RU2465860C1 - Method for non-invasive ablation and destruction of dielectric body segments with loss and apparatus for implementation thereof - Google Patents

Abstract

FIELD: medicine.

SUBSTANCE: group of inventions refers to medical equipment and may be used for implementation of non-invasive ablation and thermal and thermomechanical destruction of limited areas inside biological bodies of non-uniform structure and other dielectric bodies with loss exposed to electromagnetic field or ultrasound. An apparatus comprises a generator, emitters on the surface of a reflection shield, an analogue-to-digital converter, a power splitter, a multiplex switch and a control unit for emitters. It is preceded by emitter alignment in a travelling-wave mode followed by alignment of each emitter on the specified focus points according to the special algorithm by varying complex incident wave amplitudes and phases; after the alignment, emission power is increased to a value required to perform ablation and destruction of the preset dielectric body segments.

EFFECT: group of invention provides optimal focusing in the pre-set point, minimal size of a focal spot and maximal concentration and focusing accuracy of the impinging field.

9 cl, 11 dwg

Description

The invention relates to medical equipment and can be used to implement non-invasive ablation and thermal and thermomechanical destruction of limited areas inside biological bodies with an inhomogeneous structure and other dielectric bodies with losses.

In cardiology, a method of radiofrequency ablation is known [1], when using a catheter inserted into the heart chamber, a high-frequency electromagnetic field (f = 1 ... 500 MHz) is applied to effect thermal effects on certain sections of the inner surface of the heart in order to block the electrical impulse through these sites. One of the disadvantages of this method is the complexity and trauma of introducing a catheter into the heart chamber and the need for high-precision positioning of the catheter electrodes in the desired region of the heart. For these purposes, parallel computed tomography is usually used, as a result of which the patient receives significant doses of x-ray radiation. Often, ablation on the external surface of the heart from the epicardium is required, which requires an even more time-consuming and unsafe procedure for the patient.

In medicine, there is also the problem of destruction (thermal burning) of certain tissue sections of various organs without surgical intervention, when there is no possibility of catheter insertion without significant surgical procedures, such as coagulation of a tumor of internal organs, elimination of calciform and other formations in blood vessels, liver, kidneys, bladder, etc.

For technical problems, the need often arises for thermal or thermomechanical destruction of various defective formations within solid-filled volumes. For example, when monitoring the inside of the lens antennas and eliminating defects within them. A similar problem arises when controlling quality and eliminating defects in products made of high-quality concrete, plastic, etc.

The non-destructive testing methods used for these tasks using ultrasonic (ultrasound), electromagnetic (EM) fields and x-ray radiation will initially solve only the first part of the problem, namely, to determine the localization of defects or harmful formations, but they will not allow to eliminate these defects and formations without significant interventions in neighboring areas. Thus, a known method [2, 3] of ultrasonic echoscopy for the detection and visualization of structural changes in the tissues of biological organs and in the dielectric media of various products.

Ultrasound devices have been developed for noninvasive ablation of tumors in urology and gynecology [4, 5], liver, mammary glands, bones and soft tissues, kidneys, etc. [6]. In these devices, in order to concentrate the field, the method of focusing ultrasonic radiation using reflectors, lenses, and controlled phased arrays is used [2, 3]. Similar methods of EM field concentration are used in radio engineering, in particular, in antenna technology [7].

The main disadvantage of the known methods [2, 3] is the insufficient spatial concentration of ultrasound and EM fields in the required body volumes. The lenses or reflectors used for focusing [8] make it possible to obtain a high concentration of EM and ultrasound fields at the focal point of homogeneous media in a plane perpendicular to the focal axis, and much smaller in the direction of the focal axis. In addition, in these methods it is impossible to focus in inhomogeneous (irregular) media with insufficiently known or unknown parameters of heterogeneity, and, as a result of this, it is impossible to control the position of the focus, and therefore it is impossible to focus the field to a given point in the inhomogeneous (irregular) environment.

In [9], a method of non-invasive ablation in cardiology using the application of x-ray radiation was described, which allows one to obtain a high degree of concentration of x-ray radiation at the desired point. However, the disadvantages of this method are also obvious, associated with significant doses of radiation received by the patient during heart ablation.

Due to the presence of irregularities in the irradiated structure by pulsed ultrasound signals, side reflections of probe pulses from these inhomogeneities occur, which together with the main reflected pulses occupy almost the entire range of time delays, significantly worsening focusing accuracy and the degree of field concentration in the focal spot and increasing the level of the irradiated field in the rest area [10].

In addition, the above methods make it possible to obtain only good two-dimensional spatial resolution in three-dimensional image space, and the use of a pulsed irradiation mode for spatial resolution leads to additional distortion of the two-dimensional image due to the frequency dependence of the shape of the radiation pattern of the AR. In addition, when moving (scanning) the focused beam both along the longitudinal axis and in the plane of the antenna cross section, the dimensions of the focal spot change significantly. In addition, since the irradiated structure in the general case is inhomogeneous and the parameters of its inhomogeneity are unknown, this leads to additional errors in focusing, a decrease in the field power flux density at the focus, and blurring of the focal region. Additional “blurring” of the focused region also occurs when the structure can move in space. In addition, due to the presence of irregularities in the irradiated structure by pulsed ultrasound signals, side reflections of probe pulses from these inhomogeneities arise, which together with the main reflected pulses occupy almost the entire range of time delays, which significantly impair the focusing accuracy and the degree of field concentration in the focal spot and increase the level of the irradiated fields in the rest of the region [10].

The method of multimode focusing of longitudinal and transverse ultrasound waves, proposed in [11], using controlled amplitude and phase radiation of individual HEADLIGHTS to mutually compensate the phases of longitudinal and transverse waves, is unsuitable for non-invasive ultrasound ablation in cardiology, because, firstly, it has the frequency limit of the ultrasound field is 100 ... 400 kHz, at which the size of the focal spot exceeds the minimum size required for ablation of 3 mm. Secondly, during ablation in cardiology, transverse ultrasound waves are practically absent. In addition, in ultrasound ablation in cardiology, the amplitude-phase distributions required for focusing in this method are proposed to be determined on the basis of computer simulation of the process of propagation of ultrasound waves in a substantially heterogeneous and irregular environment of biological tissue, while the tissue parameters necessary for modeling should be obtained from analysis of ultrasound tissue research with an already focused beam. Such a problem is incorrect in its formulation, its solution is unstable and poorly converging even for a biological volume that does not change in time and can hardly be obtained in a time interval that is reasonable for medical research. In addition, not all tissue parameters necessary for modeling can be determined by ultrasound and even other additional (magnetic-nuclear or X-ray) tomographic studies, the methods and hardware of which are described in [12, 13, 14, 15] when using the latter as additional funds for ablation. In addition, a temporary change in the positions of biological tissue (in cardiology, this is a heartbeat) does not allow the focusing method proposed in [11] to be used for non-invasive ablation in cardiology.

