perform operations such as cutting. In this way, the shaft assembly 40 transmits the ultrasonic vibration generated by the transducer 20 to the acting part 50 .

[0022] High-power ultrasonic vibrations can instantly vaporize moisture in tissue cells in contact with the active portion 50, breaking protein hydrogen bonds and causing cell disintegration, thereby incising the tissue. Traditionally, frictional heat generated by high-power ultrasonic mechanical vibrations can assist in coagulation and hemostasis while incising the tissue. For example, a 55.5 kHz center frequency is currently used, which offers good stability for ultrasonic cutting.

[0023] However, although the frequency of 55.5kHz has a good cutting effect, it lacks a bactericidal effect on the incision. Therefore, after laparoscopic surgery, for example, performed using an ultrasonic scalpel, it is often necessary to give a large dose of antibiotics to prevent infection. Studies have shown that in addition to the above-mentioned cutting effect, ultrasonic vibrations can also induce cavitation of liquids. Specifically, under the action of ultrasonic vibrations, tiny bubble nuclei in the liquid vibrate. When the sound pressure reaches a certain intensity, the bubbles will expand rapidly and then suddenly close, generating shock waves when the bubbles close. The lifespan of bubbles in cavitation is about 0.1μs. When they collapse sharply, they can release huge energy and generate microjets with strong impact force at a speed of about 110m / s, and at the same time generate local high temperature and high pressure (5000K, 1800 atmospheres). The above-mentioned instantaneous high temperature and high pressure generated by cavitation can be used for local sterilization near surgical tissues.

[0024] The effect of cavitation is affected by factors such as power, frequency, and the physical properties of the liquid (for example, surface tension, viscosity, temperature, gas content, etc.). In particular, the higher the frequency of ultrasonic vibration, the stronger the power required to produce cavitation. In other words, within the reasonable power range of medical surgical ultrasonic scalpels, lower frequencies will be conducive to producing more significant cavitation, thereby improving the sterilization effect. Studies have shown that ultrasonic vibrations in the range of 20kHz to 38kHz have a good sterilization effect. However, the center frequency of 55.5kHz commonly used for cutting is outside this range, so it can only produce a weaker cavitation effect.

[0025] Based on this discovery, the present application proposes an ultrasonic scalpel that can periodically alternate or otherwise change the output of 55.5kHz ultrasonic vibrations and ultrasonic vibrations in the range of 20kHz to 38kHz, so that while cutting tissue with high-frequency ultrasonic vibrations, the stronger cavitation effect of low frequency can be used to perform local sterilization near the tissue, thereby reducing the need for postoperative antibiotics and improving prognosis.

[0026] In order to efficiently transmit the ultrasonic vibration generated by the transducer 20 to the action part 50, the shaft assembly 40 (especially, the waveguide rod 42 of the shaft assembly 40, as described below with reference to Figure 2A and Figure 2B(which will be described in more detail) needs to resonate at the frequency f of the ultrasonic vibration. According to the propagation principle of mechanical vibration, efficient conduction of ultrasonic vibration can be achieved when the effective propagation length of the shaft assembly 40 (especially the waveguide rod 42) is equal to an integer multiple nλ / 2 (n is a positive integer) of half the wavelength λ=v / f (v represents the propagation speed of the mechanical wave in the shaft assembly 40) of the ultrasonic vibration at the frequency f. It can be understood that the shaft assembly 40 of the ultrasonic knife (especially the waveguide rod 42) should have a reasonable length so as to avoid unnecessary increase in the difficulty of operation due to excessive length when the action part 50 is sufficient to touch the tissue to be operated. In some embodiments, the length of the waveguide rod 42 can be more than ten centimeters, more than twenty centimeters or more than thirty centimeters, etc., depending on the depth of the tissue to be operated, and meets the above-mentioned length requirement of nλ / 2.

[0027] Furthermore, in some embodiments, in order to simultaneously achieve efficient conduction of ultrasonic vibrations of a first frequency f1 of 55.5 kHz and ultrasonic vibrations of a second frequency f2 in the range of 20 kHz to 38 kHz, the second frequency f2 can be selected to be half of 55.5 kHz, that is, 27.75 kHz. In this case, the second wavelength λ2 corresponding to the second frequency f2 of 27.75 kHz is twice the first wavelength λ1 corresponding to the first frequency f1 of 55.5 kHz. Therefore, it can be understood that when the length of the waveguide rod 42 is an integer multiple nλ2 / 2 of half the second wavelength λ2, the length is also a corresponding integer multiple nλ2 / 2=2nλ1 / 2=nλ1 of the first wavelength λ1. Therefore, by determining the length of the waveguide rod 42 and the setting position of the support portion based at least in part on the second frequency f2 (e.g., 27.75 kHz), it is possible to take into account both efficient conduction of ultrasonic vibrations of a first frequency λ1 of 55.5 kHz and a second frequency λ2 of 27.75 kHz, as will be referred to later. Figure 2B Described in more detail.

