RU2799358C2 - Methods and devices for aesthetic therapy of biological structures using radio frequency and magnetic energy - Google Patents

Abstract

FIELD: medical equipment.

SUBSTANCE: device for magnetic therapy and RF therapy makes it possible to provide muscle contraction with a time-varying magnetic field and by heating the biological structure. It contains an applicator containing an RF electrode and a device generating a magnetic field. The device may also include a main unit, a human-machine interface and a control unit. The control unit regulates the signal delivered to the RF electrode and forms an RF circuit, and also regulates the signal delivered to the magnetic field generating device and forms a magnetic circuit electrically isolated from the RF circuit.

EFFECT: RF circuit may include a power supply and a power amplifier, and the magnetic circuit may contain an energy storage device to supply the magnetic field generating device with electric current.

17 cl, 44 dwg

Description

BACKGROUND OF THE INVENTION

[1] Aesthetic medicine includes all procedures that result in an improvement in appearance according to the criteria of the patient. Patients want to minimize all imperfections, including, for example, unwanted adipose tissue in certain areas of the body, improve body shape and eliminate the effects of natural aging. Patients require fast, non-invasive procedures that provide satisfactory results with minimal health risks.

[2] The most common methods used for non-invasive aesthetic tasks are based on the use of mechanical waves, for example, in ultrasound or shock wave therapy, or electromagnetic waves, for example, in radiofrequency therapy or light therapy, including laser therapy. The effect of mechanical waves on tissue is based on the effects of cavitation, vibration and/or warming. The effect of applications using electromagnetic waves is based on the creation of heat in the biological structure.

[3] Mechanical therapy using mechanical waves and/or pressure can be used to treat cellulite or fat cells. However, such mechanical therapies have several disadvantages, such as the risk of panniculitis, destruction of non-target tissues, and/or inhomogeneous results.

[4] Thermal therapy, including heating, is applied to a patient to improve the appearance of the skin and body, for example, by increasing the production of collagen and/or elastin, softening the skin, reducing cellulite, and/or eliminating fat cells. However, heat therapy has several disadvantages, such as the risk of overheating the patient or even heat damage to unwanted biological structures. The risk of panniculitis and/or inconsistent results can be a very common side effect of current heat therapies. In addition, insufficient blood and/or lymph flow during and/or after therapy can lead to panniculitis and other post-therapy complications. In addition, therapy may be uncomfortable and may be painful.

[5] Muscle stimulation with a time-varying magnetic field provides several advantages over known methods of biological structure therapy and allows for non-invasive stimulation of muscles located under other muscles. In addition, time-varying magnetic fields can be used to provide muscle stimulation in order to induce muscle contraction through a thick layer of adipose tissue. Electrical stimulation to produce muscle contraction must deliver an electrical current from the electrode through the adipose tissue to the nerve and/or neuromuscular plate associated with the muscle. Adipose tissue has a higher electrical resistance than muscle tissue, and delivery of electrical current from the electrode through insulating adipose tissue to muscle tissue may be less efficient. Targeting the electrical current to the right muscle can be inaccurate, and stimulating the muscle can be very difficult, almost impossible. Additionally, with thicker adipose tissue, the strength of the electric current delivered by electrotherapy must be higher, and such a large amount of electric current propagating and dissipating over a long distance can be very uncomfortable for the patient. On the other hand, time-varying magnetic fields induce an electrical current in the muscle, neuromuscular plate, and/or nerve, so that targeting and stimulating a muscle with a time-varying magnetic field is simpler, more accurate, more convenient, and more efficient. The time-varying magnetic field also allows for convenient stimulation of a large number of muscles and/or muscle groups, and the applicator may not be in direct contact with the patient's body, which may also improve hygiene and other therapy parameters.

[6] The combination of radiofrequency (RF) therapy, which provides heating of the patient's soft tissue, and magnetic therapy, which stimulates the patient's muscle tissue, can have an excellent synergistic effect. Combination therapy can provide improved therapy that can result in shorter therapy times, increased patient comfort during therapy, allow different therapeutic effects to be combined to produce synergy, improve patient safety, and provide other benefits, as detailed later in this document.

[7] In order to achieve the best synergistic effect, it is preferable to target the magnetic therapy providing muscle stimulation and the RF therapy to the same area of the body (for example, the same area of the body), where at least one RF electrode providing RF therapy should be flat. and/or conform to the patient's skin to provide uniform heating of the patient's soft tissue. In order to target RF therapy and magnetotherapy to the same area of the body, it is necessary to place the magnetic field generating device and the RF electrode close to each other, for example, so that the magnetic field generating device and the RF electrode are at least partially overlapped each other. However, placing the RF electrode and the magnetic field generating device in close proximity to each other can be problematic because the time varying magnetic field generated by the magnetic field generating device can induce unwanted physical effects such as eddy currents, skin effect and/or or other physical effects in the RF electrode. Undesirable physical effects can result in significant energy loss, inefficiency in device placement, and heating of the RF electrode, which affects the function of the device, such as misalignment of the device, inaccurate targeting of generated energies, degradation of generated magnetic and electromagnetic fields, and/ or other disadvantages. An RF electrode can be influenced by a device that generates a magnetic field, and vice versa.

[8] The device and method described in this document provides a solution for providing RF and magnetotherapy with the maximum synergistic effect, and also maintain the safety and effectiveness of the delivered magnetic and RF (electromagnetic) fields.

SUMMARY OF THE INVENTION

[9] The present invention provides a therapeutic device and method for providing one or more therapeutic effects to at least one biological structure in at least one region of the body. The therapeutic device provides a unique opportunity to shape the body of a human or animal, improve appearance, restore muscle functionality, increase muscle strength, change (for example, increase) muscle volume, change (for example, increase) muscle tone, initiating hypertrophy of muscle fibers, initiating hyperplasia of muscle fibers, reducing the number and volume of fat cells and adipose tissue, eliminating cellulite, and so on. The therapeutic device and method of therapy may use radio frequency (RF) therapy and magnetotherapy to induce heating of at least one target biological structure in a body region and induce muscle stimulation, including muscle contraction, in an adjacent or same body region. The therapeutic device may use an RF electrode as a therapeutic energy source to provide RF energy (which may be referred to as an RF field) to provide RF therapy and a magnetic field generating device as a therapeutic energy source to generate a time-varying magnetic field to provide magnetotherapy. .

[10] To improve the efficiency and safety of therapy, to minimize energy loss and undesirable physical effect induced in at least one RF electrode and / or device generating a magnetic field, the device can use one or more segmented RF electrodes, and the segmented RF electrode refers to an RF electrode containing, for example, one or more holes, notches and/or protrusions to minimize the effects of a nearby time-varying magnetic field generated by a magnetic field generating device. The opening may be an opening in the housing of the RF electrode. The notch may be an opening in the RF electrode housing along the boundary of the RF electrode. Openings in the housing of the RF electrode can be identified in the plan view, which depicts a plan view of the RF electrode. Holes, cutouts and/or areas on the outside of the protrusions may be filled with air, dielectric and/or other electrically insulating material. The holes, notches, and/or protrusions of the RF electrode can minimize the induction of eddy currents in the RF electrode, minimize energy loss, and prevent overheating of the therapeutic device. In addition, holes, cutouts, and/or protrusions can minimize the effect of magnetic therapy on RF therapy being performed. The proposed design of the RF electrode allows the same applicator to contain a device that generates a magnetic field and an RF electrode that at least partially overlap each other, according to the horizontal projection of the applicator, while simultaneously allowing RF therapy and magnetotherapy to be targeted to the same area of the patient's body with parameters described in this document. The incorporation of an RF electrode and a magnetic field generating device into one applicator allows improved targeting of therapy and provides positive therapeutic effects with minimal negative effects mentioned above.

[11] In addition, the mutual isolation of at least one RF circuit and at least one magnetic circuit prevents interaction between electrical and/or electromagnetic signals.

[12] A magnetic field generating device, in combination with an energy storage device, allows a magnetic field to be generated at an intensity (which may be a magnetic flux density) that induces muscle contraction. The energy storage device can be used to store electricity, allowing the storage of an electric field having a voltage in the range of 500 V to 15 kV. The power storage device can supply the stored electric power to the magnetic field generating device in the form of a single pulse of a few microseconds to a few milliseconds in duration.

[13] The method of therapy allows heating at least one area of the body in which muscle contraction is also caused, minimizing damage to the muscles and/or ligaments, for example, rupture or inflammation. Heating of the skin, contracted muscle, contracting muscle, relaxed muscle, adipose tissue, adipose tissue, and/or adjacent biological structure of the area of the body being treated may shift the boundary beyond which the patient may find the therapy uncomfortable.

[14] Therefore, heating can allow a large amount of electromagnetic energy (eg, RF and/or magnetic field) to be delivered to the patient's body in order to provide more muscle work through muscle contraction and subsequent relaxation. Another advantage of using RF therapy and magnetotherapy in the same area of the body is that muscle work (provided, for example, by repeated muscle contraction and relaxation) accelerates the flow of blood and lymph in the target area and thus improves the dissipation of thermal energy generated by RF therapy. The use of RF therapy and magnetic therapy also increases the homogeneity of heating of the biological structure, which prevents the formation of thermal spots, edge effects and/or other undesirable effects. A therapy that results in muscle stimulation and heat in the same area of the body can lead to excess acidity of the extracellular matrix, leading to apoptosis or necrosis of adipose tissue. RF therapy can provide selective heating of adipose tissue, resulting in at least one of apoptosis, necrosis, reduction in fat cell volume, and removal of cellulite.

BRIEF DESCRIPTION OF GRAPHICS

[15] The accompanying drawings, which are included in this document and are part of the technical description, depict the present invention and, together with the description, also serve to explain the principles of the invention and enable a person skilled in the art to make and use it.

[16] FIG. 1a-1e show illustrative schematic representations of a therapeutic device.

[17] FIG. 1f illustrative individual parts of the therapeutic device are depicted.

[18] FIG. 2 is an exemplary diagram of connections between parts of the device, such as an applicator, a remote control, an additional therapeutic device, and a communication device.

[19] FIG. 3 is an exemplary diagram of the connections between the server and parts of the device, such as applicators, remote control, and additional therapeutic devices.

[20] FIG. 4 is an exemplary diagram of the communications between the communication medium, the therapeutic generator, and the host unit of the therapeutic device.

[21] FIG. 5 depicts the relationship between the communication medium and the therapeutic generator of the therapeutic device.

[22] FIG. 6 depicts different views of an exemplary main body of a therapeutic device.

[23] FIG. 7 depicts an exemplary Human Machine Interface (HMI).

[24] FIG. 8a-8d are external views of parts of an exemplary applicator.

[25] FIG. 9a shows an exemplary magnetic field generating device in plan view of an applicator.

[26] FIG. 9b shows the thickness of an exemplary magnetic field generating device.

[27] FIG. 10a-10g depict possible locations for an exemplary RF electrode relative to an exemplary magnetic field generating device.

[28] FIG. 11 is a plan view of the location of an exemplary RF electrode relative to an exemplary magnetic field generating device.

[29] FIG. 12 is a plan view of an applicator containing RF electrodes and a magnetic field generating device partially overlapping each other, according to a plan view of the applicator.

[30] FIG. 13a-13b depict an exemplary apertured RF electrode.

[31] FIG. 13c depicts an exemplary RF electrode with holes, projections, and notches.

[32] FIG. 13d shows another exemplary RF electrode with holes and cutouts.

[33] FIG. 13e depicts an exemplary RF electrode with projections.

[34] FIG. 14a-14e show a parallel pair of protrusion bipolar RF electrodes.

[35] FIG. 15a-15c depict pairs of protrusion bipolar RF electrodes, wherein the first RF electrode at least partially surrounds the second RF electrode in the RF electrode pair.

[36] FIG. 16 depicts one exemplary protrusion crossing magnetic field lines with a difference greater than 0.1 Tesla.

[37] FIG. 17 is an exemplary diagram of a magnetic circuit.

[38] FIG. 18a is an exemplary diagram of the electrical components of a therapeutic device.

[39] FIG. 18b shows an exemplary RF circuit diagram.

[40] FIG. 19 depicts an exemplary composition of the magnetic field, including single pulses or pulses.

[41] FIG. 20 shows a trapezoidal envelope.

[42] FIG. 21 shows different types of muscle stimulation.

[43] FIG. 22 shows a carrier matrix for attaching an applicator and/or additional therapeutic device to a patient's body.

[44] FIG. 23 is a sectional view of a first side portion of an exemplary curved applicator.

[45] FIG. 24 shows an exemplary balancing element SYM.

[46] FIG. 25 is an exploded view of the applicator elements.

[47] FIG. 26 depicts an exemplary spatial arrangement of components within a main body of a therapeutic device.

[48] FIG. 27a-27d show an example of the simultaneous application of magnetic fields.

[49] FIG. 27e shows an example of separate application of magnetic fields.

[50] FIG. 28 shows an exemplary increasing magnetic field envelope.

[51] FIG. 29 shows an exemplary decreasing magnetic field envelope.

[52] FIG. 30 shows an exemplary rectangular magnetic field envelope.

[53] FIG. 31 shows an exemplary combined magnetic field envelope.

[54] FIG. 32 shows another exemplary combined magnetic field envelope.

[55] FIG. 33 shows an exemplary triangular magnetic field envelope.

[56] FIG. 34 shows an exemplary trapezoidal magnetic field envelope.

[57] FIG. 35 shows another exemplary trapezoidal magnetic field envelope.

[58] FIG. 36 shows another exemplary trapezoidal magnetic field envelope.

[59] FIG. 37 shows an exemplary stepped magnetic field envelope.

[60] FIG. 38 shows another exemplary stepped magnetic field envelope.

[61] FIG. 39 shows another exemplary trapezoidal magnetic field envelope.

[62] FIG. 40 shows an example of a magnetic field envelope including modulation in the repetition rate region.

[63] FIG. 41 shows an exemplary trapezoidal envelope formed from magnetic field sequences.

[64] FIG. 42 shows another exemplary combined magnetic field envelope.

[65] FIG. 43 shows another exemplary combined magnetic field envelope.

[66] FIG. 44 shows two illustrative magnetic field envelopes with an example of a period between the envelopes.

DETAILED DESCRIPTION

[67] The present therapeutic device and its method of use provide a new physiotherapy and/or aesthetic therapy by combining RF therapy and muscle stimulation therapy that aims at different therapeutic effects, for example, for rejuvenation, healing and/or remodeling of at least parts of at least one biological structure of the patient's tissue in at least one region of the body.

[68] A biological structure may be any tissue in the human and/or animal body that may have an identical function, structure, and/or composition. The biological structure may include or be at least part of any type of tissue such as: connective tissue (eg tendons, ligaments, collagen, elastin fibers), adipose tissue (eg subcutaneous adipose tissue and/or visceral adipose tissue), bone, dermis and/or other tissue, e.g. at least one neuron, neuromuscular plate (neuromuscular junction), muscle cell, one or more individual muscles, muscle group, at least part of a muscle fiber, extracellular matrix volume , endocrine gland, nervous tissue (eg, peripheral nervous tissue, neuron, neuroglia, neuromuscular plate) and/or a joint or part of a joint. For the purposes of this application, a biological structure may be referred to as a target biological structure.

