CN115382119B - Pulse output control method and therapeutic apparatus - Google Patents
Pulse output control method and therapeutic apparatus Download PDFInfo
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N7/02—Localised ultrasound hyperthermia
- A61N7/022—Localised ultrasound hyperthermia intracavitary
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/01—Measuring temperature of body parts ; Diagnostic temperature sensing, e.g. for malignant or inflamed tissue
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N2007/0004—Applications of ultrasound therapy
- A61N2007/0008—Destruction of fat cells
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
- A61N2007/0043—Ultrasound therapy intra-cavitary
Abstract
The invention discloses a control method of pulse output and a therapeutic apparatus, wherein the control method of pulse output comprises the following steps: step S10, outputting detection pulses to target tissues; step S20, receiving reflected waves fed back by the target tissue, and detecting the temperature of the target tissue according to the received reflected waves; and step S30, adjusting the power of the therapeutic pulse output to the target tissue according to the detected temperature of the target tissue. The invention realizes nondestructive temperature detection of the inside of the target tissue of the treatment area so as to improve the treatment effect.
Description
Technical Field
The invention relates to the field of ultrasonic treatment equipment, in particular to a pulse output control method and a therapeutic apparatus.
Background
High intensity focused ultrasound (HIFU: highIntensity focused ultrasound), unlike laser and RF (Radio Frequency) high frequency devices, concentrates energy in a non-invasive manner at selected portions without any damage to the skin surface, i.e., focuses the released ultrasound at a focal point that is a specific location to generate heat, thereby inducing a sharp rise in the temperature at the treatment site. By such warming function, the fat cells are induced to coagulate and necrotize without leaving side effects on various affected parts, and the therapy is performed.
The accurate temperature of the focusing point cannot be obtained in the treatment process by the existing equipment, and the output power range is preset only through experimental experience, so that the temperature of the focusing point falls in a rough range, the obtained treatment effect is required to be improved, and the risk of scalding a treatment area caused by overhigh temperature exists.
Disclosure of Invention
The invention mainly aims to provide a pulse output control method and a therapeutic apparatus, which aim to realize nondestructive temperature detection of the inside of target tissues of a treatment area so as to improve the treatment effect.
In order to achieve the above object, the present invention provides a control method of pulse output, comprising the steps of:
step S10, outputting detection pulses to target tissues;
step S20, receiving reflected waves fed back by the target tissue, and detecting the temperature of the target tissue according to the received reflected waves;
and step S30, adjusting the power of the therapeutic pulse output to the target tissue according to the detected temperature of the target tissue.
Optionally, the method for controlling pulse output specifically includes the following steps:
in outputting a therapeutic pulse to a target tissue periodically, outputting a detection pulse to the target tissue before any one of the therapeutic pulses and after any one of the therapeutic pulses.
Optionally, before any one of the therapeutic pulses, the method for controlling pulse output specifically includes the following steps:
the steps S10 to S30 are repeatedly performed, wherein the step S30 specifically includes the following steps:
and stopping the treatment pulse and displaying the prompt information when the detected temperature is greater than or equal to the first preset temperature.
Optionally, before any one of the therapeutic pulses, the method for controlling pulse output specifically includes the following steps:
the steps S10 to S30 are repeatedly performed, wherein the step S30 specifically includes the following steps:
and outputting a therapeutic pulse with preset power to the target tissue when the detected temperature is less than the first preset temperature.
Optionally, after any one of the therapeutic pulses, the method for controlling pulse output specifically includes the following steps:
the steps S10 to S30 are repeatedly performed, wherein the step S30 specifically includes the following steps:
and when the detected temperature is higher than a third preset temperature, the power of the therapeutic pulse is reduced.
Optionally, when the detection pulse is output to the target tissue for the first time, when the detected temperature is smaller than the first preset temperature, the method specifically comprises the following steps after outputting the treatment pulse with the preset power to the target tissue:
the steps S10 to S30 are repeatedly performed, wherein the step S30 specifically includes the following steps:
and when the detected temperature is higher than a third preset temperature, the power of the therapeutic pulse is reduced.
Optionally, the step S20 specifically includes the following steps:
and receiving the reflected wave output by the target tissue, and calculating the temperature of the target tissue according to the time offset of the reflected wave at the reference temperature and the time offset of the detected reflected wave, wherein the time offset of the reflected wave is specifically the time interval from outputting the detection pulse to receiving the reflected wave.