[0028] Figure 2A FIG. 4 is a diagram schematically showing a waveguide rod 42 and an action portion 50 of an ultrasonic knife according to an embodiment of the present application. Figure 2A The lengths, diameters, etc. shown are for illustrative purposes only and are not drawn to scale, and therefore do not constitute any limitation to the waveguide rod 42 according to the present application. Figure 2B yes Figure 2A FIG. 4 is a schematic diagram of a partial enlarged cross section of the waveguide rod 42 shown in the dotted line frame. Figure 2BAs shown, the shaft assembly 40 is composed of an internal waveguide rod 42, a sleeve 44 sleeved around the waveguide rod 42, and support portions 46 sleeved at intervals along the length of the waveguide rod 42. The support portions 46 flexibly support the waveguide rod 42 to the inner wall of the sleeve 44, which has high mechanical strength, thereby improving the mechanical stability of the shaft assembly 40 and increasing the output intensity of the ultrasonic vibration at the action portion 50.

[0029] Without being limited by any theory, the support portion 46 can be positioned along the length of the waveguide rod 42 at a node formed by the propagation of ultrasonic vibrations along the waveguide rod 42, that is, at a location along the length of the waveguide rod 42 where the vibration amplitude is minimum. In this case, the support portion 46 can minimize the absorption of vibration energy while providing support, thereby increasing the power of the ultrasonic vibrations output by the active portion 50 while maintaining the output power of the transducer 20. Furthermore, by absorbing vibrations at frequencies other than the resonant frequency, the support portion 46 can also, to a certain extent, limit the propagation of vibrations at these frequencies, thereby concentrating the frequency of the output ultrasonic vibrations.

[0030] When using a first frequency of 55.5kHz and a second frequency of 27.75kHz simultaneously, the position of the support portion 46 needs to take into account the node positions at both frequencies. Since the second wavelength λ2 corresponding to the second frequency f2 is twice the first wavelength λ1 corresponding to the first frequency f1, the number of nodes n1 formed by the first frequency f1 propagating in the waveguide rod 42 of the shaft assembly 40 is twice the number of nodes n2 formed by the second frequency f2 propagating in the waveguide rod 42 of the shaft assembly 40. In other words, Figure 2B As shown, one of each pair of adjacent nodes n1 of the first frequency f1 coincides with the node n2 of the second frequency f2, while the other does not coincide with the node n2 of the second frequency f2. In other words, all the nodes n2 of the second frequency f2 coincide with the nodes n1 of the first frequency f1. Figure 2B As shown, in some embodiments, the support portions 46 are positioned along the length of the waveguide rod 42 to correspond to at least some of the node positions n2 generated by the waveguide rod 42 at the second frequency f2. In this case, the entire support portion 46 can absorb as little ultrasonic vibration energy as possible, thereby increasing the power of the ultrasonic vibration output to the active portion 50. Furthermore, by absorbing vibrations at frequencies other than the first frequency f1 and the second frequency f2, the support portions 46 can also, to a certain extent, limit the propagation of vibrations at other frequencies, thereby concentrating the frequency of the output ultrasonic vibrations.

[0031] In some embodiments, as Figure 2BAs shown, support portions 46 may not be provided at all node positions n2, but may be provided only at some of the node positions n2. Accordingly, the distance between two adjacent support portions 46 may be an integer multiple nλ2 / 2 (n is a positive integer) of half the wavelength λ2 / 2 corresponding to the second frequency f2, for example, d1 = 2×λ2 / 2 = λ2, d2 = λ2 / 2, and so on. It will be understood that the distance between these support portions 46 will be an integer multiple nλ1 of the wavelength λ1 corresponding to the first frequency f1.