[69] The therapeutic effect provided to at least a portion of at least one target biological structure may include muscle contraction (including supramaximal contractions and/or tetanic contractions), muscle twitching, muscle relaxation, and heating of the biological structure). Also, the therapeutic effect may include, for example, remodeling of the biological structure, reduction in the number and/or volume of fat cells by apoptosis and/or necrosis, muscle strengthening, increase in muscle volume, initiation of muscle fiber hypertrophy, muscle fiber hyperplasia, restoration of muscle functionality, proliferation myosatellitocytes and/or differentiation into muscle cells, improved muscle shape, improved muscle endurance, muscle shaping, muscle relaxation, muscle volume reduction, collagen fiber restructuring, neocollagenesis, elastogenesis, collagen therapy, improved blood and lymph flow, development of at least part at least one target biological structure and/or other functions or benefits. During therapy of a body region with a therapeutic device, more than one therapeutic effect may be provided, and different therapeutic effects may be combined.

[70] The therapeutic effect provided to the target biological structure may result in body shaping, body contouring, body toning, muscle toning, muscle shaping, body shaping, breast lift, buttock lift, buttock rounding, and/or hardness of the buttocks. In addition, providing a therapeutic effect can result in body rejuvenation, such as wrinkle reduction, skin rejuvenation, skin tightening, skin color uniformity, skin sagging reduction, lip enhancement, cellulite reduction, stretch mark reduction, and/or scar removal. The therapeutic effect may also lead to an acceleration of the healing process, a decongestant effect and/or other physiotherapeutic and therapeutic effect.

[71] The therapeutic device may provide one or more types of therapeutic energy, wherein the therapeutic energy may include a magnetic field (also referred to as magnetic energy) and an RF field (also referred to as RF energy) and/or a magnetic field (also referred to as magnetic energy). A magnetic field is provided during magnetotherapy. The RF field provided during RF therapy may include an electrical component of the RF field and a magnetic component of the RF field. The electrical component of the RF field may be referred to as the RF wave or RF waves. The RF electrode may generate an RF field, RF waves, and/or other RF field components.

[72] The magnetic field and/or RF field may be characterized by intensity. In the case of a magnetic field, the intensity may include magnetic flux density or magnetic flux density amplitude. In the case of an RF field, the intensity may include the energy flux density of the RF field or RF waves.

[73] The body region may include at least a portion of the patient's body including at least one muscle or group of muscles covered by another soft tissue structure, such as adipose tissue, skin, and/or other. The area of the body may be subjected to therapy performed by the therapeutic device. The body region can be a part of the body such as the buttock, outer thigh fat, waist fat, abdomen, hip, leg, calf, thigh, arm, torso, shoulder, knee, neck, limb, body fat in chest area, face or chin and/or any other tissue. For the purposes of this description, the term "body region" may be used interchangeably with the term "body region".

[74] Skin tissue consists of three main elements: the epidermis, dermis and hypodermis, the so-called subcutaneous tissue. The outer and thinnest layer of the skin is the epidermis. The dermis is made up of collagen, elastic connective tissue, and reticular fibers. The hypodermis is the lowest layer of the skin and contains hair follicle roots, lymphatic vessels, collagen tissue, nerves, and subcutaneous white adipose tissue (SWAT) fat. Adipose tissue may refer to at least one lipid-rich cell, for example, an adipose cell such as an adipocyte. Fat cells form lobules connected by connective tissue, fibrous membranes (retinaculum cutis).

[75] Another part of adipose tissue, the so-called visceral adipose tissue, is located in the abdominal cavity and forms visceral white adipose tissue (VWAT), located between the parietal peritoneum and the visceral peritoneum, closely below the muscle fibers adjacent to the hypodermis layer.

[76] A muscle may include at least a portion of a muscle fiber, an entire muscle, a group of muscles, a neuromuscular plate, a peripheral nerve, and/or a nerve innervating at least one muscle.

[77] Deep muscle may refer to muscle that is at least partially covered by superficial muscles and/or muscle covered by a thick layer of other tissue, such as adipose tissue, where the thickness of the overlying layer can be from at least 4.5, 7, 10 or more centimeters up to 15 cm.

[78] Individual muscles may be abdominal muscles, including rectus abdominalis, obliquus abdominalis, transversus abdominis, and/or quadratus lumborum. Individual muscles may be the gluteal muscle, including the gluteus maximus, gluteus medius, and/or gluteus minimus. Individual muscles may be those of the lower limb, including quadriceps femoris, Sartorius, gracilis, biceps femori, adductor magnus longus/brevis, tibialis anterior, extensor digitorum longus, extensor hallucis longus, triceps surae, gastroenemiis lateralis/medialis, soleus, flexor hallucis longus , flexor digitorum longus, extensor digitorum brevis, extensor hallucis brevis, adductor hallucis, abductor halluces, ab/adductor digiti minimi, abductor digiti minimi and/or interossei plantares). The ligament may be Cooper's ligament of the breast.

[79] One example would be the application of a therapeutic device and method of therapy to the abdomen of a patient, which may provide a therapeutic effect (or where the therapy may subsequently lead to such an effect), e.g., reduction in the number and volume of fat cells, strengthening of muscles, elimination of fat , restructuring of collagen fibers, acceleration of neocollagenesis and elastogenesis, muscle strengthening, improvement of muscle functionality, muscle endurance and muscle shape. These therapeutic effects can lead to a reduction in the circumference of the abdominal region, the elimination of sagging and/or strengthening of the abdominal region, the reduction of cellulite, the reduction of scars, as well as the improvement of body posture by strengthening the abdominal muscles, which can also improve body contour, body appearance and health. patient.

[80] One other example would be the application of a device and method of therapy to an area of the body including the buttocks, which may provide a therapeutic effect (or where the therapy may subsequently lead to such an effect), for example, reduction in the number and volume of fat cells, restructuring of collagen fibers , accelerating neocollagenesis and elastogenesis, strengthening muscles, increasing muscle tone and shaping muscles. These therapeutic effects may result in waist or buttock circumference reduction, buttock tightening, buttock rounding, buttock firming and/or cellulite elimination.

[81] Another example would be the application of a therapeutic device and method of therapy to an area of the body including the thighs, which may result in a reduction (or where the therapy may subsequently result in such a reduction) in the number and volume of fat cells, muscle strengthening, muscle shaping and increased muscle tone. Application of the therapeutic device and method of therapy to the area of the body, including the thigh, can lead to a reduction in the circumference of the thigh, elimination of sagging abdomen and reduction of cellulite.

[82] Yet another example would be the application of a therapeutic device and method of therapy to an area of the body including the arm, which may result in a reduction (or where the therapy may subsequently result in such a reduction) in the number and volume of fat cells, muscle strengthening, muscle shaping and increased muscle tone. Application of the therapeutic device and method of therapy to the area of the body, including the arm, can lead to a reduction in the circumference of the abdominal region, elimination of sagging abdomen and reduction of cellulite.

[83] One or more therapeutic effects provided to one or more target biological structures may be based on selectively targeting the RF field into the interior of one or more biological structures and providing heat along with the application of a magnetic field causing muscle stimulation (including muscle contraction). RF therapy may result in selective heating of one or more biological structures, polarization of the extracellular matrix, and/or alteration of the potential of cell membranes in the patient's body. The magnetic field may be a time-varying magnetic field or a static magnetic field. When a time-varying magnetic field is used, magnetotherapy may be referred to as time-varying magnetotherapy. Magnetotherapy can cause muscle contraction, muscle relaxation, cell membrane polarization, eddy current induction, and/or other therapeutic effects caused by generating a time-varying magnetic field in at least a portion of one or more targeted biological structures. A time-varying magnetic field can induce an electric current in a biological structure, and an induced electric current can lead to muscle contraction. Muscle contractions can be multiple. Muscle contraction provided by the magnetic field may include supramaximal contraction, tetanic contraction, and/or incomplete tetanic contraction. In addition, the magnetic field can also cause muscle twitches.

[84] The therapeutic effect provided by the use of a therapeutic device and the use of magnetotherapy and RF therapy can be combined. For example, reduction in the number and volume of fat cells can be achieved along with muscle strengthening, muscle shaping, and/or muscle toning during actual therapy or for some time (eg, three or six months) after therapy. In addition, the effect provided by the use of the therapeutic device and the use of magnetotherapy and RF therapy may be cumulative. For example, an increase in muscle tone can be achieved by reducing the number and volume of fat cells in combination with muscle strengthening.

[85] The method of therapy can provide a therapeutic effect to at least one target biological structure through heat therapy provided by the RF field, in combination with applied magnetotherapy. The therapeutic effect can be provided to the target biological structure by heating at least one biological structure and initiating at least partial muscle contraction or muscle contraction through magnetic therapy.

[86] The method of therapy may provide heating of the area of the body where muscle contraction is initiated using a magnetic field. Heat can minimize muscle damage and/or ligament damage, including rupture or inflammation. Heating of the contracting muscle and/or adjacent biological structure can also shift the threshold for discomfort in therapy. Therefore, the heating caused by the RF field may allow more magnetic energy to be delivered to the patient's biological structure to increase muscle work. Heating the muscle and/or adjacent biological structure can also increase the quality and/or level of muscle contraction. Due to the heating provided by the RF field, more muscle fibers and/or a longer portion of the muscle fiber can contract during magnetic therapy. Heating also improves the penetration of muscle stimuli generated by magnetotherapy. Additionally, by repeated initiation of at least partial muscle contraction or full muscle contraction, the threshold for uncomfortable heating experienced by the patient may also be shifted to a higher level. Such a threshold shift may allow more RF energy to be delivered to the patient's body.

[87] Repeated muscle contraction followed by muscle relaxation, combined with heat, can suppress discomfort caused by muscle stimulation (eg, muscle contraction). Muscle stimulation combined with heat may provide improved post-therapy regeneration and/or better prevention of panniculitis and other tissue damage.

[88] Repeated muscle contraction followed by muscle relaxation in combination with RF heating (according to preliminary trials) may have positive results for therapy and/or suppression of diabetes symptoms. Repeated muscle contraction caused by the applied magnetic field, together with the heating of the biological structure by the RF field, can also improve the outcome of the treatment of diabetes symptoms or positively influence the results of drug treatment of the symptoms of diabetes. The success of treating the symptoms of diabetes can be due to the penetration of a large amount of RF energy deep into the patient's abdomen. Such penetration can be caused by the simultaneous application of magnetic therapy, which can lead to the suppression of the patient's discomfort caused by the high density of the RF energy flux and the increase in tissue temperature. Also, magnetic therapy can lead to polarization and depolarization of the patient's tissue, which can also increase the penetration of RF energy into the patient's body. RF therapy and/or magnetotherapy may influence glucose metabolism or promote weight loss, which may suppress symptoms of diabetes. It is believed that weight loss and exercise in patients with symptoms of diabetes may contribute to the suppression of symptoms of diabetes.

[89] The use of RF therapy through an RF field in combination with magnetotherapy through a magnetic field can also positively influence the proliferation and differentiation of myosatellitocytes into muscle cells. The test results show that magnetic therapy, including periods of time with different duration, repetition rate and magnetic flux density (for example, pulses or sequences, as defined below) can provide the stimulation necessary to start the proliferation and differentiation of myosatellocytes.

[90] The test results also show that a method of therapy providing a magnetic field, including at least two or at least three consecutive periods of time with different duration, repetition rate and magnetic flux density (for example, pulses, packets or sequences, as defined below), can have a percussive effect on the muscle. As a consequence, a regeneration process can be started, which leads to proliferation and differentiation of myosatellitocytes, and this can be subsequently accelerated by the delivered RF field. Proliferation and differentiation of myosatellitocytes can lead to muscle strengthening, restoration of muscle functionality, increase in muscle volume and improvement in muscle shape, body tone or muscle tone.

[91] The method of applying at least partial muscle stimulation or muscle contraction along with heating to the same area of the body can lead to excess acidity of the extracellular matrix. Excessive acidity can lead to apoptosis of adipose tissue and accelerate weight loss and loss of body volume. Excess acidity can be caused by the release of fatty acids into the extracellular matrix, and the release of fatty acids can be caused by concentrated and high-intensity muscle work. Concentrated and high-intensity muscle work can be provided by a large number of repeated muscle contractions caused by the application of a time-varying magnetic field generated by the described magnetic field generating device and therapeutic device.

[92] The therapeutic effect of RF therapy can be enhanced by magnetotherapy, for example, by reducing or eliminating the risk of panniculitis or local inflammation of the skin, since any accumulation of adipocytes can be prevented due to improved metabolism. Improved blood and/or lymph flow may help remove adipocytes. The removal of adipocytes can also be facilitated by an increased number of cells that carry out phagocytosis of adipocytes. The synergistic effects of magnetotherapy and radiofrequency (RF) therapy significantly increase metabolism. Therefore, the risk of side effects is limited and the therapy results provided by the present invention are achieved in a shorter period of time.

[93] The therapeutic device and method of therapy can provide therapy to the same area of the patient's body, and magnetotherapy and RF therapy can be targeted inside at least part of one or more biological structures. One or more tissue volumes of the patient's body, which are affected by the target RF and/or magnetotherapy, may be close to each other. The volume of at least a portion of at least one or more exposed biological tissue structures of a patient's body can be defined as the exposed tissue volume in which the therapeutic effect provided by the therapeutic device and/or method of therapy described above occurs. The therapeutic effect can be caused by repeated muscle contraction (eg, provided by magnetotherapy), a change in tissue temperature (eg, provided by RF therapy), and/or at least partial polarization and acceleration of molecules in the patient's tissue (preferably provided by RF therapy and magnetotherapy). A change in tissue temperature may include, for example, an increase in tissue temperature of at least 3°C, or 4°C, or 5°C, or 6°C, or 7°C, or 10°C relative to normal tissue temperature. In addition, a change in tissue temperature may include an increase or decrease in tissue temperature in the range of 1°C to 50°C, 2°C to 30°C, or 2°C to 25°C compared to untreated tissue that is in the same or a different area of the body. A change in tissue temperature can be interpreted as a change in temperature in any volume or any area of biological tissue.

[94] Proximity of tissue volumes exposed to at least one RF therapy and/or at least one magnetic therapy denotes the distance between two exposed tissue volumes. At least two exposed volumes of tissue located close to each other may at least partially overlap each other, and from 2% to 15%, or from 5% to 30%, or from 2% to 100%, or from 30 % to 60%, or 80% to 100%, or 40% to 85% of the less exposed tissue volume may be covered by the larger tissue volume exposed. Also, the distance between volumes of tissue exposed may be in the range of 0.01 cm to 10 cm, or in the range of 0.01 cm to 5 cm, 0.01 cm to 3 cm, or 0.01 cm to 1 cm. Alternatively, overlap in the ranges mentioned above can be applied to two or more exposed tissue volumes having the same volume without any differentiation between smaller or larger tissue volumes.

[95] FIG. 1a-1e show illustrative schematic representations of a therapeutic device. Schematic representations can only be applied to the main unit and applicator. The therapeutic device may include an input interface 103, a control system 104, a power supply 105, a power supply network 106, one or more therapeutic clusters 107, and one or more therapeutic energy sources 108.

[96] Multiple therapeutic energy sources 108 can be connected to or communicate with at least one therapeutic cluster 107. The control system 104 may be connected to and communicate with each therapy cluster.