Optionally, the step S20 specifically further includes the following steps:
the reflected wave output from the target tissue is received, and the temperature of the target tissue is calculated from the frequency of the reflected wave at the reference temperature and the frequency of the detected reflected wave.
Optionally, the step S20 specifically further includes the following steps:
the reflected wave output by the target tissue is received, and the temperature of the target tissue is calculated from the reflected wave energy at the reference temperature and the energy of the detected reflected wave.
The invention provides an ultrasonic therapeutic apparatus, comprising:
a controller including a memory and a processor, wherein the memory stores a pulse output control program, and the pulse output control program realizes the steps of the pulse output control method when being executed by the processor;
the ultrasonic generating unit is connected with the controller and is used for outputting therapeutic pulses and/or detection pulses according to the control instruction output by the controller;
and the energy adjusting unit is connected with the controller and is used for adjusting and outputting the energy of the therapeutic pulse and/or the detection pulse according to the control signal of the controller.
The control method of the invention through pulse output comprises the following steps: step S10, outputting detection pulses to target tissues; step S20, receiving reflected waves fed back by the target tissue, and detecting the temperature of the target tissue according to the received reflected waves; and step S30, adjusting the power of the therapeutic pulse output to the target tissue according to the detected temperature. The control method aims at temperature feedback of therapeutic pulse output power, and the detected temperature and the magnitude of the therapeutic pulse output power have a matching relationship. The method of detecting the temperature of the target tissue is based on reflected wave detection of the detection pulse. When the ultrasonic therapeutic device works, the transducer transmits detection ultrasonic pulses to target tissues, receives reflected pulse signals, calculates the temperature of the target tissues by detecting the change of the reflected pulse signals in the time domain, the frequency domain or the energy domain, realizes nondestructive temperature detection of the target tissues, and adjusts the output power of ultrasonic therapeutic pulses according to the temperature change feedback. Compared with the existing measurement method for measuring the skin surface, the temperature detection result of the target tissue based on reflected wave detection is obtained based on subcutaneous target tissue, the detection result is more accurate, the output power of the ultrasonic treatment pulse is adjusted according to the temperature change feedback, the treatment effect is improved, and damage caused by overhigh temperature is avoided. The invention realizes nondestructive temperature detection of the inside of the target tissue of the treatment area so as to improve the treatment effect.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings that are required in the embodiments or the description of the prior art will be briefly described, and it is obvious that the drawings in the following description are only some embodiments of the present invention, and other drawings may be obtained according to the structures shown in these drawings without inventive effort for a person skilled in the art.
FIG. 1 is a flowchart illustrating an embodiment of a method for controlling pulse output according to the present invention;
FIG. 2 is a schematic diagram of the operation of the present invention for outputting detection pulses;
FIG. 3 is a schematic diagram of an output therapeutic pulse waveform according to an embodiment of the method for controlling pulse output of the present invention;
FIG. 4 is a schematic diagram of an output detection pulse waveform according to an embodiment of a method for controlling pulse output of the present invention;
fig. 5 is a waveform diagram illustrating output pulse power adjustment according to an embodiment of the present invention.
The achievement of the objects, functional features and advantages of the present invention will be further described with reference to the accompanying drawings, in conjunction with the embodiments.
Detailed Description
The following description of the embodiments of the present invention will be made clearly and fully with reference to the accompanying drawings, in which it is evident that the embodiments described are only some, but not all embodiments of the invention. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention. It should be noted that, if directional indications (such as up, down, left, right, front, and rear … …) are included in the embodiments of the present invention, the directional indications are merely used to explain the relative positional relationship, movement conditions, etc. between the components in a specific posture (as shown in the drawings), and if the specific posture is changed, the directional indications are correspondingly changed.
In addition, if there is a description of "first", "second", etc. in the embodiments of the present invention, the description of "first", "second", etc. is for descriptive purposes only and is not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In addition, the technical solutions of the embodiments may be combined with each other, but it is necessary to base that the technical solutions can be realized by those skilled in the art, and when the technical solutions are contradictory or cannot be realized, the combination of the technical solutions should be considered to be absent and not within the scope of protection claimed in the present invention.
Referring to fig. 1 and 2, in an embodiment of the invention, the pulse output control method includes the following steps:
step S10, outputting detection pulses to target tissues;
step S20, receiving reflected waves fed back by the target tissue, and detecting the temperature of the target tissue according to the received reflected waves;
and step S30, adjusting the power of the therapeutic pulse output to the target tissue according to the detected temperature of the target tissue.