[0032] It should be understood that while the first frequency is described as 55.5 kHz for device design purposes, in practice, the first frequency used can be selected within an acceptable frequency range centered around 55.5 kHz based on the actual resonant frequency of the waveguide rod 42. Furthermore, the second frequency used can be obtained by dividing the selected first frequency by two. Alternatively, the second frequency can be selected within an acceptable frequency range centered around 27.75 kHz based on the actual resonant frequency of the waveguide rod 42, and then the first frequency can be obtained by multiplying the selected second frequency by two. Specifically, although the waveguide rod 42 is designed to have a resonant frequency of 55.5 kHz, for example, the actual resonant frequency of the waveguide rod 42 is affected by factors such as manufacturing tolerances, material inhomogeneities, and temperature-induced mechanical property variations, and may deviate from the designed 55.5 kHz. Therefore, if the frequency of the electrical signal output by the main unit 10 is directly selected as 55.5 kHz, it may deviate from the actual resonant frequency of the waveguide rod 42, thereby reducing the transmission efficiency of the ultrasonic vibration.

[0033] Figure 3 Schematically illustrates the acceptable frequency range and resonant frequency of the ultrasonic scalpel according to an embodiment of the present application, wherein the horizontal axis represents the frequency f / kHz and the vertical axis represents the transmission efficiency e% of the ultrasonic energy. The transmission efficiency e% represents the percentage ratio of the power output from the waveguide rod 42 to the action part 50 to the power of the ultrasonic vibration generated by the transducer 20. Figure 3 As shown in FIG. 1 , the transmission efficiency e% of ultrasonic energy is higher at the resonant frequency f2 and f1=f2×2, and lower at other frequencies. In some embodiments, 55.5 kHz can be used as the center of the acceptable frequency interval, and the width of the acceptable frequency interval can be set to 2 kHz (i.e., ±1 kHz), thereby obtaining a first frequency interval [f1 - ,f1 + ], that is, 54.5kHz to 56.5kHz. Accordingly, the upper and lower limits f2 of the second frequency interval are - 、f2 + Can be the upper and lower limits f1 of the first frequency interval respectively - 、f1 + Half of, for example, f2- =27.25kHz to f2 + =28.25kHz. Each time a new waveguide rod 42 is replaced, or when the host 10 does not store the locked first resonant frequency f1 for other reasons, or when the doctor or assistant actively operates the host 10 to command scanning, the host 10 can scan the first frequency range [f1 - ,f1 + ] to determine the first resonant frequency f1 with the highest ultrasonic vibration transmission efficiency e% for tissue cutting, and divide the first resonant frequency f1 by two to obtain the second resonant frequency f2=f1 / 2 for sterilization. Alternatively, the host 10 can also be used in the second frequency range [f2 - ,f2 + ] scans within the inner chamber to determine the second resonant frequency f2 with the highest ultrasonic vibration transmission efficiency e% for sterilization. This second resonant frequency f2 is then multiplied by two to obtain the first resonant frequency f1 = f2 × 2 for tissue cutting. It should be noted that the center and width of the above acceptable frequency ranges are merely examples and can be flexibly selected based on actual needs.

[0034] Without being limited by any theory, scanning the acceptable frequency range to determine the resonant frequency corresponding to the highest ultrasonic vibration transmission efficiency e% can be performed by any method known in the art or to be developed in the future. In some embodiments, the host 10 can detect and compare the voltage and current phases at the power supply terminals of the transducer 20, and determine the frequency corresponding to the minimum phase difference as the resonant frequency within the acceptable frequency range.

[0035] The host 10 is configured to drive the transducer 20 by adjusting the frequency of the electrical signal of the host 10. The transducer 20 generates a resonance signal, and the host 10 detects the resonance signal and generates a signal in the second frequency range [f2 - ,f2 + ], thereby first locking the waveguide rod 42 at the second resonant frequency f2, and then locking the first resonant frequency f1 to twice the second resonant frequency f1 = f2 × 2. Alternatively, the frequency of the electrical signal of the host 10 is adjusted to drive the transducer 20. The transducer 20 generates a resonant signal, and the host 10 detects the resonant signal and generates a resonant signal in the first frequency interval [f1 - ,f1 + ] is scanned within, thereby first locking the first resonant frequency f1 of the waveguide rod 42, and then locking the second resonant frequency f2 to half of the first resonant frequency f2 = f1 / 2.

[0036] Figure 4A-4Bis a diagram schematically showing the change of the working frequency of the ultrasonic scalpel over time according to an embodiment of the present application, wherein the horizontal axis represents time, the vertical axis represents vibration frequency, and t=0 time represents the time when the action part 50 contacts the target tissue and the host 10 starts to output an electrical signal to drive the transducer 20 to generate ultrasonic vibration, for example, the time when the doctor steps on the switch 60. In some embodiments, as Figure 4A As shown, the vibration frequency is the second resonant frequency f2, for example, approximately 27.75 kHz, from time 0 to time t1. Then, after time t1, the vibration frequency changes to the first resonant frequency f1, for example, approximately 55.5 kHz. In this case, before cutting the target tissue at the first resonant frequency f1, the cavitation effect generated by the lower second resonant frequency f2 from time 0 to t1 can be used to locally sterilize the vicinity of the target tissue, thereby reducing the possibility of infection.