[97] The depicted portions of the therapeutic device in FIG. 1a-1e may represent electrical circuit elements. Also, one or more of the parts shown schematically in FIG. 1a-1e may contain several separate electrical elements. Electrical elements can generate, send, modify, receive or transmit an electromagnetic signal (eg, an electrical signal) between individual electrical elements. An electromagnetic signal may be characterized by current, voltage, phase, frequency, envelope, current, signal amplitude, and/or a combination thereof. When the electromagnetic signal reaches the therapeutic energy source, the corresponding therapeutic energy source may generate therapeutic energy and/or a field.

[98] The interface 103 input can receive data entered by the user. The input interface may include a human machine interface (HMI). The HMI may comprise one or more displays, such as a liquid crystal display (LCD), a light-emitting diode (LED) display, an organic LED (OLED) display, which may also include a touch display. The HMI may include one or more controls for adjusting or controlling the therapeutic device. The control element may be at least one button, lever, dial, switch, knob, slider, pointer, touch pad, and/or keyboard. The input interface may communicate or be connected to the control system and the power supply network.

[99] The user may be an operator (eg, doctor, technician, nurse) or the patient itself, however, only the patient can operate the therapeutic device. In most cases, the therapeutic device can be operated by a user with suitable training. In most cases, the user can be anyone who influences therapy parameters before or during therapy, except for the patient.

[100] The control system 104 may include a master unit or one or more control units. The control system may be an integral part of the input interface 103 . The control system 104 can be controlled via the input interface 103 . The control system may include one or more control elements for adjusting or controlling any part or electrical elements of the therapeutic device. A master unit is a part of a therapeutic device (e.g. applicator and/or main unit) or an electrical circuit element that can be selected by the user and/or the therapeutic device to establish master-slave communication, including high priority commands, with other parts. therapeutic device. For example, the master unit may be a control unit or part of an input interface that provides high priority commands to other parts of the therapeutic device. The therapeutic device may comprise a master-slave link chain. For example, therapy cluster 107 may contain one control unit that provides commands to the electrical elements of therapy cluster 107, while therapy cluster control unit 107 is a slave to the master unit. The control system 104 may be connected or communicated with the input interface 103, one or all of the power supplies 105, the power supply network 106, and/or with one or all of the therapeutic clusters present in the therapeutic device. The control system 104 may include one or more processors (eg, microprocessors) or process control blocks (PCBs).

[101] Power source 105 may provide electrical energy, including an electrical signal, to one or more therapeutic clusters. The power supply may include a module that converts AC voltage to DC voltage.

[102] The power supply network 106 may be a power plug. The power supply network may be a connection to the power system. However, the power supply network may be a battery to operate the therapeutic device without the need for a power grid. The power supply network may provide the electrical energy required for operation to the entire therapeutic device and/or parts thereof. As shown in the illustrative schematic drawings in FIG. 1a-1e, the power supply network provides electrical power to the input interface 103, the control system 104, and the power source 105.

[103] The therapeutic cluster 107 may contain one or more electrical elements associated with the generation of appropriate therapeutic energy. For example, a therapy cluster for magnetotherapy (designated as HIFEM) may contain, for example, an energy storage element and a switching device. As another example, an RF therapy cluster (referred to as an RF cluster) may comprise, for example, a power amplifier and/or a filter.

[104] The therapeutic energy source 108 may comprise a specific therapeutic energy source. In the case of magnetotherapy, the source of therapeutic magnetic field energy may be a device that generates a magnetic field, such as a magnetic coil. In the case of RF therapy, the source of therapeutic RF energy (including RF waves) may be an RF electrode.

[105] The therapeutic device may contain one or more circuits for therapy. One circuit for therapy may contain an energy supply, electrical elements of one therapeutic cluster and one corresponding source of therapeutic energy. In the case of magnetotherapy, the magnetic circuit may contain a power supply, a HIFEM cluster, and a device that generates a magnetic field. In the case of RF therapy, the RF circuit may comprise a power supply, an RF cluster, and a device that generates a magnetic field. The electromagnetic signal generated and/or transmitted internally for RF therapy may be referred to as an RF signal. Wiring connecting the respective electrical elements of one therapeutic cluster may also be included in the respective cluster. Each of the therapeutic clusters in FIG. 1a-1e, detailed below, may be any of HIFEM, RF, or combinations thereof.

[106] One or more circuits for therapy and/or parts thereof can be independently controlled or regulated by any part of the control system 104. For example, the rate of operation of the HIFEM cluster of one therapy strand can be controlled independently of the rate of operation of the HIFEM cluster of another therapy strand. In another example, the amount of energy flux delivered by operation of the RF electrode of one therapy circuit may be set independently of the operation of the RF electrode of another therapy circuit.

[107] FIG. 1a shows an illustrative schematic diagram of a therapeutic device comprising an input interface 103, a control system 104, a power supply 105, a power supply network 106, two therapeutic clusters, including therapeutic cluster A 107a, therapeutic cluster B 107b, therapeutic energy source A 108a, and therapeutic energy source B 108b. energy. In such a case, the therapeutic device may comprise two therapy circuits. One therapy circuit may comprise a power source 105, a therapeutic cluster A 107a, and/or a therapeutic energy source A 108a. Another circuit for therapy may contain a source 105 energy supply, therapeutic cluster B 107b and/or source B 108b therapeutic energy. Therapy clusters 107a and 107b can communicate with each other.

[108] FIG. 1b shows an exemplary schematic diagram of a therapeutic device comprising an input interface 103, a control system 104, two power supplies including a power supply A 105a and a power supply B 105b, a power supply network 106, two therapeutic clusters including a therapeutic cluster A 107a and a therapeutic cluster B 107b , source A 108a therapeutic energy and source B 108b therapeutic energy. In such a case, the therapeutic device may comprise two circuits for therapy. One circuit for therapy may contain an energy source 105a, a therapeutic cluster A 107a and/or a therapeutic energy source A 108a. The other circuit for therapy may comprise an energy supply B 105b, a therapeutic cluster B 107b, and/or a therapeutic energy source B 108b. Therapy clusters 107a and 107b can communicate with each other.

[109] FIG. 1c shows an exemplary schematic diagram of a therapeutic device comprising an input interface 103, a control system 104, a power supply 105, a power supply network 106, two therapeutic clusters including therapy cluster A 107a and therapy cluster B 107b, and one therapeutic energy source 108. In such a case, the therapeutic device may comprise two therapy circuits. One circuit for therapy may contain a source 105 of energy supply, therapeutic cluster A 107a and/or source 108 of therapeutic energy. Another chain for therapy may contain a source 105 energy supply, therapeutic cluster B 107b and/or source 108 therapeutic energy. Therapy clusters 107a and 107b can communicate with each other. The schematic diagram shown may include a magnetic field generating device providing both RF therapy and magnetotherapy.

[110] FIG. 1d shows an illustrative schematic diagram of a therapeutic device, comprising an input interface 103, a control system 104, a power source 105, a power supply network 106, four therapeutic clusters, including therapeutic cluster A1 107a, therapeutic cluster A2 107aa, therapeutic cluster B1 107b, therapeutic cluster B2 107bb, and four therapeutic energy sources including therapeutic energy source A1 108a, therapeutic energy source A2 108aa, therapeutic energy source B1 108b, and therapeutic energy source B2 108bb. In such a case, the therapy device may comprise four therapy circuits. The first therapy circuit may comprise a power supply 105, a therapeutic cluster A1 107a, and/or a therapeutic energy source 108a. The second therapy circuit may comprise an energy supply 105, a therapeutic cluster A2 107aa, and/or a therapeutic energy source A2 108aa. The third therapy circuit may comprise a power supply 105, a therapeutic cluster B1 107b, and/or a therapeutic energy source B1 108b. The fourth therapy circuit may comprise an energy supply 105, a therapeutic cluster B2 107bb, and/or a therapeutic energy source B2 108bb. The therapeutic energy sources of the first therapy circuit and the second therapy circuit can be located in one applicator, while the therapeutic energy sources of the third therapy circuit and the fourth therapy circuit can be located in another applicator.

[111] FIG. 1e shows an exemplary schematic diagram of a therapeutic device comprising an input interface 103, a control system 104, two power supplies including a power supply A 105a and a power supply B 105b, a power supply network 106, four therapeutic clusters including a therapeutic cluster A1 107a, a therapeutic cluster A2 107aa , therapy cluster B1 107b, therapy cluster B2 107bb, and four therapeutic energy sources, including therapeutic energy source A1 108a, therapeutic energy source A2 108aa, therapeutic energy source B1 108b, and therapeutic energy source B2 108bb. In such a case, the therapy device may comprise four therapy circuits. The first circuit for therapy may include a power source A 105a, a therapeutic cluster A1 107a, and/or a therapeutic energy source 108a. The second therapy circuit may comprise an energy supply A 105a, a therapeutic cluster A2 107aa, and/or a therapeutic energy source A2 108aa. The third therapy circuit may comprise an energy supply B 105b, a therapeutic cluster B1 107b, and/or a therapeutic energy source B1 108b. The fourth therapy circuit may comprise an energy supply B 105b, a therapeutic cluster B2 107bb, and/or a therapeutic energy source B2 108bb. The therapeutic energy sources of the first therapy circuit and the second therapy circuit can be located in one applicator, while the therapeutic energy sources of the third therapy circuit and the fourth therapy circuit can be located in another applicator.

[112] FIG. 1f shows separate parts of a therapeutic device, including a main unit 11 coupled or associated with at least one applicator 12, a remote control 13, an additional or additional therapeutic device 14 and/or a communication device 15. The additional therapeutic device may have the same level of independence as the entire therapeutic device.

[113] The therapeutic device may include a remote control 13 . The remote control 13 may include a discomfort indication button for safety purposes, so that when the patient experiences any discomfort during therapy, the user can press the discomfort indication button. When the discomfort indication button is pressed, the remote controller 13 can send a signal to the main unit and stop therapy. Also, the remote control 13 can inform the user through a human-machine interface (HMI). To stop therapy due to discomfort, pressing the discomfort indication button can override commands from the master unit. Alternatively, the discomfort indication button may be connected to the main unit 11 or be part of it.

[114] The main unit 11 may be coupled or connected to one or more additional therapeutic devices 14 that can receive electrical power from the main unit 11. devices 14. Also, one or more additional therapeutic devices 14 can also receive electricity from its own source or sources of energy. Each of the communication device 15, additional therapeutic device 14, remote control 13 and at least one applicator 12 can communicate with the main unit 11. Communication can include sending and/or receiving information. Data can be exchanged via wired and/or wireless communication such as the Internet, LAN, RF waves, sound waves, optical waves, 3G, 4G, 5G, GSM, HUB switch, LTE network, GSM network, Bluetooth, and /or other communication methods or protocols.

[115] Additional therapeutic device 14 can be any device capable of transmitting at least one type of therapeutic energy (for example: RF field, magnetic field, ultrasound, light, time-varying mechanical pressure, shock wave, or electrical current) to the patient's body in order to cause a therapeutic effect in at least one target biological structure. Additional therapeutic device 14 may include at least one electrical element that generates therapeutic energy for at least one therapy, such as magnetic, radio frequency, light, ultrasound, heating, cooling, massage, plasma and/or electrotherapy. Additional therapeutic device 14 may be capable of providing at least one therapy without commands from main unit 11. Additional therapeutic device 14 may communicate with main unit 11, communication device 15, and/or other additional therapeutic devices 14. Additional therapeutic devices 14 may represent any other device of the same or another company, and this device may be able to provide one or more specific types of therapeutic energy. The additional therapeutic device 14 may be an extension of the therapeutic device, wherein the additional therapeutic device 14 may provide therapeutic energy with parameters determined by the HMI of the main unit 11.

[116] The communication device 15 may be wired and/or wirelessly connected to the main unit 11. The communication device 15 may be a computer, such as a laptop or desktop computer, or a mobile electronic device, such as a smartphone, or an electronic tablet. The communication device may send and/or receive information related to therapy, functionality of the therapeutic device, and/or other information. Additional therapeutic device 14 and/or communication device 15 may communicate directly with the main unit 11 or indirectly with the main unit 11 using one or more additional devices or communication devices. To ensure communication, the communication device may include a receiver, a transmitter and a control unit for processing sent and/or received information.

[117] Information sent to and/or received from a separate part of the therapeutic device may include data from communication between communication device 15 and main unit 11, data from communication between applicator 12 and main unit 11, data from communication between additional therapeutic device 14 and the main unit 11 and/or data from the communication between the remote control 13 and the main unit 11. The sent and/or received information may be stored in the data logger, cloud storage and/or other storage devices. The data logger may be part of the main unit 11 or any other part of the therapeutic device. The other storage device may be a USB device, another storage device, and/or an internal memory communication device. At least some of the sent and/or received information may also be displayed using the HMI. The sent and/or received information can be displayed, evaluated and/or modified by user actions via the HMI and/or automatically by the control system. One type of information sent and/or received may be a predetermined or current value or a selection of one or more therapy parameters or patient information. The patient information may include, for example, the gender of the patient, the age and/or body type of the patient.

[118] Sent and/or received information may also inform external control bodies such as a support center, for example, a service department and/or a sales department, which are also a subset of communication devices. Information sent to and/or received from external controls may include information about the status of the therapeutic device, the history of one or more therapies performed, the history of the therapeutic device, software update information, wear information, RF electrode life, service life device that generates a magnetic field, therapy alerts, therapy credit/billing information, such as information about the number of treatments or credits paid, and/or other performance and usage information.

[119] One possible type of information sent and/or received may be recognition of the attachment of one or more applicators 12, a remote control 13, additional therapeutic devices 14, and/or communication devices 15. According to the information, the therapeutic device may manually or automatically recognize the type of additional therapeutic device 14 and/or applicator 12 attached. Automatic recognition may be provided by the control system. Based on information about the attachment of one or more applicators 12, the attachment of additional therapeutic devices 14 and/or communication devices 15, the therapeutic device may provide an update to the HMI, display notification of attachment to the applicators, and/or possible optimization of new therapy options. Possible optimization of new therapy options may include, for example, adjusting at least one therapy parameter, activating an additional therapeutic energy source, changing the parameters of the new therapeutic energy source, and/or others. The therapy device (e.g., control system) may automatically adjust or suggest adjustments to therapy parameters based on the newly attached applicator 12 and/or additional therapeutic devices 14. Recognition of the attached applicator 12, additional therapy device 14, and/or communication device 15 may be based on special connectors (for example, on a special pin connector). Also, connection recognition can be provided by a specific physical characteristic, for example, the impedance of the connected part, or a specific signal applied by the applicator or its connected part to the main unit 11. The connection between the separate parts of the therapeutic device, for example, the main unit 11, the applicator 12, the console 13 remote control, additional therapeutic device 14 and/or communication device 15 may be provided by wired and/or wireless communication (eg, RFID tag, RF, Bluetooth and/or light electromagnetic pulses). The applicator 12 can be connected to the main unit 11 with a wire to generate sufficient electricity. Alternatively, the applicator may be wirelessly connected to communicate with the main unit 11 and/or with the communication device 15. The attached applicator 12, additional therapeutic device 14 and/or communication device 15 can be recognized using software, a specific binary ID, manual recognition of parts selected from a list implemented in the therapeutic device, and/or using a pairing application.