The ultrasonic therapeutic apparatus outputs ultrasonic energy to subcutaneous tissue to achieve therapeutic effect, and ultrasonic pulses form a heat dispersion region in the target tissue, so that focused ultrasonic energy acts on the subcutaneous tissue, and the therapeutic range of the ultrasonic therapeutic apparatus is diffused by diffusing the region on which the focused ultrasonic energy acts. The ultrasonic therapeutic apparatus adjusts the output of ultrasonic energy in real time according to the temperature of the heat dispersion area in the therapeutic process, so that the formed heat dispersion area needs to be at a proper temperature to meet the therapeutic effect. If the temperature of the heat dispersion area is too high, the user can be provided with a tingling sensation, the user experience is affected, even skin scald can be caused under serious conditions, and if the temperature of the heat dispersion area is too low, the effect of ultrasonic treatment is not strong, and the effect is not obvious.
The accurate temperature of the focus point cannot be obtained in the treatment process by the existing equipment, and the position acted by the treatment pulse is subcutaneous target tissue, so that the common temperature sensor can only detect the temperature of the skin surface, and the subcutaneous tissue temperature is not accurately measured, so that the treatment output power cannot be accurately regulated, and the treatment effect of the ultrasonic therapeutic instrument is affected.
Due to the difference of acoustic parameters such as acoustic impedance, density, sound velocity and the like of tissues, back scattering (weak difference) or reflection (strong difference) can occur at the place where the acoustic parameters change in the process of the propagation of the ultrasonic wave in the tissue body. Part of the ultrasound waves are thus transmitted backwards and the remainder continues to propagate deep in the tissue, thus producing a feedback echo.
Under ultrasonic pulse wave scanning, biological tissues (liver, spleen, kidney and the like) are scattering models of discrete random media, and the time domain, the frequency domain and the energy domain of the discrete random media model have a corresponding relation with temperature. The temperature of the subcutaneous target tissue can thus be detected from the changes in the time, frequency and energy domains of the received feedback echoes by outputting detection pulses.
In this embodiment, the transducer emits an ultrasonic pulse for detection to the target tissue, the ultrasonic pulse for detection generates a feedback echo in the process of propagating to the target tissue, the transducer receives the reflected pulse signal, sends the information of the reflected pulse signal to the control host, and the control host writes a discrete random medium model related to ultrasonic waves in advance, and calculates the temperature of the target tissue according to the time offset, the frequency and the energy of the reflected pulse signal.
Through the working process, the temperature of the target tissue is calculated by detecting the change of the reflected pulse signal, the nondestructive temperature detection of the target tissue is realized, the output power of the ultrasonic treatment pulse is adjusted according to the temperature change feedback, the treatment effect is improved, and the damage caused by overhigh temperature is avoided.
In step S10 to step S30, the pulses output from the transducer to the target tissue include a detection pulse and a treatment pulse, the detection pulse is output to detect the temperature of the target tissue, and then the output power of the treatment pulse is adjusted according to the temperature of the target tissue.
When the ultrasonic wave detection device is operated, the transducer outputs detection pulses to subcutaneous target tissues, the target tissues output feedback pulses to the transducer after receiving the detection pulses, and back scattering (weak difference) or reflection (strong difference) can occur at the place where the acoustic parameters change in the process of the propagation of the ultrasonic wave in the tissue body due to the difference of acoustic parameters such as acoustic impedance, density and sound velocity of the tissue. The discrete random medium model of the biological tissue under the action of the ultrasonic pulse wave is written into the control system of the ultrasonic therapeutic apparatus in advance, the temperature of the target tissue can be detected by detecting the feedback pulse, and the temperature information can be extracted by analyzing the change of the ultrasonic scattering signal in the time domain, the frequency domain or the energy domain. Compared with the existing temperature measurement method for setting treatment, the temperature measurement method in the embodiment can accurately measure the temperature of subcutaneous target tissues, and measurement errors are reduced.