In addition, recommendations for the implementation of non-invasive ablation and destruction using EM or ultrasound fields exist independently for both the EM and ultrasound fields. At the same time, there are no clear recommendations on the choice of PAR sizes used for ablation and destruction. At the same time, there are general (fundamental) regularities in the selection of the field type for non-invasive ablation and destruction, as well as in the selection of the appropriate field frequency and minimum PAR sizes, at which the technology of non-invasive ablation and destruction is strictly limited.

Closest to the claimed invention is a method and device [16], in which for selective destruction of tumor cells, the focusing of the ultrasound field is carried out using phased antenna arrays (AR). The specified method includes the selection and location of ultrasonic field emitters on a limited open surface, the formation of temporary signal pulses, phasing, focusing, radiation and control of the focused field within a biological or other dielectric object, reception of a reflected field by each of the AR emitters, and subsequent signal processing. However, the described method allows to obtain only a good two-dimensional spatial resolution in three-dimensional image space, and the use of a pulsed irradiation mode for spatial resolution leads to additional distortion of the two-dimensional image due to the frequency dependence of the shape of the radiation pattern of the AR. In addition, when moving (scanning) a focused beam both along the longitudinal axis and in the plane of the antenna cross section, the dimensions of the focal spot change significantly. Since the irradiated structure is generally inhomogeneous and the parameters of its heterogeneity are unknown, this leads to additional errors in focusing, a decrease in the field power flux density at the focus, and blurring of the focal region. Additional “blurring” of the focused region also occurs when the structure can move in space.

The technical task of this invention is to provide a method and device that provides optimal focusing at a given point, the minimum size of the focal spot and the maximum concentration and focusing accuracy of the ultrasound or EM field in a given area of a biological or other dielectric object with an unknown or not well-known inhomogeneous structure while ensuring the minimum acceptable field concentration outside a given area of the focal spot, maintaining a high concentration and focusing accuracy at time m moving object area considered, selection of an optimum frequency range and type fields, electromagnetic or ultrasonic, size and geometry PAR supplied power. The type of radiated field is carried out according to the minimum value of the loss coefficient inside the irradiated object.

и фазой

где

- радиус-вектор первой точки фокусировки относительно начала выбранной системы координат, запоминаем амплитуды

и фазы

соответственно падающего излучения и излучения, отраженного от участка воздействия на диэлектрическом теле, затем при возбужденном первом излучателе возбуждают второй излучатель сигналом с произвольной комплексной амплитудой

измеряют амплитуду

и фазу

излучения, отраженного от участка воздействия на диэлектрическом теле, при этом изменяют значение амплитуды падающей волны

до выполнения соотношений:

где ^∗ - знак комплексного сопряжения, А₂ - постоянный коэффициент, определяемый в процессе настройки, запоминают амплитуду

и фазу

падающей волны, после этого при возбужденных первом и втором излучателях возбуждают третий излучатель сигналом с произвольной амплитудой

и фазой

измеряют амплитуду

и фазу

излучения, отраженного от участка воздействия на диэлектрическом теле, при этом изменяют значение амплитуды падающей волны

до выполнения соотношений:

где A₃ - постоянный коэффициент, определяемый в процессе настройки, запоминают амплитуду

и фазу

падающей волны, далее последовательно возбуждают аналогичным образом остальные излучатели, подстраивая амплитуды и фазы падающей волны до выполнения соответственно соотношений:

j=4…n, где n - общее количество излучателей, A_j - постоянный коэффициент, определяемый в процессе настройки, запоминают амплитуду

и фазу

падающей волны, проверяют местонахождение заданной точки фокусировки относительно выбранного участка диэлектрического тела и при отрицательном результате процедуры фокусировки излучателей повторяют заново, при положительном результате производят запись параметров фокусировки - амплитуду и фазу каждого из излучателей, далее осуществляют процедуры фокусировки всех излучателей для заданного количества М точек фокусировки на участке воздействия на диэлектрическом теле и запоминание параметров фокусировки, при расположении точки М' абляции и деструкции вне М точек фокусировки и находящихся в области тетраэдра, вершины которого совпадают с координатами

ближайших к точке М', причем расстояние от точки М' до точек с координатами

является наименьшим среди всех возможных точек m=1…М, определяют и записывают их комплексные амплитуды

путем интерполяции:The problem is achieved in that in the method of non-invasive ablation and destruction of parts of the dielectric body with losses, namely, that the dielectric body is placed inside the reflective screen, the selected area of the dielectric body is exposed to radiation of the corresponding intensity and frequency using emitters placed on the reflective screen so so that the maxima of their radiation diagrams are directed inside the volume bounded by the specified reflective screen, focus radiation from the emitters after Accordingly, prior to placing the dielectric body inside the reflective screen, a volume absorber is placed inside the volume bounded by the reflective screen, and each of the emitters is excited with low-power radiation with a wavelength _With λ = 2r _F where r _F - focal spot of a predetermined radius, λ _C - the length of the wave in the dielectric lossless, and is adapted to each radiator Regis traveling wave absorber volumetric removed, then produce emitters for the chosen setting point of focus, which excites the first transducer signal with arbitrary amplitude

and phase

Where

- the radius vector of the first focus point relative to the beginning of the selected coordinate system, remember the amplitude

and phases

respectively, the incident radiation and radiation reflected from the site of exposure on the dielectric body, then when the first emitter is excited, the second emitter is excited by a signal with an arbitrary complex amplitude

measure the amplitude

and phase

radiation reflected from the site of exposure on the dielectric body, while changing the value of the amplitude of the incident wave

until the ratios are satisfied:

where ^∗ is the sign of complex conjugation, And ₂ is a constant coefficient determined during the setup process, remember the amplitude

and phase

incident wave, after that, when the first and second emitters are excited, the third emitter is excited by a signal with an arbitrary amplitude

and phase

measure the amplitude

and phase

radiation reflected from the site of exposure on the dielectric body, while changing the value of the amplitude of the incident wave

until the ratios are satisfied:

where A ₃ is a constant coefficient determined during the setup, remember the amplitude

and phase

incident wave, then sequentially excite the rest of the emitters in a similar manner, adjusting the amplitudes and phases of the incident wave until the following ratios are satisfied:

j = 4 ... n, where n is the total number of emitters, A _j is a constant coefficient determined during the tuning process, the amplitude is stored

and phase

incident wave, check the location of the given focus point relative to the selected area of the dielectric body and, if the emitter focusing procedure is negative, repeat the procedure, focus parameters are recorded, the amplitude and phase of each emitter are recorded, then the focusing procedures of all emitters are carried out for a given number of M focus points in the area of influence on the dielectric body and storing the focus parameters, with the location of the point M ' blyatsii degradation and M is located and the focus points in the tetrahedron, whose vertices coincide with the coordinates

closest to the point M ', and the distance from the point M' to points with coordinates

is the smallest among all possible points m = 1 ... M, their complex amplitudes are determined and recorded

by interpolation:

,

,

- радиус-векторы соответствующих точек;

- расстояние между точками m₃ и m₂;

- расстояние между точками m₃ и М''';

- расстояние между точками m₁ и М''';

- расстояние между точками m₁ и М'';

- расстояние между точками m₄ и М'',

- расстояние между точками m₄ и М'; после чего увеличивают мощность излучения до величины, необходимой для осуществления абляции и деструкции в указанной области и безвредной вне указанной области, и осуществляют абляцию и деструкцию в указанных точках, при этом радиус кривизны а отражающего экрана выбирают из условии

, где a _диэл - радиус диэлектрического тела;

- оптимальный радиус, при котором при заданной мощности поля излучателей, расположенных на отражающем экране в точке фокусировки диэлектрического тела, достигается максимальное значение плотности потока мощности поля; радиус a ₁ совместно с величиной а _opt определяют возможный интервал выбора радиуса а отражающего экрана; величина а ₁ зависит от допустимого уровня p_{ДОП Н} плотности потока мощности

на периферии диэлектрического тела, нормированной к аналогичному параметру

в точке фокусировки, и определяется из условийWhere

,

,

- radius vectors of the corresponding points;

- the distance between the points m ₃ and m ₂ ;

- the distance between points m ₃ and M ''';

- the distance between the points m ₁ and M ''';

- the distance between the points m ₁ and M '';

- the distance between points m ₄ and M '',

- the distance between points m ₄ and M '; then increase the radiation power to the value necessary for the implementation of ablation and destruction in the specified area and harmless outside the specified area, and carry out ablation and destruction at these points, while the radius of curvature a of the reflecting screen is selected from the condition

where a _diel is the radius of the dielectric body;

- the optimal radius at which at a given field power of the emitters located on the reflective screen at the focus point of the dielectric body, the maximum value of the field power flux density is achieved; the radius a ₁ together with the value a _opt determine the possible interval for choosing the radius a of the reflecting screen; the value of a ₁ depends on the permissible level p _{ADD N} power flux density

on the periphery of the dielectric body normalized to a similar parameter

at the focal point, and is determined from the conditions

tgΔ(λ_С) - угол диэлектрических потерь в среде для используемого типа поля.

tgΔ (λ _C ) is the dielectric loss angle in the medium for the type of field used.

In this case, an ultrasonic or electromagnetic field selected on the basis of the minimum value of the loss coefficient inside the irradiated object can be used as the acting radiation.

The surface of the reflective screen may have a cylindrical or spherical shape or a shape that matches the surface of the dielectric body.

The emitters can be excited by a harmonic or pulsed signal.

учитывают зависимость координат

от времени t в случае, если координаты точек фокусировки диэлектрического тела смещаются во времени, например, для различных органов биологических объектов, таких как сердце.In addition, when determining the coordinates of the focusing points m = 1 ... M and the necessary complex amplitudes of excitation

take into account the dependence of coordinates

from time t in case the coordinates of the focus points of the dielectric body are shifted in time, for example, for various organs of biological objects, such as the heart.

The task is also achieved by the fact that in a device for non-invasive ablation and destruction of parts of a dielectric body with losses, containing a generator, a control input of which is connected to a control and calculation unit connected to a visualization unit, ADCs and emitters placed on the surface of a reflective screen, according to the invention n-channel power divider, n-channel channel switch and n-channel emitter excitation control unit, the outputs of which are connected to correspondingly to n-emitters, while the output of the generator through the ADC is connected to the input of the n-channel power divider, the control inputs of the n-channel power divider, n-channel switch of channels and the n-channel excitation control unit of the emitters are connected respectively to the control outputs of the control unit and calculation, the first and second information inputs of which are connected respectively to the information outputs of the n-channel control unit for emitters excitation, each of the channels of the n-channel control unit excitation of emitters consists of a signal amplitude control unit connected in series, the input of which is the input of the corresponding channel of the n-channel emitter excitation control unit, a signal phase control unit, an isolation and a switch unit, an incident and reflected wave comparison unit and a series-wise KBV meter and a controlled matching unit , the output of which is the output of the corresponding channel of the n-channel block for controlling the excitation of emitters, the first input of the block is compared I of the incident and reflected waves is connected to the output of the signal phase control unit, and its second input is connected to the second output of the isolation unit, the output of the switch through a normally closed contact is connected to the output of the corresponding channel of the n-channel emitter excitation control unit, and through the normally open contact with the input of the KBV meter, while the control inputs of the signal amplitude control unit, the signal phase control unit and the controlled matching unit are the control inputs of the corresponding channel n-channel unit drive control emitters, and outputs the comparison block the incident and reflected waves and IPM meter data outputs are n-channel drive control unit emitters.

Moreover, the generator can be made in the form of a source of electromagnetic radiation or in the form of a source of ultrasonic radiation.

The surface of the reflective screen may have a cylindrical or spherical shape.

The proposed method for non-invasive ablation and destruction of parts of a dielectric body with losses and a device that implements it provide optimal focusing at a given point and its minimum size, maximum concentration and focusing accuracy of an ultrasound or EM field in a given region of a dielectric object with an unknown or insufficiently known inhomogeneous structure due to the preliminary adjustment and subsequent focusing of the emitters using the developed special control algorithm, est filtering the signal from the radiation source, ensuring the minimum permissible field concentration outside the focus point, maintaining a high power concentration and focusing accuracy when temporarily moving a given ablation and destruction region, choosing the optimal frequency range and supplied power.

The invention is illustrated by drawings.