[120] The connecting side in the main unit 11 may include a unit capable of reading and/or recognizing information contained in the connecting side of the applicator and/or the connecting side of the additional therapeutic device. Based on the read and/or recognized information, the applicator and/or additional therapeutic device can be recognized by the main unit 11. The connecting side of the main unit 11 can serve as a connecting element of the first side in the connection, while the connection of the applicator or additional therapeutic device can serve as connecting element of the second side in the connection. Sending information, receiving information and/or recognition of the second side connector by the first side connector may be based on the binary information received by the conductive contact between the two sides of the connection, by optical reading and/or by the recognition provided by the first side connector. Optical recognition may be based, for example, on reading specific QR codes, barcodes, and the like for specific applicators 12.

[121] The first side connector located in the main unit 11 may include a unit capable of reading/recognizing binary information implemented in the second side connector of the cable from the applicator 12 and/or additional therapeutic device 14. The information implemented in the second side connector hand, can be stored on the SD card. Based on such implemented information, any part of the therapeutic device can be recognized by the main unit 11.

[122] Communication between separate parts of the therapeutic device (including, for example, the main unit 11, the remote control, one or more applicators, one or more additional therapeutic devices and/or communication devices) can be based on peer-to-peer communication (denoted as P2P) and/or master-slave communications. During P2P communication, the individual parts of the therapeutic device have the same command priority and/or can communicate directly with each other. P2P communication can be used during the initial recognition of the connected separate parts of the therapeutic device. P2P communication can be applied between some parts of the therapeutic device during therapy, for example, between communication devices.

[123] Master-slave communication can be applied between separate parts of a therapeutic device for at least a short time during, before and/or after each treatment of an individual patient. During master-slave communications, one part of the therapeutic device may issue commands with the highest priority. A separate part of the therapeutic device, such as the main unit 11, may issue commands with the highest priority and be called the master unit. The therapeutic device may comprise at least one master-slave communication between individual electrical elements, such as a power supply and/or one or more control units, where one or more control units act as a master device.

[124] The lead block may be selected by the user before, after and/or during therapy. The user can select the lead unit from available individual parts or electrical components of the therapeutic device. Therefore, the user can select the main unit 11, the applicator 12, the remote control 13, the additional therapeutic device 14 or the communication device 15 as the master unit. The master unit may be a selected control unit present in a separate part of the therapeutic device, such as the control unit in the main unit 11. The user may select the master unit to facilitate adjustment of therapy parameters. The user may also select the communication device 15 as the master, whereby the communication device selected as the master may control more than one therapeutic device. The main unit 11 may contain a control unit as a master unit, monitoring and evaluating at least one therapy parameter, for example, the patient's temperature, the voltage on the individual elements of the therapeutic device, and/or other, which allows safe therapy even if the connection is between. Also, the drive unit may be an independent electrical element outside the human-machine interface. The head unit can be controlled by the user through a human-machine interface.

[125] Alternatively, the master unit may be automatically selected based on a predetermined priority value of the attached parts of the therapeutic device. The selected master unit may remain unchanged and a previously selected part of the therapeutic device may serve as the master unit throughout therapy. However, the selection of the master unit may be changed during therapy based on command priority and/or user selection. The master unit may also be defined according to the production configuration or it may be subject to a factory reset. For example, the remote controller 13 may issue a highest priority command to stop therapy when the patient feels discomfort, and therapy will be stopped regardless of which individual part of the therapy device has been selected as the master unit and regardless of the therapy parameters set.

[126] FIG. 2-5 depict several possible master-slave communication schemes that may be used for communication between the main unit 11 and one or more applicators 12, remote controls 13, additional therapy devices 14 and/or communication devices 15. According to FIG. 2, one or more therapeutic generators 201 generate a modified electrical signal to signal a therapeutic energy source, such as an RF electrode and/or a magnetic field generating device. Therapeutic generators 201 may comprise a group of electrical elements or at least two elements from a group of electrical elements present in the circuit of the therapeutic device and/or the main unit. An electrical group may include a control unit, a power supply, a coaxial cable system, one or more switches, one or more energy storage devices, one or more PIN diodes, one or more LC circuits, one or more LRC circuits, one or more amplifiers. power and/or other parts of the therapeutic device that actively modify the electrical signal in a controlled manner. The therapeutic generator may provide modification of the electrical signal in a controlled manner.

[127] Modifying the electrical signal in a controlled manner may include, for example, providing and/or controlling the adjustment of the impedance of the RF therapy provided based on the match of the impedances measured on the patient's tissue and/or the RF electrodes. An actively modified electrical signal can be interpreted as an electrical signal that can have different parameters, such as frequency, balancing, amplitude, voltage, phase, intensity, etc. The electrical signal parameters may be based on therapy requirements, including patient type and therapy parameters. In addition, electrical signal parameters can be modified based on feedback information, such as measured RF energy standing wave ratio, tissue temperature, RF electrode temperature, applicator core temperature, applicator surface temperature, electric current and voltage of individual elements of the therapeutic device and/or another.

[128] The schematic in FIG. 2 shows a security block 203 preventing any unauthorized access to therapeutic device communication and protecting personal data and/or user account. The security unit 203 may protect the therapeutic device from computer viruses, unauthorized access, and/or protect communication between individual parts of the therapeutic device from being read or modified by an unauthorized environment or person. The security unit 203 may provide communications encryption and/or anti-virus services to prevent unwanted binary code from being injected into the therapeutic device and/or communications. The security unit 203 can correct errors made during communication. The security unit 203 may block the unauthorized/unwanted external device from communicating with the therapeutic device.

[129] The security unit 203 shown in FIG. 2 may be in the communication diagram between the host 202 and the communication interface 204. The security unit 203 may also be part of the user element 208, the service center 207 and/or the vendor 206. The security unit 203 may also be located between the communication interface 204 and the communication environment 205, therapeutic generator 201 and/or may be part of them.

[130] The communication interface 204 may include hardware and/or software components that convert an electrical, electromagnetic, infrared, and/or other signal into a readable form to enable communication between at least two parts of the therapeutic device and/or other parties or communication media. Communication interface 204 may provide communication and/or encoding of information and/or data. The communication interface 204 may be, for example, a modem or a GSM module enabling communication between the therapeutic device and a computer network or server. Communication interface 204 may be part of a host 202, a therapeutic generator 201, and/or another part of a therapeutic device.

[131] The communication medium 205 may be a medium transmitting communication data. The communication medium 205 may be used in communication between the therapeutic device and the user 208, the service center 207 and/or the vendor 206. The communication medium 205 may be a wire, SD card, flash memory, coaxial cable, any conductive connection, a server, any type of network operating in accordance with regulations, such as RF waves, sound waves, optical waves, GSM, 3G, 4G, 5G, HUB switch, Bluetooth, Wi-Fi and / or other medium that may contain one or more servers.

[132] Communication data/information may be redirected to individual parts of the therapeutic device and/or individual users or services such as user 208, service center 207 and/or merchant 206. Communication data/information may be redirected by host 202, environment 205 communication and/or therapeutic generator 201. For example, the server may filter data for the user 208 and filter other communication information to be redirected to the service center 207, the control unit and/or another part of the therapeutic device.

[133] The element labeled "user 208" in FIG. 2 may be a user controlled HMI. Alternatively, the element labeled "user 208" in FIG. 2 may be another communication device (personal computer, laptop, mobile device, tablet, etc.) controlled by the user, wherein the communication device can send information to at least one part of the therapeutic device and/or receive information from at least one part of the therapeutic device. The information provided by this communication channel may be the type of therapy protocol, information about the therapeutic effect, the actual value and/or a predetermined value of one or more therapy parameters, feedback information, selection of the area of the body to be treated, recommendations for behavior before and after therapy and/or other information. At least some of the information may be sent to the user operating the therapeutic device as well as to the patient, for example, by a mobile phone, tablet or laptop software application.

[134] The service center 207 shown in FIG. 2 may be a service department that has authorized access to information about the therapeutic device. The service center 207 may be a service department of a company that provides or manufactures a therapeutic device, and communication between the company's service department and the user can be provided through an HMI, a communication device, and/or automatically through a pre-programmed software interface. The information provided by this communication link may include the wear and tear of an individual electrical element of the therapeutic device, the lifespan of any RF electrode and/or magnetic field generating device, failure of an individual electrical element, possible software optimization and/or updating of the device, provision of applications for attaching another additional therapeutic device, and/or others. Optimization and/or updating of the therapeutic device may include, for example, remote access to the software of the therapeutic device and/or error correction.

[135] Vendor 206 shown in FIG. 2 may be a sales department with authorized access to therapeutic device information. The merchant 206 may inform the user of the type of accessories that may be added to the therapeutic device. In addition, the merchant 206 may be a reseller for the sale of plug-ins and/or may be a reseller for the sale of accessories for the therapeutic device. In addition, the merchant 206 may provide an offer related to the payment and rental system. The information sent over the communication channel to or from the merchant 206 may be, for example, the number of treatments, the time of the treatments, and/or the type of therapy used, applicator information, and/or other information.

[136] The therapeutic device may include a recorder for storing data about therapy history, operation history, communications between individual parts of the therapeutic device, data from or to the payment and rental system, operation errors, and/or other information. The data may be available to the merchant 206, the service center 207, and/or the user 208 via a communication medium (eg, via a cloud storage and/or server). The therapeutic device may include a payment and rental system for managing bills for the use of the therapeutic device and/or associated additional therapeutic devices. The payment and rental system can send such information to the supplier in order to prepare an invoice. Data from the recorder can be downloaded by verified authorized personnel, such as a maintenance specialist, an accountant and/or another person with administrator rights. Verification of an authorized person can be provided with a special key, password, multi-bit program code and/or a special connecting cable.

[137] The payment and rental system may be based on credit funds deducted from the user's account. The credit funds may be predetermined by the therapeutic device supplier, eg, the therapeutic device manufacturer. Credit funds may be credited to an account when the therapeutic device is in use and/or may be credited to an online account associated with one or more therapeutic devices, the user and/or provider. Credit funds can be deducted according to the selected therapy protocol or area of the body. The credit cost of one or more therapies and/or part of the therapy may be displayed to the user before the start of the therapy, during the therapy, and/or after the therapy. If the user's account has run out of credit, the therapy device may prohibit any further therapy until the credit has been deposited. Credit funds can be used as a currency that varies for a particular therapy, and different therapies can cost different amounts in credit funds depending on the type of therapy, the duration of therapy, the number of applicators used and/or other factors. Credit funds may also be used to rent or purchase an individual part of the therapeutic device, the entire therapeutic device, hardware or software additions to the therapeutic device, and/or other consumable items and spare parts related to the therapeutic device. The interface where credits can be entered into the system may be part of a therapeutic device, an HMI, and/or may be available over the network via a web interface.

[138] One or more software add-ons (eg, software applications) may be associated with a therapeutic device and method of therapy. One or more software add-ons may be downloaded to any communication device, such as a smartphone, tablet, computer, and/or other electronic device. The plug-in may communicate with the main unit and/or other part of the therapeutic device. The plug-in communication device may be used to display or adjust one or more therapy parameters or therapy-related information. Such displayed therapy parameters and therapy-related information may include, for example, time since the start of therapy, the measured size of the area of the body treated before and/or after individual therapies, schematic representations of packages or sequences applied, time to end of therapy, frequency the patient's heart rate, the patient's body temperature, such as body surface temperature, the types of therapy provided, the type of therapy protocol, the comparison of the patient's body parameters with previous therapy (for example, percentage of body fat), and/or the actual therapeutic effect of the therapy (for example, muscle contraction or muscle relaxation). A plug-in may also be provided to patients to inform them about the schedule of therapies, note progress between individual therapies, the percentile of treatment outcomes compared to other individuals, and/or advice on behavior before and/or after therapy. Behavioral recommendations may include, for example, advice on how much water the patient should drink during the day, what the patient should eat, what type and amount of exercise the patient should do before and/or after therapy, and/or other information that may improve therapy results.

[139] Communication between individual elements of the communication scheme, such as therapeutic generator 201, master unit 202, security unit 203, communication interface 204, communication environment 205, user 208, service center 207 and/or merchant 206, may be bidirectional or multidirectional.

[140] Communication between user 208, service center 207, vendor 206, communication environment 205, and/or communication between therapeutic generator 201 and master unit 202 may be protected by security unit 203 to ensure secure communication and eliminate errors. Block 203 security may be between the host unit 202 and interface 204 communication and/or between the environment 205 communication and interface 204 communication.

[141] As shown in FIG. 3, another communication option for providing remote access between the user 208, the service center 207 and/or the vendor 206 and the therapeutic device may be provided by the server 301. The server 301 may include a security unit 203. The security block 203 may be implemented as individual access by a user 208, a service center 207, and/or a merchant 206.

[142] As shown in FIG. 4, communication environment 205 may communicate with one or more therapy generators 201. One or more therapy generators 201 may communicate with master 202. Information from communication environment 205 may be verified by security 203 before therapy generator 201 sends the information. to the lead block 202.

[143] FIG. 5 shows a schematic representation of communication between communication medium 205 and one or more therapy generators 201A-201D. Therapy generator A 201A can communicate with at least one or more therapy generators 201B-201D. Another therapy generator B 201B may also communicate with at least one or more therapy generators 201A, 201C, 201D. Therapy generator C 201C cannot communicate directly with therapy generator A 201A, but can communicate via therapy generator B 201B. Block 203 security may be in the communication channel between each therapeutic generator 201A-201D and/or between therapeutic generator 201A and the environment 205 communication.

[144] FIG. 6 shows the main unit 11 of the therapeutic device. The main unit 11 may include an HMI 61, a ventilation mesh 62, at least one of the applicator holders 63a and 63b, at least one device control element 64, applicator connectors 65a and 65b, at least one main input 66 for supplying electricity, curved casing 67 of main unit 11, wheels 68, opening 69 in main unit casing, main unit handle 70 and/or logo area 71. The main input 66 for supplying electricity may provide contact or connection to the power system or power supply network.

[145] The ventilation mesh 62 of the therapeutic device may be designed as a single piece and/or may be divided into multiple ventilation meshes 62 to provide heat dissipation. Ventilation mesh 62 may face the person operating the main unit 11, may face the floor and be invisible, and/or the ventilation mesh 62 may be on the sides of the main unit 11. A ventilation mesh facing the floor may be used to minimize noise, disturbing patient, since processes such as cooling of the main unit 11 and/or electrical components powered by electricity may generate noise. The surface area of all ventilation meshes 62 on the surface of the main unit 11 may range from 100 cm ² to 15000 cm ² , or from 200 cm ² to 1000 cm ² , or from 300 cm ² to 800 cm ² .

[146] Manipulation with the main unit 11 can be carried out using the rotating wheels 68 on the bottom of the main unit 11 and/or using the handle 70 of the main unit. The area 71 for the logo of the company providing the therapeutic device may be located under the handle 70 of the main unit and/or anywhere on the curved casing 67 and HMI 61.