[0037] In some embodiments, as Figure 4B As shown, starting from time t=0, the vibration frequency is the second resonant frequency f2 within the first time period T1, for example, about 27.75kHz. Then, the vibration frequency changes to the first resonant frequency f1 at time t1 and lasts for the second time period T2, for example, about 55.5kHz. Thereafter, the vibration frequency changes to the second resonant frequency f2 at time t2 and lasts for the first time period T1, and so on. In this case, the vibration frequency periodically alternates between the second resonant frequency f2 and the first resonant frequency f1, thereby continuously sterilizing the new wound surface exposed as the tissue is cut, so as to further reduce the possibility of infection. It should be understood that Figure 4A and Figure 4B The time points and time periods shown are for illustrative purposes only and do not represent actual times, durations, or ratios thereof.

[0038] Figure 5 is a flow chart showing the operation of an ultrasonic scalpel according to an embodiment of the present application. As described above, the ultrasonic scalpel needs to lock the resonant frequency of the waveguide rod 42 to perform tissue cutting and sterilization operations. During the use of the ultrasonic scalpel, a scenario in which the waveguide rod 42 needs to be replaced may occur, for example, when the target tissue depth is too deep, the waveguide rod 42 is damaged or overheated, etc. At this time, it will take a certain amount of time to replace the waveguide rod 42, and the host 10 may need to rescan within the frequency range to lock the new actual resonant frequency of the waveguide rod 42. As an example, after replacing the waveguide rod 42, when the doctor steps on the switch 60, the host 10 automatically rescans the acceptable frequency range, so that the doctor or assistant does not need to operate a button or user interface on the host to command the host 10 to perform a scan. However, since the waveguide rod 42 may not be replaced after a long interval (for example, a more complex and time-consuming surgical operation is performed), it is expected that there is no need to perform a rescan after this interval to save operating time.

[0039] To facilitate operation and save time for the doctor or assistant, the present application envisions providing an identification tag (not shown, for example, an RFID tag) on ​​the waveguide rod 42 and providing a sensor (not shown, for example, an RFID sensor) on the transducer 20. The sensor on the transducer 20 recognizes the identification tag on the waveguide rod 42 to determine whether the waveguide rod 42 has been replaced.

[0040] Specifically, when the threshold time has not yet passed since the transducer 20 last generated ultrasonic vibrations in response to an electrical signal from the host 10 (e.g., the N-1th time), since it is unlikely that the waveguide rod 42 will be replaced within such a short time, the transducer 20 does not need to perform an identification operation in this operation (e.g., the Nth time), and the host 10 does not need to rescan (unless the doctor or assistant actively operates the host 10 to command a scan). Instead, the tissue cutting and sterilization operations are performed directly using the previously locked first resonant frequency f1 and second resonant frequency f2. When the threshold time has passed since the transducer 20 last generated ultrasonic vibrations in response to an electrical signal from the host 10, the sensor senses the identification tag and compares it with the identification tag sensed last time. When the identification tag sensed is the same as the identification tag sensed last time, it indicates that the waveguide rod 42 has not been replaced, so the transducer 20 does not need to be operated, and the host 10 does not need to be rescanned (unless the doctor or assistant actively operates the host 10 to command a scan). Instead, the previously locked first resonant frequency f1 and second resonant frequency f2 are directly used for tissue cutting and sterilization operations, thereby saving operation time.

[0041] Accordingly, when the sensed identification tag differs from the identification tag sensed last time, the change in the identification tag of the waveguide rod 42 is reported to the host 10 to indicate that the waveguide rod 42 has been replaced. In response to the report of the change in the identification tag of the waveguide rod 42, the host 10 can adjust the frequency of the electrical signal to drive the transducer 20 to rescan within the frequency range to lock onto the new first resonant frequencies f1' and f2'. In some embodiments, the host 10 can scan within a second frequency range (e.g., 27.25 kHz to 28.25 kHz) to determine the new second resonant frequency f2' of the waveguide rod 42. This second resonant frequency f2' is then multiplied by two to obtain the new first resonant frequency f1' of the waveguide rod 42. Alternatively, in other embodiments, the host can scan within a first frequency range (e.g., 54.5 kHz to 56.5 kHz) to determine the new first resonant frequency f1' of the waveguide rod 42. This first resonant frequency f1' is then divided by two to obtain the new second resonant frequency f2' of the waveguide rod 42.