When the ultrasonic treatment is carried out, the output of ultrasonic energy to subcutaneous target tissue is controlled to realize the treatment effect, and the temperature of the target tissue and the size of ultrasonic output power have a matching relationship, namely the ultrasonic output power is set for the temperature of the ultrasonic target tissue to realize the expected treatment effect. Compared with the existing measurement method for measuring the skin surface, the temperature detection result of the target tissue based on reflected wave detection is obtained based on subcutaneous target tissue, and the detection result is more accurate. As the nondestructive temperature detection of the target tissue is realized in the embodiment, the measurement result is more accurate, the output power of the ultrasonic treatment pulse is adjusted according to the temperature change feedback, the treatment effect is improved, and the damage caused by overhigh temperature is avoided.
The control method of the invention through pulse output comprises the following steps: step S10, outputting detection pulses to target tissues; step S20, receiving reflected waves fed back by the target tissue, and detecting the temperature of the target tissue according to the received reflected waves; and step S30, adjusting the power of the therapeutic pulse output to the target tissue according to the detected temperature. The control method aims at temperature feedback of therapeutic pulse output power, and the detected temperature and the magnitude of the therapeutic pulse output power have a matching relationship. The method of detecting the temperature of the target tissue is based on reflected wave detection of the detection pulse. When the ultrasonic therapeutic device works, the transducer transmits detection ultrasonic pulses to target tissues, receives reflected pulse signals, calculates the temperature of the target tissues by detecting the change of the reflected pulse signals in the time domain, the frequency domain or the energy domain, realizes nondestructive temperature detection of the target tissues, and adjusts the output power of ultrasonic therapeutic pulses according to the temperature change feedback. Compared with the existing measurement method for measuring the skin surface, the temperature detection result of the target tissue based on reflected wave detection is obtained based on subcutaneous target tissue, the detection result is more accurate, the output power of the ultrasonic treatment pulse is adjusted according to the temperature change feedback, the treatment effect is improved, and damage caused by overhigh temperature is avoided. The invention realizes nondestructive temperature detection of the inside of the target tissue of the treatment area so as to improve the treatment effect.
In one embodiment, when periodically outputting therapeutic pulses to a target tissue, one of the detection pulses is output to the target tissue before any one of the therapeutic pulses and after any one of the therapeutic pulses.
In this embodiment, the ultrasonic treatment energy is pulsed toward the tissue to be treated, with two adjacent treatment pulses being in a time interval sufficient to complete the transmission and reception of the detection pulses. Typically, the transmission frequency is 2Hz-50Hz, i.e. the time interval between two adjacent therapeutic pulses is 20ms-500ms.
Referring specifically to fig. 3, there are three therapeutic pulse output periods, i.e., a period of 0 to T1, a period of T2 to T3, and a period of T4 to T5, in total, a period of 0 to T5, a period of T1 to T2, and a period of T3 to T4, which are two intervals. After the treatment pulse is finished, a detection pulse is output for detecting the change of the temperature of the subcutaneous target tissue at intervals before the next treatment pulse is output, so that the power of the next treatment pulse is adjusted.
It is necessary to detect the temperature once before any one of the therapeutic pulses is output and after any one of the therapeutic pulses is output, and to adjust the output of the pulses according to the detection of the temperature.
Wherein, before the therapeutic pulse is output, the therapeutic pulse output/non-output is controlled according to the detection of the temperature. After the therapeutic pulse is output, the power of the next therapeutic pulse is adjusted according to the detected temperature.
For example, after the treatment pulse output in the time period of 0 to T1 is ended, two detection pulses are output in the time period of T1 to T2, after the first detection pulse is detected, the energy converter controls the power of the treatment pulse to be increased according to the temperature detected by the detection pulse, then a second detection pulse is output, the energy converter outputs the treatment pulse in the time period of T2 to T3 according to the detected temperature, and the power of the treatment is the power regulated by the energy converter in the time period of T1 to T2. After the treatment pulse output in the time period of T2-T3 is finished, two detection pulses are output in the time period of T3-T4, after the first detection pulse is detected, the energy converter controls the power of the treatment pulse to be reduced according to the temperature detected by the detection pulse, then a second detection pulse is output, the energy converter outputs the treatment pulse according to the time period of the detected temperature T4-T5, and the power of the treatment pulse is the power regulated to be reduced by the energy converter in the time period of T3-T4.
The controller divides the temperature detected by the detection pulse into a plurality of preset temperature intervals, and the transducer adjusts the power of the subsequent output treatment pulse according to the control logic of each preset temperature interval. The control of the power of the therapeutic pulse is realized based on the temperature detected by the detection pulse, and the corresponding relation between the temperature of the target tissue and the power of the therapeutic pulse is written in the controller in advance.