.Figure 1 shows the structural electrical diagram of a device for non-invasive ablation and destruction of parts of the dielectric body with losses; figure 2 is a structural electrical diagram of one channel of the n-channel block control the excitation of emitters; figure 3 shows the layout of m = 1 ... M focus points in the required volume of the plot of the dielectric body - the heart muscle, determined in the process of presetting; Fig. 4 is a diagram explaining the process of determining the parameters of the field focusing at an arbitrary point M ', Fig. 5 shows the calculated dependence of the electric radius k _C a ₁ at p _{DOP N} = 0.01 for cases in the dielectric (three values tgΔ = 0.1; 0.05 and 0.01). Setting values of k _With , it is easy to determine the values of the radius a ₁ . The calculated dependences of k _С a ₁ on tgΔ for p _{DOP N} = 0.01 and p _{DOP N} = 0.05 are shown in the table. The optimal electric and radius k _С a _{opt of the} spherical surface on which the emitters are placed is determined from the expression

.

p _{ADP N} tgΔ k _C a ₁ 0.01 970 0.01 0.05 105 0.1 24 0.01 1170 0.05 0.05 153 0.1 57

в фокусе по отношению к средней плотности потока мощности источников

от электрического радиуса сферы k_С a, на поверхности которой располагаются излучатели, при различных значениях потерь tgΔ в диэлектрике. По графику на фиг.6 для выбранного размера k_С a=k_Сa_opt определяется необходимая мощность генератора

.Figure 6 presents the calculated dependence of the concentration coefficient K power flux density

in focus with respect to the average power flux density of the sources

from the electric radius of the sphere k _С a , on the surface of which emitters are located, at different values of losses tgΔ in the dielectric. According to the graph in FIG. 6, for the selected size k _С a = k _С a _opt , the required generator power is determined

.

, нормированной к плотности потока мощности в фокусе

, от электрического расстояния k_С a до фокуса диэлектрической сферы для различных tgΔ, в качестве примера показаны границы a ₁ при р_{ДОП Н}=10^-2, которые показывают, что величина Р_{ДОП Н} не может быть меньше некоторой минимальной для данного tgΔ величины Р_{ДОП Н min}.Figure 7 presents the calculated dependence of the power flux density

normalized to power flux density in focus

, from the electric distance k _C a to the focus of the dielectric sphere for different tgΔ, as an example, the boundaries a ₁ are shown for p _{DOP N} = 10 ^-2 , which show that the value P of _{DOP N} cannot be less than a certain minimum value for a given tgΔ of P _{ADD N min} .

The schedule in Fig.7 determines the permissible values of a ₁ from the condition

,

,

, плотность потока мощности источников на расстояниях a ₁ от фокальной точки. Радиус а сферической поверхности выбирается из условийwhere p _{DOP N} - permissible, normalized to

, the power flux density of sources at distances a ₁ from the focal point. The radius a of the spherical surface is selected from the conditions

.

.

On Fig shows the calculated dependence P _{DOP N min} (tgΔ) for a spherical dielectric volume with losses; figure 9, 10, 11 shows the algorithm that implements the proposed method for focusing emitters and subsequent thermal destruction.

The implementation of the above method of ablation and destruction, presented in the form of an algorithm (Fig.9, 10, 11), is as follows.

At the first stage, the optimal ablation irradiation frequency is selected from the condition:

λ _C = 2r _F ,

tgΔ(λ_С) - угол диэлектрических потерь в среде для обоих полей, и выбором того поля, потери в котором минимальны.where r _Ф is the radius of the focal spot, λ _С is the wavelength of the incident field in the dielectric without loss, and the appropriate type of field (ultrasound or EM) depends on the level of losses at this frequency and is determined from a comparison for both fields of ultrasound or EM values

tgΔ (λ _С ) is the dielectric loss angle in the medium for both fields, and by choosing the field in which the losses are minimal.

Calculations show that, in particular, the appropriate frequency range for ultrasound ablation in cardiology lies in the range 0.5 ... 2 MHz.

The radius a of the spherical (cylindrical) surface, on which the emitters are located, is selected from the conditions

,

,

- оптимальный радиус сферической (цилиндрической) поверхности, при котором при заданной полной мощности поля излучателей, расположенных на сферической (цилиндрической) поверхности в точке фокусировки диэлектрического тела, достигается максимальное значение плотности потока мощности поля; радиус а ₁ совместно с величиной а _opt определяют возможный интервал выбора радиуса а сферической или цилиндрической поверхности, на которой располагаются излучатели; величина а ₁ зависит от допустимого уровня р_{ДОП Н} плотности потока мощности

на периферии диэлектрического тела, нормированной к аналогичному параметру

в фокусе, и определяется из условийwhere a _diel is the radius of the dielectric body;

- the optimal radius of the spherical (cylindrical) surface, at which, for a given total field power of the emitters located on the spherical (cylindrical) surface at the focal point of the dielectric body, the maximum value of the field power flux density is achieved; the radius a ₁ together with the value a _opt determine the possible interval for choosing the radius a of the spherical or cylindrical surface on which the emitters are located; the value of a ₁ depends on the permissible level p _{ADP N} power flux density

on the periphery of the dielectric body normalized to a similar parameter

in focus, and is determined from the conditions

.

.

The radius of an arbitrary closed surface coinciding with the surface of the dielectric body in which ablation or destruction is carried out is half the maximum length between the points of a given dielectric body.

Then, each of the emitters is tuned to the traveling wave mode by matching each of the n-emitters in the presence of a volume absorber inside the reflecting screen, which can be used graphite for the electromagnetic field or rubber for the ultrasound field, by changing the parameters of the matching unit in each of emitters.

To improve the contact of emitters with a dielectric (biological) object, water or liquid with low dielectric losses can be used.

At the second stage, instead of the volume absorber, a dielectric body is placed inside the volume bounded by the reflective screen and the emitters are tuned to points located in the selected area. The tuning mode is performed in static mode on a fixed dielectric object at low generator power. In particular, for a biological object, for example, the heart, this action can be performed when it is stopped for a short time at a power of up to 1 W, which is harmless to the body.

и фазы

и запись амплитуды

и фазы

первого излучателя. Далее получают отраженную от диэлектрического тела волну в первом излучателе и записывают ее амплитуду

и фазу

Оставляя условия возбуждения первого излучателя неизменными, включают следующий, второй излучатель, выбирают произвольную амплитуду

и фазу

проверяют условие фокусировки

. Если оно не выполняется, происходит подстройка амплитуды падающего сигнала во втором излучателе и условие фокусировки проверяется снова. При выполнении указанного выше условия фокусировки - значения амплитуды

и фазы

второго излучателя записываются.The emitter system is tuned to the first focus point. For this purpose, the first emitter is turned on, while all other emitters are in the off state, an arbitrary amplitude is selected

and phases

and amplitude recording

and phases

first emitter. Next, a wave reflected from the dielectric body is received in the first radiator and its amplitude is recorded.

and phase

Leaving the conditions for the excitation of the first emitter unchanged, include the next, second emitter, choose an arbitrary amplitude

and phase

check the focus condition

. If it is not satisfied, the amplitude of the incident signal in the second radiator is adjusted and the focusing condition is checked again. When the above focusing conditions are fulfilled, the amplitude values

and phases

the second emitter are recorded.