[0042] It should be understood that various modifications may be made to the disclosed apparatus. Therefore, the above description should not be construed as limiting, but merely as illustrative of aspects of the present disclosure. Those skilled in the art will envision other modifications within the scope and spirit of the present disclosure. For example, any and all features of one described aspect may be appropriately incorporated into another aspect, and the beneficial effects of such features in one aspect may be expected to be realized in another aspect.

Claims

1. An ultrasonic surgical system, characterized in that: include: A host computer generates an electrical signal for generating ultrasonic vibrations; a transducer that receives the electrical signal and generates ultrasonic vibration in response to the electrical signal; a shaft assembly, the shaft assembly comprising a waveguide rod, a first end of the waveguide rod being connected to the transducer to conduct the ultrasonic vibration generated by the transducer; as well as an action portion, located at the second end of the waveguide rod, configured to receive the ultrasonic vibration generated by the transducer and transmitted through the waveguide rod, and output the received ultrasonic vibration, The host is configured to adjust the electrical signal to drive the transducer to generate ultrasonic vibrations within a first frequency range or a second frequency range, wherein the upper frequency limit and the lower frequency limit of the first frequency range are respectively twice the upper frequency limit and the lower frequency limit of the second frequency range. wherein the waveguide rod has a first resonant frequency in the first frequency range and a second resonant frequency in the second frequency range, and the first resonant frequency is twice the second resonant frequency; The first frequency range is 54.5 kHz to 56.5 kHz, and the second frequency range is 27.25 kHz to 28.25 kHz; The host is configured to, when the active part contacts the tissue, drive the transducer to generate ultrasonic vibrations of the second resonant frequency for a first duration and then generate ultrasonic vibrations of the first resonant frequency for a second duration by changing the frequency of the electrical signal; or, the host is configured to, when the active part contacts the tissue, drive the transducer to generate ultrasonic vibrations of the second resonant frequency for a first duration and ultrasonic vibrations of the first resonant frequency for a second duration alternately.

2. The ultrasonic surgical system according to claim 1, wherein The host is configured to drive the transducer by adjusting the frequency of the electrical signal of the host, and the transducer generates a resonant signal. The host detects the resonant signal and scans it within the second frequency range, thereby first locking the waveguide rod at the second resonant frequency and then locking the first resonant frequency to twice the second resonant frequency; or, the host detects the resonant signal and scans it within the first frequency range, thereby first locking the first resonant frequency of the waveguide rod and then locking the second resonant frequency to half of the first resonant frequency.

3. The ultrasonic surgical system according to claim 1, wherein The waveguide rod is used to provide a conduction path for the ultrasonic vibration, and the shaft assembly further includes: A sleeve is provided around the waveguide rod. A plurality of support parts are sleeved on the waveguide rod at intervals along the length direction of the waveguide rod, and flexibly support the waveguide rod in the sleeve.

4. The ultrasonic surgical system according to claim 3, wherein: Positions of the support portions along the length direction of the waveguide rod correspond to at least some of the node positions generated by the waveguide rod at the second resonant frequency.

5. The ultrasonic surgical system according to claim 2, wherein: The waveguide rod further has an identification tag, and the transducer has a sensor for sensing the identification tag.

6. The ultrasonic surgical system according to claim 5, wherein: The sensor is configured to, when receiving the electrical signal from the host for the Nth time, sense the identification tag and compare it with the identification tag sensed for the N-1th time if a threshold time has passed since the transducer received the electrical signal from the host for the N-1th time, and If the threshold time has not passed since the transducer received the electrical signal from the host for the (N-1)th time, the transducer generates ultrasonic vibrations directly based on the first and second resonant frequencies locked for the (N-1)th time.

7. The ultrasonic surgical system according to claim 6, wherein: If the sensed identification tag is the same as the identification tag sensed for the N-1th time, the transducer generates ultrasonic vibration directly based on the first resonant frequency and the second resonant frequency locked for the N-1th time. If the sensed identification tag is different from the identification tag sensed for the N-1th time, the transducer reports the change of the identification tag of the waveguide rod to the host, and The host is configured to, in response to a report of a change in the identification tag of the waveguide rod: By adjusting the frequency of the electrical signal to drive the transducer to rescan within the second frequency range, the new second resonant frequency of the waveguide rod is locked, and the new first resonant frequency is locked to twice the new second resonant frequency, or The frequency of the electrical signal is adjusted to drive the transducer to rescan within the first frequency range, thereby locking the new first resonant frequency of the waveguide rod and locking the new second resonant frequency to half of the new first resonant frequency.

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