[147] As shown in FIG. 6, the front side of the main unit 11 facing the patient may be designed as a curved casing 67 of the main unit. The front side of the main unit 11 facing the patient may not have right angles according to the horizontal projection of the main unit 11. The front side of the main unit 11 facing the patient may be designed in the form of one, two or more parts covering the interior of the main unit 11 The main unit 11 with a curved front side can improve the handling of the main unit 11 itself near the patient support, while minimizing the risk of collision between the main unit 11 and various sensitive parts of the patient's body (such as fingers). The front side of the main unit 11 may also include an opening 69 in the main unit casing. Opening 69 in the housing of the main unit may include a thermal imaging camera to monitor the temperature of the patient or body area being treated, a camera to track the location of one or more applicators, the movement of the patient, and/or the like. The opening 69 in the main unit casing may be an opening in the curved main unit casing 67 . The opening 69 in the housing of the main unit may contain one or more connecting elements for attaching additional therapeutic devices. In addition, the opening 69 in the housing of the main unit may contain one or more sensors, for example, a camera, an infrared sensor for scanning the movement of the patient, heating the area of the body undergoing therapy, and/or biological structure. Based on information obtained from such sensors, the actual value and/or a predetermined value of one or more therapy parameters can be optimized as the patient moves, the skin surface temperature reaches a threshold, the area of the body being treated is determined, and/or the like. The front side of the main block 11 may also include one or more applicator connectors 65a and/or 65b.

[148] Patient-facing applicator connectors 65a and 65b may be closer to the patient's body than applicators attached to the side facing the operator (eg, physician or maintenance technician). Accordingly, the length of the connecting tube 814 connecting the applicator to the main unit 11 can be minimized. Handling an applicator and/or multiple applicators connected via shorter connecting tubes 814 may be easier than handling an applicator connected using a longer connecting tube 814. The front side of the main unit 11 may not have corners and/or geometric corners. and may have at least partially elliptical and/or circular curvature. The curvature may have a radius of curvature in the range of 20 cm to 150 cm, 30 cm to 100 cm, 30 cm to 70 cm, or 40 cm to 60 cm. 200°, or 50° to 180°, or 90° to 180°. The angle of curvature can be determined in the same way as the angle 30 of section 26 in FIG. 23, as described in more detail below.

[149] The main unit 11 may include one or more applicator holders, such as 63a and 63b. Alternatively, one or more applicator holders may be attached to the main unit 11. Each applicator holder 63a and 63b may be specific to a different applicator type. Each applicator holder 63a and 63b can hold one applicator 12a or 12b. Each applicator holder 63a and 63b can have multiple functions. For example, applicator holders 63a and 63b can be used to preheat or precool at least a portion of the applicator. In addition, the applicator holders 63a and 63b may contain another HMI and be used to display information about the selected therapy, the actual value, and/or the predetermined value of one or more therapy parameters. Also, the applicator holder 63a and/or 63b can signal that the applicator is ready for use. In addition, the applicator holder 63a and/or 63b may indicate the current temperature of at least a portion of the applicator. An indication can be given by flashing a color indicator or by vibrating. The applicator holder 63a and/or 63b can be used to set an actual value and/or a predetermined value of one or more therapy parameters and/or applicator parameters, such as the temperature of the part of the applicator in contact with the patient.

[150] The main unit 11 may include a device control 64 for turning the main unit 11 on and off, manually setting the power supply settings, and/or other functions. The applicator connectors 65a and 65b can be used to transmit an electrical and/or electromagnetic signal from the main unit 11 and the applicators. The applicator connectors 65a and 65b can be used to connect one or more applicators (via connector tube 814), a communication device, an additional therapeutic device, and/or storage devices, such as a USB interface device, an SSD drive, diagnostic devices, and/or other data storage devices known in the art. Applicator connectors 65 (for example, 65a and/or 65b) for connecting one, two or more applicators may be located in the main unit 11 or on the side of the main unit 11. The length of the coaxial cables may be related to the frequency of the transmitted electrical signal. To allow easier handling of one or more applicators 12a and/or 12b, the length of the connection from the main unit 11 to, for example, the applicator 12a (and hence the connecting tube 814) should be as long as possible. However, the length of the at least one coaxial cable between the electrical elements in the main unit 11 may be related to the frequency of the transmitted electrical signal (eg, RF signal) sent to at least the therapeutic energy source (eg, RF electrode to provide RF energy). Therefore, the length of at least one coaxial cable within the main unit (eg between the power supply and the applicator connector 65a and/or 65b) can be as short as possible. The length of the coaxial cable contained in the main unit 11 may range from 3 cm to 40 cm, or from 7 cm to 30 cm, or from 10 cm to 20 cm. In order to optimize the handling of one or more applicators 12a or 12b attached to the main unit 11, the applicator connectors 65a and 65b may be on the curved front side of the main unit 11.

[151] HMI 61 may include a touch screen displaying the actual value and/or a predetermined value of one or more therapy parameters. The touch screen may provide a selection of displayed therapy parameters and/or the ability to adjust them. The HMI 61 can be divided into two display sections 61a and a selection section 61b. The display section 61a may display the actual value and/or predetermined value of one or more therapy parameters and other information to the user. The selection section 61b in the HMI 61 may be used to select therapy parameters and/or otherwise adjust therapy. The HMI may be contained, may be attached to, or may be part of one or more applicators 12, main unit 11, additional therapeutic device 14, and/or one or more other communication devices 15.

[152] The HMI may be contained in the main unit 11. The HMI may be fixed in a horizontal orientation to the main unit 11, or the HMI 61 may be oriented or tilted at an angle of 0° to 90° relative to the floor or other horizontal supporting surface. The angle between the HMI 61 plane and the floor can be adjusted by at least one swivel or can be rotated in at least one rectangular coordinate system. The HMI 61 may take the form of a detachable HMI, such as a tablet. The HMI 61 can be adjusted by telescopic movement and/or rotation according to one, two or three coordinates in a rectangular coordinate system using a holder that can adjust the distance between the HMI 61 and the main unit 11 and/or the orientation of the HMI 61 relative to the main unit 11 and the user. The holder may contain at least one, two or three realized hinge elements.

[153] One HMI 61 can be used for more than one type of therapeutic device provided by the supplier. The HMI software interface may be part of the main unit software or part of the software included in one or more additional therapeutic and/or communication devices. The software interface can be downloaded and/or updated by connecting to a communication device, additional therapy device, flash memory, remote connection to a vendor, service department and/or the Internet.

[154] FIG. 26 shows an exemplary layout of the interior of the main unit 11. The interior of the main unit 11 may contain a control system for several electrical components, one or more RF control circuits, magnetic circuits, and/or other elements necessary for the proper functioning of the therapeutic device. The location of the individual elements in the main block 11 can be described using a rectangular coordinate system with zero values at the bottom edge of the front side facing the patient. The main block 11 may comprise one or more struts 74. At least two struts 74 may form an X-shape, the ends of which may be attached to other vertical struts 74 to form the structure of the main block 11. The main block 11 may comprise at least one a cooling system 78 configured to cool an electrical element, such as one or more control units, printed circuit boards (PCBs), power supplies, switches, energy storage devices, and/or another electrical element of the therapeutic device. The cooling system 78 may be used to supply and/or cool the cooling fluid supplied to the applicator. SYM element 79 may be in the upper third of the Z coordinate and in the first third of the X coordinate, while the Y coordinate does not matter. The SYM function is explained below. The main unit 11 may also include one or more housings 72 made of aluminum or other metallic materials. One or more housings 72 may provide electrical, electromagnetic and/or radiation isolation (hereinafter referred to as simply insulation) of one or more internal parts of the main unit 11 from another part of the main unit 11. For example, at least a portion of the RF circuit 73 may be in the last third X and Z coordinates in one of the buildings. The power source 75 supplying power to at least a portion of the RF circuit and/or the magnetic circuit may be located in the last third of the X coordinate and in the first third of the Z coordinate. The power storage device 76 may be at least partially isolated from one or more RF circuits. When multiple magnetic circuits are used, the multiple magnetic circuits can be at least partially isolated from each other. To ensure a short length of the coaxial cable from the power storage device 76 to the applicator connector 65, as mentioned above, both elements (the energy storage device 76 and the connector 65, for example, 65a of the applicator) can be in the same half of the X coordinates. and Z, for example, in the first half of the X and Z coordinates. Other electrical elements of the magnetic circuit, depicted as rectangular block 77, may be in the first half of the X coordinate and the second third of the Z coordinate.

[155] FIG. 7 shows an exemplary display interface 700 of HMI 61. HMI 61 may display one or more applicator symbols 701. One or more applicator symbols 701 and their colors may indicate the quality of the connection, the number and/or type of applicators available or attached, additional therapeutic devices attached to the main unit 11 and/or involved in therapy. List 702 may redirect to a page or other display layout where a list of therapy protocols can be registered or configured. Therapy protocol list 702 may include one or more predefined values for one or more therapy parameters (e.g., magnetic field intensity, RF field intensity, magnetic unit pulse intensity, magnetic pulse intensity, pulse duration, packet duration, individual packet composition, pulse duty cycle). , envelope shape, therapy time, therapy components, threshold temperature of the biological structure during therapy, and/or other parameters). The list of therapy parameters may contain one or more stored therapy protocols optimized for individual patients or areas of the body. Once a therapy protocol has been selected, therapy parameters can be further optimized by the user. Also, therapy parameters can be adjusted by selecting additional patient parameters such as the patient's body type (e.g., very thin, skinny, average weight, overweight, or obese), or the patient's body mass index (BMI), gender, age group (e.g., under 30, 30-39, 40-49, 50-59, 60 and older). Also, therapy parameters can be further optimized by selecting only a portion of the therapy protocol.

[156] HMI 61 may contain one or more sliders, which may have multiple functions. For example, slider 703 can be used as a navigation element to select which interface page to use, such as list 702, therapy icon 704, or records 707. Also, slider 703 can be used to display the remaining time until the end of therapy.

[157] The therapy icon 704 may represent the interface shown in FIG. 7. Timer 705 may represent the duration of therapy, the remaining time until the end of therapy, and/or the time elapsed since the start of therapy. The "Protocol 1" icon 706 may represent the type or number of the protocol selected and/or currently in use or prepared for use. Records element 707 may redirect to another interface page with registered therapy history, information about patients treated, information about the payment and rental system, information about payments and/or cost of therapy in credit funds. Record element 707 may display how much credit is left in the credit account, how much credit has been spent, how long the therapeutic device has been used, and/or other billing information. The icon depicted by the "settings" symbol 708 may redirect the user to the settings of the therapeutic device, including, for example, adjusting the melody and/or the volume of the sound emitted by the device and/or the brightness of the screen. The sound produced by the therapeutic device and/or the brightness of the screen may differ before and/or during therapy. The "settings 708" interface may also allow changing the date, time, language, type and/or parameters of the connection between the main unit and the applicator, additional therapeutic device and/or communication device. The "settings 708" interface may contain icons for initiating calibration and scanning functionality of the therapeutic device and its attached parts. The settings 708 interface may provide software information, software history and/or software updates, a button to contact support and/or submit an error log, the type of operation mode (e.g., "basic" or "expert" with permitted additional settings of the therapeutic device), the ability to top up therapy credits, reset to factory settings, and/or other settings.

[158] Intensity signs 709 may be displayed in the form of a percentage, a number, a power, and/or other format. Signs 709 intensity can be adjacent to the icon, which can adjust the intensity of the source of therapeutic energy. Intensity signs 709 may be below the icon, above the icon, and/or in the icon (eg, as a number in the intensity bar 710) and/or other visualization that can adjust the intensity of the therapeutic energy source. Each intensity band 710 representing one source of delivered therapeutic energy (eg, RF field or magnetic field) may have its own intensity signs 709 . The therapeutic device may contain multiple applicators 714, for example, the first applicator A and the second applicator B may be connected to the main body of the therapeutic device. Thus, applicators A and B can be applied to different muscles in the same muscle group or pair of muscles, such as the left and right buttocks, the left and right sides of the abdomen, the left and right thighs, and other paired muscles or interacting muscles. The number of attached applicators and/or additional therapeutic devices providing therapeutic energy may be less than two or more than two.

[159] As shown in FIG. 7, each applicator may provide magnetotherapy 718 (the left side of the HMI, labeled HIFEM A and HIFEM B for the purposes of FIG. 7 and depicted in the exemplary HMI) and/or RF therapy 712 (the right side of the HMI, labeled RF A and RF B for the purposes of Fig. 7 and depicted in the exemplary HMI).

[160] The intensity of each RF field and/or magnetic field can be adjusted independently, for example, by scrolling a separate magnetic intensity scroll element 719 and/or RF intensity scroll element 711 across the intensity bands 710. One or more scroll elements or one or more intensity bars can move independently or can move together with another scroll element or intensity bar to adjust multiple magnetic fields at the same time, multiple RF fields at the same time and/or multiple RF and magnetic fields provided by one applicator at the same time . Also, one or more scroll elements or intensity bars can be adjusted independently or can be moved together with another scroll element or intensity bar to adjust multiple magnetic fields simultaneously, multiple RF fields simultaneously, and/or multiple RF and magnetic fields provided by two applicators simultaneously. One or more intensity bands 710 may differ in color and may be adjusted by intensity scroll element 719 or 711 and/or intensity buttons 720. The intensity buttons 720 can change (eg, increase or decrease) the intensity of the RF field and/or magnetic field by a fixed amount, such as 1%, or 2%, or 5%, or 10%, or in the range of 1% to 10 %, or in the range from 1% to 5% of the maximum possible field intensity. The intensity of the magnetic field and/or RF field can be adjusted independently for each source of therapeutic energy. Also, the intensity of the magnetic field and/or RF field can be adjusted by selecting and/or attaching one or more applicators, additional therapeutic devices, and/or therapeutic energy sources.

[161] The operation of one or more RF electrodes and/or magnetic field generating devices may be synchronized and may be controlled by one, two or more intensity scroll elements 719 and/or intensity buttons 720. Therapy can be started with the start button 713, which can automatically (eg, after starting therapy) change to a pause button. Therapy can be restarted and/or terminated using the stop button 716 during therapy. The interface may also show an indicator of a discomfort indication button 717 that can be activated by a patient via a remote control when therapy becomes uncomfortable. When the discomfort indication button 717 is activated, therapy can be automatically and immediately interrupted (eg, suspended or terminated). When the discomfort indicator button 717 is activated, the therapeutic device may provide a human-perceivable signal, including an acoustic warning, including an audible signal. In addition, the human-readable signal may include a visual warning, such as flashing a color indicator. Depending on the patient's discomfort, the user can adjust, for example, therapy parameters or therapy protocol, attachment or contact of the applicator. The interface may also include a soft power switch 715 for turning the therapeutic device on or off.

[162] As shown in FIG. 7, the HMI may contain two intensity bands (eg, 710) for RF therapy and two intensity bands for magnetic therapy. Additionally, the HMI may contain two intensity scrollbars (eg 711) for RF therapy and two intensity bars (eg 719) for magnetic therapy. In addition, the HMI can contain four intensity buttons for RF therapy and four intensity buttons (eg 720) for magnetic therapy. One intensity scroll element, one intensity bar and/or two intensity buttons can be provided per therapy circuit. Therefore, in FIG. 7 shows the HMI of a therapy device containing two circuits for RF therapy and two circuits for magnetic therapy.

[163] The therapeutic device may contain one or more applicators. The therapeutic device may contain two, three, four, five or more applicators. Each applicator may contain at least one, two or more different therapeutic energy sources, such as one or more RF electrodes providing RF therapy and one or more magnetic field generating devices providing magnetotherapy. For example, the first applicator may contain one RF electrode and one magnetic field generating device, and the second applicator may contain another RF electrode and another magnetic field generating device. One applicator can be connected to the main unit with one connecting tube. The connecting tubes of different applicators can be connected to each other or separated for each applicator. Alternatively, several applicators can be connected to the main unit with one common connecting tube. At least one therapy parameter of at least one applicator can be changed independently of one or more other applicators and/or additional therapeutic devices.