и фазу

проверяют условие фокусировки

Если оно не выполняется, происходит подстройка амплитуды падающего сигнала в третьем излучателе и условие фокусировки проверяется снова. При выполнения указанного выше условия фокусировки значения амплитуды

и

третьего излучателя записываются.Leaving the conditions for the excitation of the first and second emitters unchanged, include the next, third emitter, choose an arbitrary amplitude

and phase

check the focus condition

If it is not satisfied, the amplitude of the incident signal in the third radiator is adjusted and the focusing condition is checked again. When the above conditions for focusing the amplitude value

and

The third emitter is recorded.

и фазу

и проверяют условие фокусировки

. Если оно не выполняется, происходит подстройка амплитуды и фазы падающего сигнала в j-м излучателе и условие фокусировки проверяется снова. При выполнении указанного выше условия фокусировки значения амплитуды

и фазы

j-го излучателя записываются.Leaving the conditions for the excitation of the first, second and third emitters unchanged, include the next, j-th (j = 1 ... n) emitter, choose an arbitrary amplitude

and phase

and check the focus condition

. If it is not satisfied, the amplitude and phase of the incident signal are adjusted in the jth emitter and the focusing condition is checked again. When the above conditions for focusing the amplitude value

and phases

jth emitter are recorded.

After enumerating all the emitters or in case of early termination of the setup procedure, there is all the data for tuning all emitters to the first focus point. The first focusing point is superimposed on the coordinate grid of the dielectric (biological) object (Fig. 3), and a check is made to see if this focusing point is in the desired (given) area. If the result is positive, the procedure of focusing all the emitters to the second focusing point is repeated; otherwise, the first point is focused again.

This cycle is repeated until the required number of focus points M specified by the operator is miscalculated or the specified area of the dielectric (biological) object is scanned with the required step. Moreover, for an arbitrary point M 'outside the found M focus points, but located in the region of the tetrahedron (Fig. 4), one can find the excitation parameters, i.e. complex amplitudes of the emitters, by interpolation according to the following algorithm (figure 4):

,

,

,

,

.

.

задают в виде дискретного набора Q_a уровней

и Q_φ уровней

, q_a=1…Q_a, q_φ=1…Q_φ. При этом перебор уровней амплитуд и фаз j-го излучателя проводится до выполнения условий минимизации разностиTo speed up the preset procedure, the incident field in each jth emitter

set in the form of a discrete set of Q _a levels

and Q _φ levels

, q _a = 1 ... Q _a , q _φ = 1 ... Q _φ . In this case, the amplitude levels and phases of the jth emitter are enumerated until the conditions for minimizing the difference

.

.

равно

Так уже при Q_φ=2 М_max=8, при Q_φ=4 М_max=64, при Q_φ=8 М_max=512. Максимальное количество различных дискретных значений амплитуды Q_a, фазы Q_φ и коэффициентов

в каждом j-ом излучателе зависит от требуемой точности фокусировки. Для ускорения процесса предварительной настройки в качестве начального приближения для

можно выбрать величину, комплексно сопряженную коэффициенту передачи

от j-го излучателя до m-го фокуса. Коэффициент передачи

может быть рассчитан приближенно в предположении приблизительно известных параметров среды (в частности, для биологической ткани - скорости УЗ волны). Коэффициенты A₁, А₂, А₃, A_j определяются в процессе настройки излучателей и определяют, соответственно, величины изменения амплитуд падающего излучения до выполнения условий фокусировки.The maximum number of focused points M _max when choosing a discrete set

equally

So already at Q _φ = 2 M _max = 8, at Q _φ = 4 M _max = 64, at Q _φ = 8 M _max = 512. The maximum number of different discrete values of the amplitude Q _a , phase Q _φ and coefficients

in each j-th emitter depends on the required focusing accuracy. To speed up the preset process as an initial approximation for

you can choose a value that is complex conjugate to the gear ratio

from the j-th emitter to the m-th focus. Gear ratio

can be calculated approximately on the assumption of approximately known parameters of the medium (in particular, for biological tissue - ultrasonic wave velocity). The coefficients A ₁ , A ₂ , A ₃ , A _{j are} determined in the process of tuning the emitters and determine, respectively, the magnitude of the change in the amplitudes of the incident radiation until the focusing conditions are met.

Thus, data is obtained on all focus points on a dielectric (biological) object, where it is necessary to carry out the ablation and destruction procedure. Then, the kinematics of the motion of these points on the dielectric (biological) body is determined depending on the time and their synchronization with the coordinates of the moving dielectric (biological) object, for example, with a heartbeat.

The first focusing point on the dielectric body, which is necessary for destruction, is selected, the power required for destruction and harmless to the dielectric body outside the focus zone is established, and the destruction process itself is started, controlling it visually. The destruction time depends on the parameters of the dielectric body and can be monitored, for example, using a temperature sensor.

If necessary, select the second focusing point and continue destruction, for example, until the desired (specified) area of the biological object is cleared of all harmful ectopic centers and additional pathways that cause the re-entry effect.

If it is necessary to increase the radius of destruction, additional phase errors are introduced into the excitation of the emitters.

To enhance the field concentration at the ablation or destruction point, a pre-focused system of emitters with a controlled focus position can be used as a separate emitter.

The device for non-invasive ablation and destruction of sections of a dielectric body with losses, shown in Fig. 1, contains a generator 1, the control input of which is connected to a control and calculation unit 2, connected to a visualization unit 3, an analog-to-digital converter (ADC) 4 and emitters 5 located on the surface of the reflective screen 6, a n-channel divider 7, an n-channel channel switch 8 and an n-channel excitation control unit for emitters 9, the outputs of which are connected respectively to n-emit, are connected in series lam 5, while the output of the generator 1 through the ADC 4 is connected to the input of the n-channel power divider 7, the control inputs of the n-channel power divider 7, the n-channel switch channel 8 and the n-channel excitation control unit of the emitters 9 are connected respectively to the control outputs control and computing unit 2, the information inputs of which are connected to the information outputs of the n-channel excitation control unit of the emitters 9.