In one embodiment, before any one of the therapeutic pulses, the pulse output control method specifically includes the following steps:
the steps S10 to S30 are repeatedly performed, wherein the step S30 specifically includes the following steps:
and stopping the treatment pulse and displaying the prompt information when the detected temperature is greater than or equal to the first preset temperature.
In this embodiment, the first preset temperature is a safe temperature of the subcutaneous target tissue, and exceeding this temperature may cause the skin to be scalded. The ultrasonic energy is output for many times at the same position of the skin, so that the energy at the position is too high, the temperature of subcutaneous target tissues is too high, not only the expected treatment effect cannot be produced, but also the side effect of scalding the skin can be produced. The transducer should not output therapeutic pulses when the temperature of the subcutaneous target tissue is detected to be too high.
When the detected speed is higher than the first preset temperature, the temperature of the subcutaneous target tissue is considered to be large enough, if the ultrasonic treatment transducer outputs treatment pulses to the target tissue, the energy at the position is too high, the expected treatment effect cannot be achieved, and the side effect of scalding the skin can be generated.
In one embodiment, before any one of the therapeutic pulses, the pulse output control method specifically includes the following steps:
the steps S10 to S30 are repeatedly performed, wherein the step S30 specifically includes the following steps:
and outputting a therapeutic pulse with preset power to the target tissue when the detected temperature is less than the first preset temperature.
In this embodiment, the first preset temperature is a safe temperature of the subcutaneous target tissue, and when the first preset temperature is less than the first preset temperature, the transducer controls the output pulse of the preset power to start the treatment of the treatment area.
In one embodiment, after any one of the therapeutic pulses, the pulse output control method specifically includes the following steps:
the steps S10 to S30 are repeatedly performed, wherein the step S30 specifically includes the following steps:
and when the detected temperature is less than the second preset temperature, the power of the therapeutic pulse is increased.
In this embodiment, when the detected temperature is less than the second preset temperature, the temperature of the target tissue is too low, and the output energy of the therapeutic pulse is small, which is insufficient to meet the therapeutic requirement. And transmitting detection pulses to the target tissue after the treatment pulses are transmitted, and detecting the temperature change of the target tissue after receiving the treatment energy, so that the temperature of the target tissue is smaller than the minimum value of the preset temperature range, and increasing the power of the next treatment pulse.
At this time, the next treatment pulse power is increased, the output efficiency of ultrasonic energy is increased, the temperature of the target tissue is close to the standard temperature range, the temperature of the treatment area is in the standard temperature range, and a better treatment effect is obtained.
In one embodiment, after any one of the therapeutic pulses, the pulse output control method specifically includes the following steps:
the steps S10 to S30 are repeatedly performed, wherein the step S30 specifically includes the following steps:
and when the detected temperature is higher than a third preset temperature, the power of the therapeutic pulse is reduced.
In this embodiment, when the detected temperature is greater than the third preset temperature, the temperature of the target tissue is high but within the safe temperature range, the output energy of the therapeutic pulse is high, and the therapeutic effect is poor. And transmitting detection pulses to the target tissue after the treatment pulses are transmitted, and detecting the temperature change of the target tissue after receiving the treatment energy, so that the temperature of the target tissue is larger than the maximum value of the standard temperature range, and reducing the power of the next treatment pulses.
At this time, the next treatment pulse power is reduced, the output efficiency of ultrasonic energy is reduced, the temperature of the target tissue is close to the standard temperature range, the temperature of the treatment area is in the standard temperature range, and a better treatment effect is obtained.
The temperature measurement is realized by detecting the emission and the reception of the pulse, and can measure any one of the time, the frequency and the energy of the reflected wave. The corresponding relation between the tissue temperature value and the time, frequency and energy of the reflected wave is obtained through experiments and stored in the ultrasonic therapeutic instrument system, and the controller detects the temperature according to the variation of the time, frequency and energy of the reflected wave.
In one embodiment, the step S20 specifically includes the following steps:
and receiving the reflected wave output by the target tissue, and calculating the temperature of the target tissue according to the time offset of the reflected wave at the reference temperature and the time offset of the detected reflected wave, wherein the time offset of the reflected wave is specifically the time interval from outputting the detection pulse to receiving the reflected wave.