[164] One or more applicators, additional therapeutic devices and/or communication devices can be mechanically connected to the main unit using one or more wires and/or fluid channels. One or more wires and/or fluid conduits may extend within the connecting tube. One or more wires connected between the main unit and the applicator can be used to transmit an electrical signal (representing, for example, an RF signal) to an RF electrode located in the applicator to generate RF energy. One or more wires may be used to supply an electrical current to a magnetic field generating device located in the applicator to generate magnetic field pulses. The same wire and/or different wires connecting the applicator and the main unit 11 may be used for communication between the main unit 11 and the applicator 12 and/or for collecting feedback information. Feedback information may include, for example, measured signal parameters and/or impedimetric characteristics of the wire prior to therapy and/or during therapy. The fluid conduit between main unit 11 and applicator 12 may direct liquid, oil, water, vapour, gas and/or other temperature controlling cooling fluid.

[165] One or more applicators can be attached to the patient's body and/or body region using one or more belts, one or more belts, or by creating a vacuum under the applicator. Also, the applicator can be attached to the body area using a carrier matrix or using an adhesive layer located on at least part of the surface of the applicator and in contact with the patient's body or clothing. The applicator may be attached to a body region by pressing the applicator against the patient's body region or clothing using an adjustable mechanical positioning arm, wherein the applicator may be detachably attached to a positioning arm comprising at least one, two or more articulations. The belt may be at least partially elastic and may form a closed loop, for example, with Velcro fasteners (using Velcro fasteners), buckles, cufflinks and/or other fastening mechanisms that can be used to adjust the length. The belt may be attached to a region of the body and may include a fastening mechanism for attaching the applicator to the belt and/or to the patient's skin or clothing. Such a fastening mechanism may be, for example, a belt with applicator pockets. Attaching an applicator to a body region may include attaching or placing the applicator so that it is near or in contact with the body region. One or more applicators may be attached to the area of the body before or during the application of one or more types of therapy (eg, RF therapy or magnetotherapy). Also, the applicator can be attached to the body area, skin or clothing with a soft material cover that can be wrapped around the applicator and/or part of the body area. In addition, the applicator can be covered with a soft material cover providing other attachment points for belt attachment, soft material wrapping, or any other attachment option mentioned herein.

[166] The belt may be an adjustable length belt and may be at least partially flexible. One or more belts can attach or fix and/or attach one, two or more applicators to the patient's body or body region. The belt may be attached to one applicator 800, or one belt may attach two or more applicators to the patient's body. When multiple applicators (eg, two, three, or more) are used, one applicator may be attached to the patient's body region with one belt, and the other applicator may be attached to the body region with another belt. Alternatively, multiple applicators (eg, two, three, or more) may be attached to the patient's body region with the same belt. At least one applicator attached to the belt can be fixed relative to the patient's body during at least part of the therapy. The at least one applicator, attached by the belt to the patient's body, can be repositioned once or several times during therapy, either manually by the operator or automatically, to ensure optimal therapeutic effect and therapy comfort for the patient.

[167] Attaching the applicator and/or additional therapeutic device to the patient's body may include placing the applicator near the patient's body and/or region of the body. In case of connection near the body, the smallest distance between the applicator and the patient's skin can be from 0.01 cm to 10 cm, or from 0.01 cm to 5 cm, or from 0.01 cm to 2 cm, or from 0.01 cm up to 1 cm, or from 0.01 cm to 5 mm, or from 0.01 cm to 2 mm. However, the applicator can also be placed in direct contact with the patient's skin. In the case of direct contact, there may be no significant distance between the applicator and the patient's skin. When placed near or in direct contact, the intermediate material may be placed between the applicator and the skin, clothing, or body area of the patient. The intermediate material may be an air gap, a bolus, a carrier matrix, a belt piece, fabric, other clothing, a gel, a fluid-absorbing material, or a metal.

[168] FIG. 22 depicts an exemplary attachment of an applicator and/or additional therapeutic device 21 to a patient's body using a carrier matrix 22. The carrier matrix 22 of FIG. 22 may be in the form of a grid and/or a frame. The mesh and/or scaffold is at least partially flexible and is attached to the patient's body. The carrier matrix may be used to attach the applicator and/or additional therapeutic device 21 near the patient's body at a predetermined location, referred to as the applicator site 24, by means of a fastener 23. The carrier matrix may be a polymer scaffold, as in FIG. 22, a fabric/polymer sheet substrate, and the like. The fastening element may be one or more elements, for example, a locking mechanism, a hinge, a bayonet connection, a Velcro fastener, for attaching an applicator and/or an additional therapeutic device 21.

[169] As shown in FIG. 25, the applicator 800 may include one or more parts forming an applicator body, which can be connected to the main unit via a connecting tube 814. Also, the applicator can include one or more parts hidden in the applicator, further defining the function and functionality of the applicator. The applicator body may include various parts, for example, a handle housing 512, a handle 514, an upper housing 516, a second side portion 802 forming a lower applicator housing. The handle housing 512 may include an indicator 813 and/or an HMI 508, for example, to display and/or adjust the actual value and/or predetermined value of one or more therapy parameters. The handle 514 may be used to manipulate the applicator 800 and/or to attach the applicator 800 to a region of the patient's body. The top cover 516 may form the interior of the applicator. The top case 516 may include a vent 504 to allow air to pass into or out of the interior of the applicator to cool electrical components located within the interior of the applicator. Electrical elements located in the interior of the applicator may include, for example, an RF electrode, a device that generates a magnetic field, and/or a temperature sensor 510. The second side portion 802 forms the lower applicator housing. The second side portion 802 may include one or more projections, grooves, and/or other features. Power, energy, one or more electromagnetic signals, and/or a cooling fluid can be delivered to the applicator through the connecting tube 814. In addition, cooling of one or more electrically powered elements in the applicator (for example, a device 900 that generates a magnetic field, and/or substrate 113a with at least one RF electrode) may be provided by a fan 524 attached to the top casing 516 and/or second side portion 802. The RF electrode substrate 113a may include a temperature sensor 510 configured to sense the temperature in the applicator. , at least a portion of the lower casing 526, a region of the body and/or biological structure of the patient. The RF electrode located on the substrate can be connected to an interface 136 reconnecting the coaxial cables. Interface element 136 is further described with reference to FIG. 24. In FIG. 25 also shows a frame 506 that can be used to attach a magnetic field generating device to the top case 516 and/or to the second side portion 802. The frame 506 can be configured to eliminate noise and vibration during magnetic therapy.

[170] The applicator can be made as shown in illustrative figures 8a-8d. Applicator 800 shown in FIG. 8a-8d can be used for body area therapy.

[171] One or more RF electrodes may be located in the applicator 800 between the magnetic field generating device and the patient's body region. The RF electrode may be shaped at least in part to match the curvature of the first side portion 801, the second side portion 802, and/or the curvature of the patient's body region. The magnetic field generating device may at least partially match the curvature of the first side portion 801, the second side portion 802, and/or the curvature of the patient's body region. The RF electrode and/or the magnetic field generating device may be curved in order to focus and/or provide better targeting of the RF therapy and/or magnetotherapy. The first side portion 801 may be configured to maintain the position of the limb within the first side portion 801 during therapy. The first side portion 801 can provide stability and/or balance to the area of the body being treated. The position of the patient's limb can be maintained in the first side portion 801 even though the limb may move due to muscle contractions. Lateral movement and/or rotation of the limb may be restricted by the first side portion 801 and/or waist 817 so that the limb can be in a stable position. Rotation relative to the applicator 800 can be limited by attaching the applicator 800 to the area of the body, at least the portion of the limb being treated, with a belt. In addition, when part of the arm is subjected to magnetotherapy and/or RF therapy, at least part of the limb may also be attached to the patient's torso to minimize movement of the limb.

[172] The second side portion 802 may be on the opposite side of the applicator 800 relative to the first side portion 801. The second side portion 802 may be substantially flat, or the second side portion 802 may be at least partially concave and/or convex. The applicator 800 may be attached to the patient via a positioning mechanism, such as a belt 817, as shown in FIG. 8a and 8b.

[173] FIG. 8a shows an applicator comprising a positioning mechanism that can be secured in a recess 803 at the first end 804 of the first side portion 801 and in a recess 806 at the second end 805 of the first side portion 801. The positioning mechanism, such as a belt or belt, may be fastened, or its length can be adjusted by clip 807. Clip 807 can be moved around pin 808 in a clockwise or counterclockwise direction. Clamp 807 can be displaced by a spring. Alternatively, the clip 807 may be secured with a suitable locking mechanism or in any other manner that restricts movement. Clip 807 may include a fastener 809 on the underside of clip 807 to secure the correct length of the positioning mechanism. The fastener 809 may be a Velcro fastener, Velcro fastener, pin fastener, and other mechanical fasteners. Attaching the applicator 800 to the patient's body as described above can be used primarily when the patient's body region is attached to the first side portion 801 of the applicator 800. The shape of the RF electrode and/or the magnetic field generating device may at least partially correspond to the curvature of the first side portion. 801. The RF electrode and/or magnetic field generating device may be curved in order to focus and/or provide better targeting of RF therapy and/or magnetotherapy.

[174] FIG. 8b and 8c depict an applicator comprising a positioning mechanism that can be guided perpendicular to the curvature of the first side portion 801 and/or perpendicular to the axis 810 of the applicator. The positioning mechanism may be positioned or guided along the concave surface 815 and/or under, along or on the handle 812. The belt 817 may also be directed in any direction along and/or on the applicator 800 in order to attach the applicator 800 to the patient's skin. Attaching the applicator 800 to the patient's body as described above may be used primarily when the patient's body region is attached to the second side portion 802 of the applicator 800. The shape of the RF electrode and/or magnetic field generating device may at least partially correspond to the first side portion 801 The RF electrode and/or magnetic field generating device may be flat or curved in order to focus and/or provide better targeting of RF therapy and/or magnetotherapy.

[175] FIG. 8b is a plan view of the applicator 800. The applicator 800 may include an indicator 813 corresponding to the location of the magnetic field generating device within the applicator 800. The indicator 813 may be above the center of the magnetic field generating device. The indicator 813 can provide easy and convenient positioning of the applicator 800 by the user. A depression in the surface of applicator 800 can be used as indicator 813. Alternatively, indicator 813 can be another modification to the surface of the applicator case portion, such as a different color, a different roughness, the presence of one or more light sources (e.g., an LED), a certain curvature of the applicator body , the logo of the manufacturer or distributor and / or other. The applicator body may have at least two colors. The first color may be on the applicator body above the magnetic field generating device to ensure correct positioning of the applicator, and the rest of the applicator may have a second color different from the first color. Color can be interpreted as paint that reflects and/or absorbs light waves of a specific wavelength. Like indicator 813, the applicator may include a second indicator to display the location of at least one RF electrode.

[176] As shown in FIG. 8b and 8c, the applicator may include an outlet 811. The outlet 811 may circulate air in the applicator 800 and dissipate heat generated by one or more magnetic field generating devices and/or RF electrodes located in the applicator and receiving energy one or more more wires within the connecting tube 814. The connecting tube 814 may also contain a fluid channel that can supply or direct cooling fluid from the main unit 11 to the applicator 800.

[177] The applicator 800 may further comprise one or more temperature sensors 816, as depicted, for example, in FIG. 8c. The temperature sensor 816 may protrude from the body of the applicator 800, for example, from the surface of the second side portion 802 and/or from the first side portion 801. The temperature sensor 816 may protrude from the body of the applicator 800 in order to apply more pressure to the part of the body area being treated, applicator 800 and provide a better temperature measurement in the biological structure of the body area and/or on the patient's body.

[178] The second side portion 802 and/or the first side portion 801 may be heated and/or cooled. Heating of the second side portion 802 and/or the first side portion 801 may be used, for example, at the start of therapy to reach the therapy temperature more quickly. The temperature of the therapy may include the temperature of a region of the body and/or a biological structure elevated by the application of RF waves, which may be suitable for the application of a magnetic field. Cooling or heating parts of the applicator can be used to maintain a constant temperature on the patient's skin. Also, cooling or heating with applicator parts can be used to achieve higher therapy temperatures in the patient's biological structure more than 0.5 cm below the patient's skin. The cooling portion of the applicator in contact with the patient (eg, the second side portion 802 and/or the first side portion 801 of the applicator) can be used to minimize patient perspiration. The patient's skin may be cooled by a cooling fluid (eg, air) flowing and/or pumped from the applicator and/or other part of the therapeutic device. Cooling of the patient's skin may be provided by thermal diffusion between the cooled portion of the applicator in contact with the patient's skin and the patient's skin. The cooled portion of the applicator may be cooled by a cooling fluid flowing within the applicator and/or a Peltier element using the Peltier effect.

[179] Patient sweating may be uncomfortable for the patient and may adversely affect the collection of feedback information, contact the applicator and the patient's skin, and/or impair the adhesion of the applicator to the patient's skin. Cooling of the contact area of the applicator (eg, first side portion 801 and/or second side portion 802) may be used to prevent sweating of the patient's skin. Second side portion 802 and/or first side portion 801 may include grooves 819 into which cooling fluid may be supplied through applicator openings 820 where liquid and/or gas (e.g., air, oil, or water) may flow, as shown in FIG. . 8d. The first side portion or the second side portion of the applicator may include applicator lumens or applicator openings 820 where air from the applicator 800 may be directed to remove heat, moisture and/or sweat from the patient's skin. Lumens or holes may be located in the grooves 819. The lumen may be used to deliver the active agent to the patient. The contact portion of the applicator that is in contact with the body region may comprise a fluid absorbing material, such as a sponge, hydrophilic material, non-woven organic and/or polymeric textile, which may at least partially remove sweat from the patient's skin and/or improve conductivity between by the patient and the applicator 800. Reducing sweating of the patient in at least a portion of the area of the body undergoing therapy can be achieved by reducing the activity of the sweat glands. Sweat gland activity can be reduced by applying a pulsed magnetic field, intense light, heat shock provided by intermittent hypothermia to the patient's skin, by applying an active agent such as glycopyrronium tosylate to and/or the patient and/or other mechanisms.

[180] FIG. 23 shows an exemplary applicator containing a concave surface. The applicator may be designed such that the first side portion 801 is at least partially convex. Alternatively, the first side portion 801 may be V-shaped or U-shaped. The radius of curvature may correspond to the size of the patient's limb. Alternatively or additionally, the second side portion 802 may be at least partially convex.

[181] The patient may be in a supine position or seated on a patient support surface such as a bed, couch, or chair. The patient's hand may be placed on the first side portion 801 of the applicator 800. The first side portion 801 may be in direct contact with the patient, and RF therapy may be applied in combination with magnetotherapy. Also, a belt or belt may be guided through the concave surface 815 to attach the applicator to the patient's body.