Each of the channels of the n-channel block for controlling the excitation of the emitters 9 (Fig. 2) consists of series-connected blocks for controlling the amplitude of the signal 10, the input of which is the input of the corresponding j-th channel of the n-channel block for controlling the excitation of emitters 9, the phase control block of the signal 11, decoupling unit 12 and switch 13, a unit for comparing incident and reflected waves 14 and series-connected traveling wave coefficient meter (CBM) 15 and a controlled matching unit 16, the output of which is the output corresponding of the j-channel of the n-channel excitation control unit for emitters 9, the first input of the incident and reflected wave comparison unit 14 is connected to the output of the phase control unit of signal 11, and its second input is connected to the second output of isolation unit 12, the output of switch 13 is through a normally closed the contact is connected to the output of the corresponding j-th channel of the n-channel excitation control unit of the emitters 9, and through the normally open contact of the switch 13 - with the input of the KBV meter 15, while the control inputs of the amplitude control unit of the 10th signal, the phase control block of the signal 11 and the controlled matching block 16 are the control inputs of the corresponding jth channel of the n-channel excitation control unit of the emitters 9, and the outputs of the incident and reflected wave comparison unit 14 and the CBM 15 are information outputs of the n-channel emitter excitation control unit 9.

Moreover, the generator 1 can be made in the form of a source of electromagnetic radiation or in the form of a source of ultrasonic radiation.

The surface of the reflective screen 6 may have a cylindrical or spherical shape and completely cover the dielectric (biological) body 17.

A device that implements the method of destruction according to the above algorithm (Fig.9, 10, 11), works as follows. The signals from the generator 1 through the ADC 4 are fed to the n-channel power divider 7 with their subsequent switching through the n-channel switch 8. Switch 8 operates in two modes. In matching mode, it alternately turns on only each j-th channel (j = 1 ... n). In configuration mode, switch 8 simultaneously includes all channels with numbers from one to j (j = 1 ... n). The power divider 7 has n output channels, which are connected via n-channel switch 8 to n emitters 5 through block 9. In block 9, the amplitude and phase of the incident wave are controlled by applying an error signal from block 14 until the pairing conditions between the reflected and incident waves in each of the channels. The control procedure for the emitters 5 and the switches of block 8 is performed using the appropriate programs embedded in block 2, which can be implemented on a computer basis. To visualize the settings of the system and ablation procedure, a visualization unit 3 is used, for example, an echo-ultrasound or an MRI device (magneto-resistive therapy). As a decoupling unit 12 in the range of electromagnetic waves, a circulator can be used, for an ultrasonic field - a directional coupler with matching load.

(фиг.4) при произвольной, в т.ч. и неоднородной, структуре биологической ткани или иной диэлектрической структуры. При этом местоположение этой точки определяется в результате цифровой или аналоговой обработки отраженного поля в блоке визуализации 3. Блок визуализации 3 выводит изображение облучаемого объекта, на которое яркой точкой накладывается m-я точка фокусировки поля в этом органе.The authors found that the fulfillment of the complex conjugation conditions in the reflected field provides the best focusing of the field at the mth point, the position of which is determined by the radius vector

(Fig. 4) for arbitrary, incl. and heterogeneous, biological tissue structure or other dielectric structure. Moreover, the location of this point is determined as a result of digital or analog processing of the reflected field in the visualization unit 3. The visualization unit 3 displays an image of the irradiated object, on which the m-th focus point of the field in this organ is superimposed.

In the mode of matching emitters 5, the signal from the jth output of the switch 8, controlled by block 2, is fed to the control units of amplitude 10 and phase 11 of the signal, also controlled by block 2. Next, the signal is fed to isolation block 12, the output of which is connected to switch 13. For In this mode, the signal from the switch 13 is fed to the KBV measuring unit 15 and then to the matching block 16 controlled from block 2, from the output of which the signal is fed to the input of the jth emitter. The parameters of the matching unit 16, for example, the length of the matching loop, are selected from the conditions for providing the KBM, close to one. This operation is carried out for each of j (j = 1 ... n) emitters.

. Полученные в результате выполнения данного условия параметры фокусировки записываются в блок 2, и устройство переходит к настройке следующего излучателя, при этом параметры возбуждения предыдущего излучателя остаются неизменными. После настройки всех n-излучателей или в случае досрочного окончания процедуры настройки имеются все данные для настройки всех n-излучателей 1 на первую точку фокусировки. Проводится наложение первой точки фокусировки на координатную сетку диэлектрического (биологического) тела 17 (фиг.3), отображаемое на блоке визуализации 3, и проводится проверка, находится ли данная точка фокусировки в требуемой (заданной) области. В случае положительного результата повторяют процедуру фокусировки всех излучателей на вторую точку фокусировки, в противном случае - фокусировка первой точки повторяется заново. Данный цикл повторяется до тех пор, пока не произойдет фокусировка М точек, заданных оператором, или не просканируется заданная область диэлектрического (биологического) объекта с требуемым шагом. В итоге точки фокусировки отображаются на блоке визуализации 3.In the focus mode, the signal from the first output of the switch 8 is fed to the amplitude control unit 10 and the signal phase control unit 11, and then transmitted to the comparison unit 14. At the same time, the signal is fed through the isolation unit 12 and the switch 13 directly to the input of the first emitter. From the output of the first emitter, the reflected signal through the switch 13 and the isolation unit 12 is supplied to the comparison unit 14. In the future, the amplitude and phase of the signal are controlled from the unit 2 (blocks 10, 11) until the condition

. The focusing parameters obtained as a result of the fulfillment of this condition are recorded in block 2, and the device proceeds to adjust the next radiator, while the excitation parameters of the previous radiator remain unchanged. After tuning all the n-emitters or in case of early termination of the setup procedure, there is all the data for tuning all n-emitters 1 to the first focus point. The first focusing point is superimposed on the coordinate grid of the dielectric (biological) body 17 (Fig. 3) displayed on the imaging unit 3, and a check is made to see if this focus point is in the desired (given) area. If the result is positive, the procedure of focusing all the emitters to the second focusing point is repeated, otherwise, the focusing of the first point is repeated again. This cycle is repeated until the M points specified by the operator are focused or the specified area of the dielectric (biological) object is scanned with the required step. As a result, focus points are displayed on imaging unit 3.

образуют своеобразный базис, позволяющий при необходимости с помощью интерполяции по соседним точкам, ближайшим четырем точкам с номерами m₁, m₂, m₃, m₄, определить параметры возбуждения излучателей для произвольной точки фокусировки М' (фиг.3, 4) по следующему алгоритму:Defined in this way in a given area of biological tissue or another dielectric medium m = 1 ... M focus points and the vector of complex amplitudes of the incident wave stresses required for focusing

form a kind of basis that allows, if necessary, using interpolation at neighboring points, the nearest four points with numbers m ₁ , m ₂ , m ₃ , m ₄ , to determine the parameters of the emitters of the emitters for an arbitrary focus point M '(Figs. 3, 4) as follows algorithm:

,

,

,

,

.

.