In this embodiment, when the temperature of the target tissue changes, the reflected sound pulse time will shift correspondingly, so that the temperature value of the target tissue can be calculated according to the reflected wave time at the reference temperature and the detected time shift change. The specific formula for calculating the target tissue temperature is as follows:
wherein t (z) is the reflected wave time at the reference temperature, t 0 (z) is the time at which the reflected wave is detected, z is the depth of the target tissue, where θ (ζ) is the temperature at depth ζ, c (ζ, θ (ζ)) represents the speed of sound at depth ζ and temperature θ (ζ), and α (ζ) represents the coefficient of thermal expansion at ζ.
In an embodiment, the step S20 specifically further includes the following steps:
the reflected wave output from the target tissue is received, and the temperature of the target tissue is calculated from the frequency of the reflected wave at the reference temperature and the frequency of the detected reflected wave.
In this embodiment, when the temperature of the target tissue changes, the frequency of the reflected sound wave pulse changes accordingly, so that the temperature value of the target tissue can be calculated according to the frequency of the reflected wave at the reference temperature and the detected frequency shift change. The specific formula for calculating the target tissue temperature is as follows:
wherein T is temperature, and alpha is thermal expansion coefficient of biological tissue; d, d 0 And c 0 Respectively the reference temperature T 0 The average scattering distance and sound velocity of biological tissue under c (T) is the sound velocity function of the target tissue with respect to temperature T, Δfk is the difference between the reflected wave frequency at the reference temperature and the detected reflected wave frequency.
In an embodiment, the step S20 specifically further includes the following steps:
the reflected wave output from the target tissue is received, and the temperature of the target tissue is calculated from the frequency of the reflected wave at the reference temperature and the frequency of the detected reflected wave.
In this embodiment, when the temperature of the target tissue changes, the peak value of the energy of the reflected sound wave pulse changes accordingly, so that the temperature value of the target tissue can be calculated from the reflected wave energy at the reference temperature and the detected energy change. The specific formula for calculating the target tissue temperature is as follows:
H/R and δ are the amplitude and duration of the incident burst sound pressure, R is the distance between the transducer and the scattering tissue volume, α (T) is the attenuation coefficient within the tissue volume, and is a function of temperature; c (T) is the speed of sound as a function of temperature, η (T) is the scattering coefficient of the tissue and is also a function of temperature, ar is the effective receiving area, ρ0, c0, α0 are the density, speed of sound, attenuation coefficient of water, respectively. If the scattering coefficient is considered to be proportional to the scattering cross section of small particles, η (T) in the equation may be estimated from the following relationship:
where ρm, cm are the density and sound velocity of the medium, ρs, cs are the density and sound velocity of the scattering particles.
In an embodiment of the present invention, the method for modulating the ultrasonic output pulse further includes the following steps:
the duty cycle and/or voltage amplitude of each of the therapeutic pulses is adjusted to control the output power of the therapeutic pulses.
In this embodiment, the output ultrasonic energy is controlled by controlling the ultrasonic output power and/or the ultrasonic pulse output repetition frequency. The ultrasonic energy output by the ultrasonic therapeutic transducer is realized by controlling ultrasonic output power and ultrasonic pulse output repetition frequency. The ultrasonic pulse output repetition frequency is the number of times output by the ultrasonic therapeutic transducer in a period of time, and the ultrasonic output power is the power output by the ultrasonic therapeutic transducer once.
Referring to fig. 4, in one embodiment of the invention, the pulse width and/or interval width of the therapeutic pulses is adjusted to control the duty cycle of the therapeutic pulses.
In this embodiment, the ultrasonic output power of the transducer is controlled by modulating the pulse to be output, specifically by modulating the time and amplitude of the pulse to be output by the ultrasonic unit. The time of the pulse to be output of the ultrasonic unit is longer, the amplitude of the pulse to be output is larger, and the time of the pulse to be output of the ultrasonic unit is longer.
Referring to fig. 4, in an embodiment of the present invention, the frequency of the pulses to be output by the ultrasound unit and/or the duty cycle of the pulses to be output by the ultrasound unit are controlled to control the time at which the pulses are to be output by the ultrasound unit.
The frequency of the pulse to be output by the ultrasonic unit and/or the duty ratio of the pulse to be output by the ultrasonic unit are/is controlled to control the time of the pulse to be output by the ultrasonic unit, wherein the larger the frequency of the pulse to be output by the ultrasonic unit is, the larger the time of the pulse to be output by the ultrasonic unit is, and the larger the duty ratio of the pulse to be output by the ultrasonic unit is, the larger the time of the pulse to be output by the ultrasonic unit is.