[182] The first side portion 801 may be at least partially elliptical or circular in vertical section, with the overall curvature 25 of FIG. 23 may be defined as part of an ellipse or circle inscribed in the curvature of at least a portion of the first side portion 801. The section where the curvature of the first side portion 801 corresponds to the inscribed ellipse or circle may be referred to as section 26. Section 26 is defined as the angle 30 between line 28 and line 29. Line 28 and line 29 intersect the center of symmetry 27 and points 31 and 32 lying in section 26 with the greatest distance according to the inscribed part of the ellipse or circle, copying the curvature of the applicator 800. The center of symmetry 27 is the center of the inscribed ellipse and/or inscribed circle . The angle 30 forming section 26 of the first side portion 801 may be at least 5° or be in the range of 10° to 270°, 30° to 235°, 45° to 180°, or 60° to 135°. The radius of curvature of at least part of the circle inscribed in the first side portion 801 may be in the range of 50 mm to 1250 mm, or in the range of 10 mm to 750 mm, or in the range of 50 mm to 500 mm, or in the range of 60 mm to 250 mm. The second side portion 802 may be curved over at least a portion of its surface, wherein the section 26 of the second side portion 802 may have an angle of at least 5° or in the range of 10° to 270°, 30° to 235°, from 45° to 180° or 60° to 135°. In addition, the radius of curvature of at least part of the circle inscribed in the second side portion 802 may be in the range of 50 mm to 1250 mm, 10 mm to 750 mm, 50 mm to 500 mm, or 60 mm to 250 mm.

[183] One or more applicators and/or additional therapeutic devices may comprise a bolus 32, as depicted, for example, in FIG. 23. Bolus 32 may refer to a layer of material that is located between the applicator or RF electrode located on the surface of the applicator and the body area or skin of the patient (including the epidermis of the patient's skin or clothing). Bolus 32 may refer to a layer of material that is located between the RF electrode located on the surface of the applicator and the body area or skin of the patient. Bolus 32 may also be a portion independent of applicator 800. Bolus 32 may be attached to first side portion 801 and/or second side portion 802 of applicator 800. Bolus 32 may be removable and detachable from applicator 800. Bolus 32 may be attached to the first side portion 801 and/or to the second side portion 802 of the applicator 800. The bolus 32 may be made of a rigid or flexible material, and/or a composition of rigid and flexible materials may be used as the bolus. The bolus 32 may include a fluid, such as water, gels, or a fluid solution containing ceramic, metal, polymer, and/or other particles, enclosed in a flexible capsule made of a biocompatible material. The bolus 32 may be shaped, while the bolus 32 as a layer between the RF electrode and the patient's skin may have different thicknesses. The thickness of the bolus 32 may be greater in an area where the energy flux density of the RF therapy (including the RF field) would be high enough to create uncomfortable heat spots and/or non-uniform temperature distribution. Bolus 32 provides more uniform heating of the biological structure and minimizes edge effects. Edge effects can also be minimized by different bolus dielectric properties across bolus volume and/or bolus area. The bolus 32 may have a greater thickness under at least a portion of the edge of the RF electrode. The thickness of the bolus under at least part of the edge of the RF electrode may be at least 5%, 10%, 15%, or 20% greater than the thickness of the bolus 32 under at least part of the center of the RF electrode, excluding holes, notches and/or ledges. The bolus 32 may be thick under at least a portion of the bipolar RF electrode and/or under at least a portion of the distance between the at least two bipolar RF electrodes. In such areas, the thickness of the bolus 32 may be at least 5%, 10%, 15%, or 20% greater than the thickness of the bolus 32, where the distance between the two closest points of two different bipolar RF electrodes is greater than at least 5%, 10%, 15%, or 20%. Bolus 32 can also improve the transfer of therapeutic energy (eg, magnetic field and/or RF field) to at least one biological structure and minimize energy reflection by providing a gradual transition in dielectric properties between two different applicator and biological structure interfaces. Bolus 32 may profile or focus the RF field and/or magnetic field to improve the effect of therapy and/or provide deeper tissue penetration of the therapy.

[184] The bolus 32 can also be a fluid-absorbing material, such as a foam, textile, or gel material, to provide better fluid conduction between the applicator and the patient's body. Better conductivity of the contacting portion of the applicator may be useful for better RF signal adjustment of the RF therapy applied to the patient's body and/or for better collection of feedback information. Bolus 32 can mediate conductive contact between the RF electrode and the patient's skin or body area. Bolus 32 can also serve as a non-conductive or dielectric material that modifies the transfer of energy to the patient's body, provides cooling to the patient's skin, removes sweat from the patient's skin, and/or provides heating, such as capacitive heating of the patient's body. The fluid-absorbing material serving as bolus 32 can also provide better thermal conductivity, whereby the temperature of the biological structure and/or applicator can be adjusted faster, easier, and more accurately. Bolus 32 may also contain an additional RF electrode to provide RF therapy.

[185] As previously mentioned, a therapeutic device may comprise one, two, three, four, six or more applicators and/or additional therapeutic devices providing magnetotherapy and/or RF therapy. Each applicator, accessory therapeutic device, and/or therapeutic energy source (e.g., magnetic field generating device and/or RF electrode) may have its own therapy circuit dedicated to delivering energy, with each parameter of therapeutic energy provided in each therapy circuit can be independently controlled by the control system. Each applicator, therapeutic device, or therapeutic energy source can be independently controlled to provide therapy and/or two or more applicators, therapeutic energy sources, and/or additional therapeutic devices can be controlled as a group and can be controlled simultaneously, synchronously, and/or can interact with each other. friend.

[186] When the therapeutic device contains two or more applicators, they can be attached so as to be in contact with different parts of the body or located near them. In one example, the first applicator may be attached so as to contact or be located near the left buttock, and the second applicator may be attached so as to contact or be located near the right buttock. In another example, the first applicator may be attached so as to contact or be located near the left side of the abdomen, and the second applicator may be attached so as to contact or be located near the right side of the abdominal region. In yet another example, the first applicator may be attached so as to contact or be located near the left thigh, and the second applicator may be attached so as to be in contact with or be located near the right thigh. In one example, the first applicator may be attached so as to contact or be located near the left shin, and the second applicator may be attached so as to contact or be located near the right shin. Multiple applicators may be useful for therapy of interacting muscles and/or a pair of muscles.

[187] One or more applicators and/or additional therapeutic devices may include a magnetic field generating device (eg, a magnetic coil) that generates a magnetic field for magnetotherapy. A magnetic field generating device can generate an RF field for RF therapy. The bottom line is that the generated frequencies of the electromagnetic field have very different values. The magnetic field generating device can create a predominant magnetic field vector for magnetotherapy throughout the lower frequencies of the generated electromagnetic field. However, the magnetic field generating device can produce a dominant magnetic field vector for magnetotherapy over higher frequencies of the electromagnetic field that can be used for RF therapy. The magnetic field generating device in the high frequency electromagnetic field can provide an RF field similar to the RF field provided by an RF electrode. When a single magnetic field generating device is used to provide both RF therapy and magnetotherapy, the difference between the frequencies for generating RF therapy and magnetotherapy can be in the range of 500 kHz to 5 GHz, or 500 kHz to 2.5 GHz, or 400 kHz to 800 kHz or 2 GHz to 2.5 GHz. Also, when a single magnetic field generating device is used to provide both RF therapy and magnetotherapy, the frequencies for RF therapy may correspond to frequencies in the range of 100 kHz to 3 GHz, 400 kHz to 900 MHz, or 500 kHz to 3 GHz.

[188] One or more applicators and / or additional therapeutic devices may contain one or more RF electrodes and one or more devices that generate a magnetic field, and the RF electrodes have characteristics, structure and / or design that differ from those of the device that generates a magnetic field. field. The RF electrode can operate as a single pole electrode, a monopolar electrode, a bipolar electrode, and/or a multipole electrode. One or more RF electrodes can be used for capacitive and/or inductive heating of a biological structure or region of the body.

[189] The applicator may contain two bipolar RF electrodes. The bipolar electrodes can transmit an RF field between two bipolar RF electrodes located in at least one applicator. Bipolar electrodes can improve the safety and targeting of delivered RF therapy compared to monopolar electrodes. The bipolar electrodes can provide an electromagnetic field passing through the tissue of the patient and around and between the RF electrodes, and due to impedance matching, the formation of standing electromagnetic waves in the patient's tissue can be prevented and unwanted thermal damage to non-target tissue can be prevented. Also, the distance between the bipolar electrodes affects the depth of penetration of RF waves, providing improved targeting of RF therapy.

[190] The applicator may comprise a monopolar RF electrode or multiple monopolar electrodes. Monopolar electrodes can transmit RF energy between the active electrode and the passive electrode, where the active electrode can be part of the applicator and the passive electrode having a large surface area can be at least 5 cm, 10 cm or 20 cm away from the applicator. The grounded electrode can be used as a passive electrode. The grounded electrode may be on the opposite side of the patient's body from the attached applicator.

[191] Magnetotherapy can be provided by a magnetic field generating device made of a conductive material such as a metal, including, for example, copper. The device that generates the magnetic field can be made in the form of a coil, which can have different sizes and shapes. The magnetic field generating device may be a coil with multiple windings, where one turn of the coil may contain one or more wires. An individual turn of one or more wires may be isolated from other turns or turns of one or more wires. In relation to a magnetic coil, each turn of wiring can be called a turn. In addition, individual wires in one turn or turn can be insulated from each other. The shape of the magnetic field generating device can be optimized for the size and design of the applicator. The coil winding may conform to the shape of at least a portion of the applicator according to a plan view of the applicator. The coil winding may be at least partially round, oval and/or may have any other shape corresponding to the shape of the applicator or part thereof. The windings may be placed on top of each other, may be placed side by side, or the arrangement of turns may be a combination of side by side and on top of other windings. The coil may be flat.

[192] FIG. 9 is a plan view of an exemplary circular planar magnetic field generating device 900. The magnetic field generating device 900 may be characterized by dimensions including an outer diameter D, an inner diameter d, an inner radius r, and an outer radius R. The magnetic field generating device 900 may further be characterized by areas A1 and A2. The area A2 may represent the area of the coil winding and the area A1 may represent the magnetic core or the area without the magnetic core or windings.

[193] The area A1 is related to the dimensions r and d. Area A1 may not contain coil windings and may be filled with air, oil, polymer material. The area A1 may represent a magnetic core, and the magnetic core may be an air core. Alternatively, the magnetic core may be a permeable material having a high field saturation, such as a hard soft iron core, iron alloys, clad transformer steel, silicon alloys, enameled metal, permendur, permalloy, powdered metals or ceramics, and/or other materials.

[194] The area A2 is related to the dimensions of outer radius R and outer diameter D.

[195] The size of the inner radius r can be from 1% to 90% of the size of the outer radius R, or from 2% to 80%, or from 3% to 60%, or from 4% to 50%, or from 8% to 30%, or 20% to 40%, or 30% to 50% of the size of the outer radius R. The dimensions of the inner radius r and the outer radius R can be used to obtain a convenient shape of the generated magnetic field.

[196] The outer diameter D of the magnetic device may be 30 mm to 250 mm, or 40 mm to 150 mm, or 50 mm to 135 mm, or 90 mm to 125 mm, and the size of the inner radius r may be 1 % to 70%, or 1% to 50%, or 30% to 50%, or 5% to 25%, or 8% to 16% of the size of the outer radius R. For example, the size of the outer radius R may be 50 mm and the dimension r can be 5 mm. Area A1 may be omitted and the magnetic field generating device may contain only area A2 with coil winding.

[197] As described, the area A2 may contain several windings. One winding may contain one or more wires. The windings may be placed side by side and one winding may be in contact with an adjacent winding to provide a magnetic field with a high magnetic flux density. The winding area A2 may be from 4 ^cm2 to 790 ^cm2 , or from 15 ^cm2 to 600 ^cm2 , or from 45 ^cm2 to 450 ^cm2 , or from 80 ^cm2 to 300 ^cm2 , or from 80 ^cm2 to 150 cm ² , or from 80 cm ² to 130 cm ² .

[198] Alternatively, the windings may include a gap between each winding. The gap can be from 0.01% to 50%, or from 0.1% to 25%, or from 0.1% to 10%, or from 0.1% to 5%, or from 0.001% to 1% of the size R-r. Such a structure can facilitate cooling and insulating individual windings of the magnetic field generating device. In addition, the shape of the generated magnetic field can be modified by such a structure of the magnetic field generating device.

[199] The coil winding wire may have a different cross-sectional area. The cross-sectional area of the winding wire can be larger in the center of the winding, where the radius of the coil winding is smaller. Such wire cross-sectional area can be 2%-50%, 5%-30% or 10%-20% larger than the cross-sectional area of the same wire measured on the outer winding of the device that generates the magnetic field, where the radius of the coil winding is larger. The cross-sectional area of the winding wire of the magnetic field generating device may be larger on the outer turn of the winding of the magnetic field generating device, where the radius of the coil winding is larger. Such wire cross-sectional area can be 2%-50%, 5%-30% or 10%-20% larger than the cross-sectional area of the same wire measured on the inner winding of the device that generates the magnetic field, where the radius of the coil winding is smaller.

[200] The principles and parameters described above can be used to modify the shape of the magnetic field applied to the patient's body, provide more uniform and/or targeted muscle stimulation (e.g., muscle contraction), reduce expansion of the magnetic field generating device during therapy and/or increasing the service life of the magnetic field generating device. The magnetic field generating device may expand and contract during generation of the time-varying magnetic field, and this may damage the magnetic field generating device. Different cross-sectional areas of the conductive material used (eg, wire or metal strip forming the winding of the magnetic field generating device) can minimize the destructive effect of expansion and contraction of the magnetic field generating device.

[201] As described above, the cross-sectional area of the conductive material used (e.g., wire and/or metal strip forming the winding of a magnetic field generating device) can vary in different individual turns of wire by between 2% and 50%, or between 5 % to 30%, or 10% to 20% to improve the focus of the magnetic therapy provided, to increase the life of the magnetic field generating device, to minimize heating of the magnetic field generating device, and/or for other purposes.

[202] In addition, the placement of winding turns on top of each other and/or the insulation and/or expansion layer between the individual conductive windings of the magnetic field generating device may not be constant and may differ depending on the cross-sectional area, the radius of the winding required the form of the magnetic field provided and/or other parameters.

[203] The thickness 901 of the magnetic field generating device 900 shown in FIG. 9b may be 0.3 cm to 6 cm, or 0.5 cm to 5 cm, or 1 cm to 3 cm in the side view of the applicator.

[204] The total surface of the device generating the magnetic field, according to the horizontal projection of the applicator, i. e. area A1+A2 may be from 5 cm ² to 800 cm ² , from 10 cm ² to 400 cm ² , from 20 cm ² to 300 cm ² or from 50 cm ² to 150 cm ² .

[205] The ratio of the area A1 to the area A2 of the winding may range from 0.01 to 0.8, or from 0.02 to 0.5, or from 0.1 to 0.3 according to the plan of the applicator. The ratio between the winding area A2 of the device generating the magnetic field and the area RF of the electrodes in the same applicator, according to the horizontal projection of the applicator, can be in the range from 0.01 to 4, or from 0.5 to 3, or from 0.5 up to 2, or from 0.3 to 1, or from 0.2 to 0.5, or from 0.6 to 1.7, or from 0.8 to 1.5, or from 0.9 to 1.2 .

[206] FIG. 10a-10g depict the location of one or more RF electrodes 101 relative to at least one magnetic field generating device 900 in applicator 800. The location of the RF electrodes 101, 102 and/or magnetic field generating device 900 can have a critical effect on efficiency and targeting sources of therapeutic energy. RF electrodes and a device that generates a magnetic field may be inside the applicator.