задают в виде дискретного набора Q_a уровней

и Q_φ уровней

q_a=1…Q_a, q_φ=1…Q_φ. При этом перебор уровней амплитуд и фаз j-го излучателя проводится до выполнения условий минимизации разностиTo speed up the preset procedure, the incident field in each jth emitter

set in the form of a discrete set of Q _a levels

and Q _φ levels

q _a = 1 ... Q _a , q _φ = 1 ... Q _φ . In this case, the amplitude levels and phases of the jth emitter are enumerated until the conditions for minimizing the difference

.

.

равно

Так уже при Q_φ=2 М_max=8, при Q_φ=4 M_max=64, при Q_φ=8 М_max=512. Максимальное количество различных дискретных значений амплитуды Q_a, фазы Q_φ и коэффициентов

в каждом j-м излучателе зависит от требуемой точности фокусировки. Для ускорения процесса предварительной настройки в качестве начального приближения для

можно выбрать величину, комплексно сопряженную коэффициенту передачи

от j-го излучателя до m-го фокуса. Коэффициент передачи

может быть рассчитан приближенно в предположении приблизительно известных параметров среды, в частности, для биологической ткани - скорости УЗ волны.The maximum number of focused points M _max when choosing a discrete set

equally

So already at Q _φ = 2 M _max = 8, at Q _φ = 4 M _max = 64, at Q _φ = 8 M _max = 512. The maximum number of different discrete values of the amplitude Q _a , phase Q _φ and coefficients

in each j-th emitter depends on the required focusing accuracy. To speed up the preset process as an initial approximation for

you can choose a value that is complex conjugate to the gear ratio

from the j-th emitter to the m-th focus. Gear ratio

can be calculated approximately on the assumption of approximately known parameters of the medium, in particular, for biological tissue - ultrasonic wave velocity.

зависят от времени t по известному закону.In the above relations take into account that the coordinates of the focal point

depend on time t according to a well-known law.

One of the options for determining the coordinates of the focal point during a heartbeat is the procedure for finding these coordinates at the same position of the heart, for example, during short-term cardiac arrest, and the subsequent determination of the dynamics of changes in these coordinates during heartbeat using a special device, for example, an echo Ultrasound diagnostics.

The stage of preliminary adjustment of the system, including the sequence of tasks, is carried out using the control algorithm embedded in block 2, which can be implemented as a high-speed computer, and the signal of the generator 1 is digitized using the ADC 4 installed at the output of the generator. To simplify the tuning procedure, the complex amplitude of the incident field in each radiator is presented in digital form and varies in a discrete manner both in amplitude and phase. The signal from the generator 1 can be either harmonic or pulsed.

All calculated dependences were obtained as a result of modeling ultrasonic and electromagnetic fields with lossy dielectric (biological tissue) in the form of a spherical volume, on the surface of which there are sources of ultrasonic or electromagnetic fields. For a dielectric volume in the form of a finite cylinder and a volume bounded by an arbitrary closed surface, the main simulation results remain qualitatively the same.

Thus, there is data on all focus points on the biological object under study, where it is necessary to carry out the ablation procedure. We determine the kinematics of the movement of these points of the biological body depending on time and synchronize them with the coordinates of a moving biological object, for example, a heartbeat.

After preliminary adjustment of the system, when all the emitters are tuned to all the points necessary for the destruction of the dielectric object, block 2 turns on the high power mode necessary for the destruction and is harmless to the dielectric object outside the destruction zone. The first point for destruction is selected and the destruction procedure itself is started, controlling it visually using the visualization unit 3. The destruction time depends on the parameters of the dielectric object determined in advance and can be monitored, for example, using a temperature sensor. After the destruction at the first point, if necessary, select the second focusing point and continue the destruction process.

If it is necessary to increase the radius of destruction, additional phase errors are introduced into the excitation of the emitters 5.

The described method of ablation and destruction and the operation of the device are presented in the form of an algorithm (Figs. 9, 10, 11) implemented in the form of a program recorded in block 2.

Information sources

1. Arazanov V.N., Ardanov A.V., Steklov V.I. Treatment of heart rhythm disturbances. - M.: Moscow, 2005 .-- 228 p.

2. Domarkas V.Y., Pileckaya E.L. Ultrasound echoscopy - L .: Engineering, Leningrad. Dep., 1988, p. 139.

3. Patent US 4696299, Non-invasive destruction of kidney stones, William R. Shene, Christopher Nowacki, Alfred G. Brisson, priority September 29, 1987.

4. Ablaterm device of EDAP firm for high-intensity focused ultrasound ablation, http://www.medlinks.ru/topics.php?op=cat&category=3 (verified on 04/13/2011).

5. ExAblate system for non-invasive ablation of tumors and specific tissues by focused ultrasound under the control of magnetic resonance imaging, manufacturer Insightec, http://rosslynmedical.ru/ru/manufacturers/insightec/ (verified on 04/13/2011).

6. Focused ultrasound therapeutic “JC” system - a device for the treatment of solid tumors using focused ultrasound, http://hifu.su/en/equipment/jc/ (checked on 04/13/2011).

7. Voskresensky D. I., Gostyukhin V. L., Maksimov V. M., Ponomarev L. I. The textbook "Microwave Devices and Antennas" / ed. D.I. Voskresensky, ed. 3rd, fix and add. - M.: Radio Engineering, 2008, p. 295.

8. Krozdorf A.E. Ultrasound technology. M .: Publishing house "Foreign technology", 1958.

9. Heart Rhythm "Noninvasive stereotactic radiosurgery (CyberHeart) for creation of ablation lesions in the atrium", Arjun Sharma, Douglas Wong, Georg Weidlich, Thomas Fogarty, Alice Jack, Thilaka Sumanaweera, Patrick Maguire, vol. 7, No. 6, June 2010.

10. The device for ultrasound diagnostics “Kranioscope-3M”, http://www.8a.ru/print/23396.php (checked on 04/13/2011).

11. Patent US 2010/0268088 A1, Multimode ultrasound focusing for medical applications, Oleg Prus, Shuki Vitek, priority from 10.21.2010.

12. Patent US 2010/0125225 A1, System for selective ultrasonic ablation, Daniel Gelbart, Samuel Victor Lichtenstein, priority dated 05/20/2010.

13. Patent US 2008/0051656 A1, Method for using high intensity focused ultrasound, Shahram Vaezy, Arthur H. Chan, Victor Y. Fujimoto, Donald E. Moore, Roy W. Martin, priority dated 02.28.2008.

14. Patent on PCT application: CN 2006/001715 20060717, Ultrasonic therapeutic system, priority dated July 17, 2006.

15. Japanese patent JP 322649 (therapeutic system that uses an apparatus of magnetic resonance imaging).

16. Patent RU No. 2147848 (prototype). The method of selective destruction of cancer cells, Zaguskin S.L., Oraevsky V.N., Rapoport S.I., priority from 05.21.1999.