In an embodiment of the present invention, the controller further includes a power adjustment unit and an ultrasonic driving unit, where the power adjustment unit configures working parameters of the ultrasonic treatment probe, and the ultrasonic driving unit is configured to drive the ultrasonic treatment probe to work according to the working parameters configured by the power adjustment unit;
the ultrasonic driving unit is used for driving the ultrasonic treatment probe to work according to the ultrasonic output power and the ultrasonic pulse output repetition frequency configured by the power adjusting unit.
In this embodiment, the ultrasonic energy adopts a dotting type pulse output mode, each ultrasonic energy is dotted, an energy focusing point is formed in the tissue in sequence, and the adjustment of ultrasonic energy output comprises the following two aspects.
Controlling and adjusting the output frequency, namely changing the time interval of two adjacent ultrasonic energy, and changing the number of focal points beaten in unit time; when the output frequency is increased, the ultrasonic energy of each emission is unchanged, and the number of the emitted ultrasonic energy in unit time is increased, so that the ultrasonic energy output in unit time is increased.
Controlling and adjusting ultrasonic power, namely changing the amplitude or pulse width of an ultrasonic power supply voltage waveform, so as to change the ultrasonic energy of each generation; when the single-shot ultrasonic energy is increased, the number of the shots in unit time is unchanged, and the output ultrasonic energy in unit time is increased.
The invention provides a controller.
In an embodiment of the present invention, the controller includes a memory and a processor, where the memory stores a pulse output control program, and the pulse output control program when executed by the processor implements the steps of the pulse output control method as described above.
The controller executes the steps of the control method including the pulse output as described above, and the specific working steps of the controller refer to the above embodiments, and since the controller of the present invention adopts all the technical solutions of all the embodiments, at least the controller has all the beneficial effects brought by the technical solutions of the embodiments, which are not described in detail herein.
The invention also provides an ultrasonic therapeutic apparatus, comprising:
the controller as described above may be configured to control,
a transducer connected with the controller for outputting therapeutic pulse and/or detection pulse according to the control instruction output by the controller
And the power adjusting unit is respectively connected with the controller and the transducer and is used for adjusting the power of the output pulse of the transducer according to the control signal of the controller.
In an embodiment of the present invention, the power adjustment unit is configured to configure time and/or voltage amplitude of a pulse to be output by the ultrasonic unit to configure ultrasonic output power, and the ultrasonic driving unit is configured to drive the ultrasonic treatment probe to work according to the ultrasonic output power and the ultrasonic pulse output repetition frequency configured by the power adjustment unit.
In this embodiment, the power adjusting unit is specifically configured to modulate a pulse to be output of the transducer, and the ultrasonic output power is configured by controlling the time and/or the voltage amplitude of the pulse to be output of the ultrasonic unit of the transducer, so as to drive the ultrasonic therapeutic probe to work.
The handle is moved by the operator during treatment, the ultrasonic window is kept to be closely adhered to the skin to slide, ultrasonic energy is output in a pulse mode, and the position of ultrasonic energy output is controlled by continuously moving the handle, so that the treatment effect is achieved. The ultrasonic therapeutic transducer provided on the ultrasonic therapeutic probe outputs focused ultrasonic energy, which is embodied as a thermal effect on the tissue, and the heat is diffused from the focal point to its surroundings to form a hot zone/thermal diffusion zone.
The heat dispersion area formed by the ultrasonic energy output by the treatment handle in a static state is smaller, and the temperature of the central area is higher; the heat dispersion area formed by the ultrasonic energy output in the moving process of the treatment handle is relatively large, the temperature of the central area of the heat dispersion area is lower than that of the heat dispersion area formed in the static state of the handle, pain can be effectively reduced, and therefore the energy distribution uniformity of the heat dispersion area formed in the moving state of the handle is better, and the experience is more comfortable.
In an embodiment of the present invention, the specific range of values of the working parameters of the ultrasonic handle unit are: the output power is 1-30W, the output frequency is 500K-15M, and the depth of acting on subcutaneous tissue is 0.5-25mm.
In one embodiment of the present invention, specific range values of the operating parameters of the treatment handle are: the repetition frequency is 2Hz-50Hz.