Claims (9)

1. The method of non-invasive ablation and destruction of parts of the dielectric body with losses, namely, that the dielectric body is placed inside the reflective screen, the selected area of the dielectric body is exposed to radiation of the appropriate intensity and frequency using emitters placed on the reflective screen so that their maxima radiation patterns are directed inward of the volume bounded by the indicated reflective screen, the radiation from the emitters is focused sequentially at the corresponding points of choice an early portion of the dielectric body in which it is necessary to carry out the ablation and destruction procedure, characterized in that before placing the dielectric body inside the reflective screen, a volume absorber is placed inside the volume bounded by the reflective screen, each of the emitters is excited with low-power radiation with a wavelength of λ _C = 2r _Ф , where r _Ф is the given radius of the focal spot; λ _C is the field wavelength in the dielectric without loss, and each emitter is tuned to the traveling wave mode, the volume absorber is removed, then the emitters are tuned to the selected focus points, for which the first emitter is excited by a signal with an arbitrary amplitude

and phase

where

- the radius vector of the first focus point relative to the beginning of the selected coordinate system, remember the amplitude

,

and phases

,

respectively, the incident radiation and radiation reflected from the site of exposure on the dielectric body, then when the first emitter is excited, the second emitter is excited by a signal with an arbitrary complex amplitude

measure the amplitude

and phase

radiation reflected from the site of exposure on the dielectric body, while changing the value of the amplitude of the incident wave

until the ratios are satisfied:

,

where ^* is the sign of complex conjugation; And ₂ - a constant coefficient, determined during the setup process, remember the amplitude

and phase

incident wave, after that, when the first and second emitters are excited, the third emitter is excited by a signal with an arbitrary amplitude

and phase

measure the amplitude

and phase

radiation reflected from the site of exposure on the dielectric body, while changing the value of the amplitude of the incident wave

until the ratios are satisfied:

,

where A ₃ is a constant coefficient determined during the setup process, remember the amplitude

and phase

incident wave, then sequentially excite the remaining emitters in a similar manner, adjusting the amplitudes and phases of the incident wave until, respectively, the ratios:

,

, j = 4, ... n, where n is the total number of emitters; A _j is a constant coefficient determined during the tuning process, the amplitude is stored

and phase

of the incident wave, check the location of the given focus point relative to the selected area of the dielectric body, and if the emitter focusing procedure is negative, repeat the procedure, if the result is positive, the focus parameters are recorded - the amplitude and phase of each emitter, then the focusing procedures of all emitters are carried out for a given number of M points focusing on the impact site on the dielectric body and remembering the focusing parameters when the location of the point M ' blyatsii degradation and M is focusing points lying in a tetrahedron, whose vertices coincide with the coordinates

,

,

,

closest to point M ', and the distance from point M' to points with coordinates

,

,

,

is the smallest among all possible points m = 1, ... M, their complex amplitudes are determined and recorded

by interpolation:

,

Where

,

,

- radius vectors of the corresponding points;

- the distance between the points m ₃ and m ₂ ;

- the distance between points m ₃ and M ''';

- the distance between the points m ₁ and M ''';

- the distance between the points m ₁ and M '';

- the distance between points m ₄ and M '';

- the distance between points m ₄ and M '; then increase the radiation power to the value necessary for the implementation of ablation and destruction in the specified area and harmless outside the specified area, and carry out ablation and destruction at these points, while the radius of curvature a of the reflecting screen is selected from the condition

where a _diel is the radius of the dielectric body;

- the optimal radius at which at a given field power of the emitters located on the reflective screen at the focus point of the dielectric body, the maximum value of the field power flux density is achieved; the radius a ₁ together with the value a _opt determine the possible interval for choosing the radius a of the reflecting screen; the value of a ₁ depends on the permissible level p _{ADP N} of the power flux density p _N (a) on the periphery of the dielectric body normalized to the same parameter p (0) at the focusing point and is determined from the conditions

tgΔ (λ _C ) is the dielectric loss angle in the medium for the type of field used. 2. The method according to claim 1, characterized in that when determining the coordinates of the focused m = 1, ... M points and the necessary complex amplitudes of excitation

take into account the dependence of coordinates

from time t. 3. The method according to claim 1, characterized in that as the acting radiation using an ultrasonic field or an electromagnetic field. 4. The method according to claim 1, characterized in that the surface of the reflective screen has a cylindrical or spherical shape or a shape that matches the surface of the dielectric body. 5. The method according to claim 1, characterized in that harmonic or pulsed radiation is used to excite the emitters. 6. The method according to claim 1, characterized in that it further increases the radius of the ablation and destruction points by defocusing the emitters. 7. Device for non-invasive ablation and destruction of parts of a dielectric body with losses, comprising a generator, a control input of which is connected to a control and calculation unit connected to a visualization unit, ADCs and emitters placed on the surface of a reflective screen, characterized in that they are introduced in series connected n-channel power divider, n-channel switch of channels and n-channel block for controlling the excitation of emitters, the outputs of which are connected respectively to n-emitters, while the output the generator through an ADC is connected to the input of the n-channel power divider, the control inputs of the n-channel power divider, the n-channel switch channel and the n-channel emitter excitation control unit are connected respectively to the control outputs of the control and calculation unit, the first and second information inputs of which connected respectively to the information outputs of the n-channel unit for controlling the excitation of emitters, each channel of the n-channel unit for controlling the excitation of emitters consists of ice-connected signal amplitude control unit, the input of which is the input of the corresponding channel of the n-channel emitter excitation control unit, signal phase control unit, isolation and switch unit, incident and reflected wave comparison unit, and series-connected CBM meter and controlled matching unit, the output of which is the output of the corresponding channel of the n-channel block for controlling the excitation of emitters, the first input of the unit for comparing the incident and reflected waves is connected to the output of the signal phase control unit, and its second input is connected to the second output of the isolation unit, the output of the switch through a normally closed contact is connected to the output of the corresponding channel of the n-channel emitter excitation control unit, and through the normally open contact is connected to the input of the KBB meter, while the control the inputs of the signal amplitude control unit, the signal phase control unit and the controlled matching unit are the control inputs of the corresponding channel of the n-channel control unit emitters, and the outputs of the incident and reflected wave comparison unit and the KBM meter are information outputs of the n-channel emitter excitation control unit. 8. The device according to claim 7, characterized in that the generator is made in the form of a source of electromagnetic radiation or in the form of a source of ultrasonic radiation. 9. The device according to claim 7, characterized in that the surface of the reflective screen has a cylindrical or spherical shape or a shape that matches the surface of the dielectric body.

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