In one embodiment, the treatment handle is moved by the operator during treatment by moving the handle in a spiral-type path centered at different positions within the treatment area.
In the embodiment, the treatment handle presses the skin before treatment by the modulation method of ultrasonic output pulse, so that the skin is fully attached to the skin, the treatment handle is controlled to move continuously during treatment, the treatment probe is slid continuously, the force is uniform during sliding, the treatment operation of a small area and a small range is realized by moving the spiral circling track at the same point, and the treatment effect is realized.
During treatment, circles are drawn by taking different positions as centers in a treatment area, the centers of the circles are different, the circles are mutually intersected, and finally, the relatively uniform energy distribution in the whole treatment surface is realized, and the treatment handle is moved to realize the treatment purpose. The energy output by treatment is relatively uniform, the temperature superposition effect is relatively good, and the treatment effect is realized.
The therapeutic handle can be controlled to slide back and forth along the Z-shaped track in the therapeutic area during treatment, the sliding force is uniform, ultrasonic energy is continuously diffused through the back and forth sliding, and finally the therapeutic energy is diffused to all therapeutic areas, so that the therapeutic effect is realized.
The foregoing description is only of the optional embodiments of the present invention, and is not intended to limit the scope of the invention, and all equivalent structural modifications made by the present description and accompanying drawings or direct/indirect application in other related technical fields are included in the scope of the present invention.
Claims (6)
1. An ultrasonic therapeutic apparatus, comprising:
the controller comprises a memory and a processor, wherein a pulse output control program is stored in the memory, and the pulse output control program realizes a pulse output control method when being executed by the processor;
the pulse output control method comprises the following steps:
step S10, outputting ultrasonic detection pulses to target tissues, and outputting a detection pulse to the target tissues before any one treatment pulse and after any one treatment pulse when periodically outputting treatment pulses to the target tissues;
step S20, receiving reflected waves fed back by the target tissue, and detecting the temperature of the target tissue according to the received reflected waves;
step S30, adjusting the energy of the ultrasonic treatment pulse output to the target tissue according to the detected temperature of the target tissue, when the detected temperature is smaller than a second preset temperature, adjusting the energy of the treatment pulse to be larger, when the detected temperature is larger than a third preset temperature, adjusting the energy of the treatment pulse to be smaller, and when the detected temperature is larger than or equal to the second preset temperature and smaller than or equal to the third preset temperature, maintaining the energy of the treatment pulse unchanged;
the ultrasonic generating unit is connected with the controller and is used for outputting therapeutic pulses and/or detection pulses according to the control instruction output by the controller; and
and the energy adjusting unit is connected with the controller and is used for adjusting and outputting the energy of the therapeutic pulse and/or the detection pulse according to the control signal of the controller.
2. The ultrasonic therapeutic apparatus according to claim 1, wherein the control method of the pulse output before any one of the therapeutic pulses specifically comprises the steps of:
the steps S10 to S30 are repeatedly performed, wherein the step S30 specifically includes the following steps:
and stopping the treatment pulse and displaying the prompt information when the detected temperature is greater than or equal to the first preset temperature.
3. The ultrasonic therapeutic apparatus according to claim 1, wherein the control method of the pulse output before any one of the therapeutic pulses specifically comprises the steps of:
the steps S10 to S30 are repeatedly performed, wherein the step S30 specifically includes the following steps:
and outputting a therapeutic pulse with preset power to the target tissue when the detected temperature is less than the first preset temperature.
4. The ultrasonic therapeutic apparatus according to claim 1, wherein said step S20 specifically comprises the steps of:
and receiving the reflected wave output by the target tissue, and calculating the temperature of the target tissue according to the time offset of the reflected wave at the reference temperature and the time offset of the detected reflected wave, wherein the time offset of the reflected wave is specifically the time interval from outputting the detection pulse to receiving the reflected wave.
5. The ultrasonic therapeutic apparatus according to claim 1, wherein said step S20 specifically further comprises the steps of:
the reflected wave output from the target tissue is received, and the temperature of the target tissue is calculated from the frequency of the reflected wave at the reference temperature and the frequency of the detected reflected wave.
6. The ultrasonic therapeutic apparatus according to claim 1, wherein said step S20 specifically further comprises the steps of:
the reflected wave output by the target tissue is received, and the temperature of the target tissue is calculated from the reflected wave energy at the reference temperature and the energy of the detected reflected wave.
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