[207] One or more RF electrodes 101, 102 may be within the applicator 800 as shown in FIG. 10a, 10b, 10d, 10e, 10f, 10g, and/or outside of applicator 800 as shown in FIG. 10c.

[208] As shown in FIG. 10a-10e and 10g, at least one RF electrode may be at least partially overlapped by an area A2 or A1 of at least one magnetic field generating device according to a plan view of the applicator. Such placement can provide the best synergistic effect of magnetic therapy and RF therapy, improve tissue heating uniformity of RF therapy, improve targeting of magnetic therapy and RF therapy, and minimize health risks.

[209] FIG. 10a is a side view of an applicator containing at least one RF electrode and a magnetic field generating device. The illustrated applicator may include at least one RF electrode 101 which may be positioned below the magnetic field generating device 900 in the applicator 800. FIG. 10b is a plan view of the same type of applicator containing an RF electrode and a magnetic field generating device. As shown in FIG. 10a and 10b, at least one RF electrode 101 may be very thin in order to reduce unwanted physical effects caused by the time-varying magnetic field. In FIG. 10b shows that at least one RF electrode 101 can be almost completely covered by the magnetic field generating device 900.

[210] FIG. 10c depicts another exemplary applicator containing at least one RF electrode and a magnetic field generating device. According to FIG. 10c, at least one RF electrode 101 may be outside the applicator 800, such as on or adjacent to the outer surface of the applicator 800. The RF electrode on the outside of the applicator may be better isolated from the magnetic field generating device and/or from other conductive elements emitting an electromagnetic field from the applicator. The improved isolation can reduce the impact of undesirable physical effects induced in at least one RF electrode 101 by a radiated electromagnetic field and/or a time-varying magnetic field. One or more RF electrodes 101 located on the outside of the applicator, as shown in FIG. 10c can also have improved contact with the patient's body, and thus the tuning operation of the electrical element of the RF circuit can be improved. In addition, the delivery of RF therapy to at least one target biological structure of the patient can be improved.

[211] FIG. 10d shows another illustrative applicator containing at least one RF electrode and a magnetic field generating device. At least one RF electrode 101 may be located below the magnetic field generating device 900. The applicator 800 may also include at least one other RF electrode 102 located above the magnetic field generating device 900, wherein both the RF electrode and the magnetic field generating device may be located in the same applicator 800. The first side portion 801 containing at least one curved RF electrode 102 near or on its surface may be used to treat a curved area of the body (eg, at least part of the thighs, hips, neck, and/or arms). The second side portion 802 with at least one flat RF electrode 101 near or on its surface can be used to treat an area of the body where a flat or nearly flat side of the applicator would be more appropriate, such as the abdomen or buttocks.

[212] FIG. 10e is a front view of an applicator 800 similar to that shown in FIG. 10d. In FIG. 10e shows that the RF electrode 101 may actually be two electrodes 101a and 101b. The electrodes 101a and 101b may be bipolar electrodes. Therefore, the applicator may include two bipolar electrodes 101a and 101b below the magnetic field generating device 900.

[213] FIG. 10f shows another exemplary applicator 800 containing an RF electrode and a magnetic field generating device. The applicator may include one or more RF electrodes 101 that minimally overlap or do not overlap at least one magnetic field generating device 900 according to a plan view of the applicator. The applicator may include two RF electrodes 101 that minimally overlap or do not overlap the magnetic field generating device.

[214] FIG. 10g shows another exemplary applicator 800 containing an RF electrode and a magnetic field generating device. The applicator may include at least one RF electrode 101 which may be positioned over the magnetic field generating device 900. The heating provided by the RF electrode positioned above the magnetic field generating device can also be provided to the magnetic field generating device itself.

[215] One or more RF electrodes located on one applicator and/or multiple applicators 800 can be placed in contact with the patient. Also, one or more RF electrodes and/or applicators may be separated from the patient by an air gap, bolus, dielectric material, insulating material, gel, and/or other material.

[216] One or more RF electrodes 101, 102 and/or magnetic field generating devices 900 in one applicator may be separated from each other by an air gap, circuit board material, insulator, cooling fluid, and/or other material. The distance between the nearest conductive part of the device generating the magnetic field and the nearest RF electrode can be from 0.1 mm to 100 mm, or from 0.5 mm to 50 mm, or from 1 mm to 50 mm, or from 2 mm to 30 mm, or from 0.5 mm to 15 mm, or from 0.5 mm to 5 mm. The spacing between the magnetic field generating device and the RF electrode can also be provided in the form of an insulating barrier separating the RF circuit from the magnetic circuit and preventing one therapy circuit or one therapeutic energy source from interfering with another therapy circuit or another therapeutic energy source. A device that generates a magnetic field located closer to the patient's body can provide stimulation and provide a therapeutic effect to at least a portion of at least one target biological structure more efficiently and deeper than a device that generates a magnetic field located at a greater distance from the patient's body.

[217] The magnetic field generating device and/or one or more RF electrodes located in or on the applicator may be cooled during therapy. Cooling of the magnetic field generating device and/or one or more RF electrodes may be provided by the Peltier element and/or by the flow of a cooling fluid such as air, water, oil and/or fluid within or near the applicator . The cooling fluid may flow or be directed around one or more magnetic field generating devices, one or more RF electrodes, between the magnetic field generating device and at least a portion of at least one RF electrode. The cooling fluid can only flow from above and/or below the magnetic field generating device. The cooling fluid may be a fluid such as gas, oil, water and/or liquid. The cooling fluid may be supplied to the applicator from the main unit, where the cooling fluid may be brought to the desired temperature. A cooling fluid may be supplied to the applicator and to the area in the vicinity of the magnetic field generating device and/or the RF electrode. Cooling fluid may be supplied to the applicator via a connecting tube attached to the main unit. The connecting tube may include a fluid passage that may serve as a passage for cooling fluid between the applicator and the main unit.

[218] The main unit may contain one or more cooling tanks, where the cooling fluid can be stored and/or cooled. Each cooling reservoir may contain one or more pumps, where one pump may provide cooling fluid to one applicator. Alternatively, a single pump may provide cooling fluid to a plurality of applicators (eg, two applicators). In addition, the main unit may contain one cooling reservoir, which stores and/or cools the cooling fluid for one corresponding applicator or more applicators. For example, when the therapeutic device contains two applicators, the main unit may contain one cooling reservoir providing cooling fluid for both applicators. In another example, when the therapeutic device contains two applicators, the main unit may contain two cooling reservoirs to provide cooling of the cooling fluid. Each cooling reservoir may provide synchronous or independent cooling of the cooling fluid supplied to one particular applicator. The cooling reservoir or fluid passage may include a temperature sensor for measuring the temperature of the cooling fluid.

[219] The fluid passage may be a plastic tube. The plastic tube may lead from the cooling reservoir to the applicator and then back to the cooling reservoir. When the therapeutic device contains, for example, two applicators, the fluid path may lead from the cooling reservoir to one applicator and then back to the cooling reservoir, and the second fluid path may lead from the same or different cooling reservoir to the second applicator and then back. to the cooling tank. However, the fluid passage may lead from the cooling reservoir to the first applicator, then to the second applicator and finally to the cooling reservoir.

[220] When the RF electrode is located near the magnetic field generating device, the time-varying magnetic field generated by the magnetic field generating device may induce undesirable physical effects in the RF electrode. Undesirable physical effects induced by a time varying magnetic field may include, for example, the induction of eddy currents, overheating of the RF electrode, skin effect, and/or the initiation of other electrical and/or electromagnetic effects, such as phase shift, in the RF electrode. Such undesirable physical effects may result in malfunction of the therapeutic device, loss of energy, reduced therapeutic effect, increased energy consumption, overheating of at least a portion of the applicator, such as overheating of the RF electrode, collection of incorrect feedback information, misadjustment of the signals sent to the RF electrode, and /or to other undesirable effects.

[221] The described invention provides options, methods or schemes for preventing and/or minimizing one or more undesirable physical effects induced in an RF electrode by a magnetic field. The same options, methods or plans can help to minimize shielding of the magnetic field by the RF electrode. One option may include positioning the RF electrode such that it minimally overlaps or does not overlap the magnetic field generating device according to a plan view of the applicator. Another option may include a specially designed RF electrode, as described below. Another option may include reducing the thickness of the RF electrode. Another option may include providing an RF electrode of a conductive material that reduces the induction of unwanted physical effects and heating of the RF electrode. One or more RF electrodes providing RF energy during therapy with the described therapeutic device may use at least one of these options, at least two options, and/or a combination of these options and their characteristics, as described below.

[222] One option for minimizing or eliminating undesirable physical effects induced in the RF electrode by a magnetic field may include positioning the RF electrode such that it minimally or does not overlap the magnetic field generating device, as measured by the horizontal projection of the applicator.

[223] FIG. 11 depicts an example in which the RF electrode 101a may be below, adjacent to, and/or above the magnetic field generating device 900 and does not overlap or minimally overlap the magnetic field generating device 900 according to the plan view of the applicator. As shown in FIG. 11, the electrode 101a may be outside the area A2.

[224] FIG. 12 depicts another exemplary applicator containing a magnetic field generating device and one or more RF electrodes. The applicator 800 may include two RF electrodes 101a and 101b separated by a gap 113. The two RF electrodes 101a and/or 101b may at least partially overlap 112 the winding area A2 and/or the area A1 of the magnetic field generating device 900 according to a plan view of the applicator. The partial overlap region 112 is represented by the circled region in FIG. 12. A plan view may be represented by an x-ray image of the applicator 800 from below the applicator. Such partial overlap region 112 may be 1% to 100%, or 1% to 99%, or 1% to 70%, or 5% to 50%, or 5% to 40%, or 10%. up to 30%, or from 25% to 100%, or from 10% to 100%, or from 30% to 95%, or from 40% to 100%, or from 70% to 100%, or from 80% to 95 %, or from 30 to 70% of the area of one RF electrode according to the horizontal projection of the applicator. The overlap area of two areas may refer to the ratio between these two different areas.

[225] One or more temperature sensors 816a may be positioned between the bipolar RF electrodes 101a, 101b as shown in FIG. 12. One or more temperature sensors 816a may be at least partially surrounded by at least one RF electrode 101a and 101b according to the plan of the applicator, as shown by temperature sensors 816a in FIG. 12. Most of the RF energy can pass between the bipolar electrodes 101a and 101b. Therefore, the volume of the area of the body or tissue being treated between or immediately below the bipolar electrodes may have the highest temperature and should be measured as the actual temperature or reference temperature to refer to a predetermined temperature. However, the temperature sensor may be placed inside the applicator or on the surface of the applicator.

[226] The characteristic shape of the RF electrode can create uneven distribution of heating temperature during therapy. It may be useful to position the temperature sensor 816b so that it is not between the bipolar RF electrodes 101a, 101b and that the temperature sensor is not surrounded by the bipolar electrodes 101a, 101b. The temperature sensor may be located inside the applicator or on the surface of the applicator. Also, a temperature sensor 816c may be located below the RF electrode. The material of the first side portion 801 and/or the second side portion 802 covering at least a portion of the temperature sensor 816 (for example, 816a, 816b or 816c) and in contact with the patient's body may be the same material from which the first side portion 801 is made and /or the second side part 802. However, the material of the first side part 801 or the second side part 802 covering the temperature sensor 816 may differ from the material of the rest of the first side part 801 or the second side part 802, for example, it may be a material with higher thermal conductivity, for example, ceramic, titanium, aluminum or other metallic material or alloy. Temperature sensor 816 may be a thermistor. The temperature sensor 816 (e.g., 816a, 816b, or 816c) may be fixed or attached to the first side portion 801 and/or the second side portion 802 with a thermally conductive material such as a thermally conductive epoxy resin layer with good thermal conductivity. The wiring between the temperature sensor 816 and the rest of the therapeutic device may be one, two, or more electrical wires with a diameter ranging from 0.05 mm to 3 mm, or from 0.01 mm to 1 mm, or from 0.1 mm. up to 0.5 mm. A wired connection containing an electrical wire with a described diameter can be advantageous by minimizing heat transfer between the wire and the temperature sensor 816. The wired connection to the temperature sensor 816 can have a thermal conductivity in the range of 5 W⋅m ^-1 ⋅K ^-1 to 320 W⋅m ^-1 ⋅K ^-1 , or from 6 W⋅m ^-1 ⋅K ^-1 to 230 W⋅ m ^-1 ⋅K ^-1 , or from 6 W⋅m ^-1 ⋅K ^-1 to 160 W⋅m ^-1 ⋅K ^-1 , or from 20 W⋅m ^-1 ⋅K ^-1 to 110 W⋅m ^{- 1} ⋅K ^-1 , or from 45 W⋅m ^-1 ⋅K ^-1 to 100 W⋅m ^-1 ⋅K ^-1 , or from 50 W⋅m ^-1 ⋅K ^-1 to 95 W⋅m ^-1 ⋅ K ^-1 . The wire connection material can be, for example: nickel, monel, platinum, osmium, niobium, potassium, steel, germanium, aluminium, cobalt, magnesium, copper and/or their alloys. At least a portion of the wired connection to the temperature sensor 816 may be thermally insulated with a protective sheath or shielding, such as a rubber tube. The temperature sensor 816 may be an optical temperature sensor, such as an infrared IR temperature sensor, which may be part of the applicator and/or housed in the main unit. During therapy, the optical temperature sensor may be in contact with the patient's skin or be at a distance of 0.1 cm to 3 cm, or 0.2 cm to 2 cm from the patient's skin. The optical temperature sensor can collect information from the patient's skin through an optical cable.

[227] One or more RF electrodes located with at least partial overlap under the device that generates a magnetic field, can provide a synergistic effect of magnetotherapy and RF therapy. A stronger or more intense therapy outcome can be provided by RF electrodes positioned at least partially overlapped below the magnetic field generating device. The RF field and the magnetic field generated by the therapeutic energy sources in such a configuration can be targeted at the same area of the body and/or the same target biological structures. This may result in better heating of the stimulated muscles and adjacent tissues, better suppression of discomfort caused by muscle stimulation (eg, muscle contraction), better regeneration after therapy, and/or better prevention of panniculitis and other tissue damage.

[228] Another option for minimizing or eliminating the undesirable physical effects induced in the RF electrode by the magnetic field may include a special design of the RF electrode.

[229] The present invention also provides that undesirable physical effects induced by a magnetic field in an RF electrode located adjacent to, or at least partially overlapping, a magnetic field generating device can be further minimized or eliminated by using a segmented RF electrode. The segmented RF electrode may include holes, notches and/or protrusions. The areas of holes and/or cutouts may be formed by air, dielectric and/or other electrically insulating material. The electrode may contain various protrusions. Several holes and/or cutouts may be visible in a plan view of such an electrode. Another parameter that minimizes or eliminates the presence of undesirable physical effects may be the thickness of the RF electrode. If the conductive material of the RF electrode is thin and the region of the RF electrode is at least partially separated by an insulator, the magnetic field induced eddy current loops can be very small and thus induction in such regions is minimized.

[230] The RF electrode may include one or more apertures or cutouts that may segment the conductive region of the RF electrode and/or the perimeter of the RF electrode. Therefore, the RF electrode is segmented compared to a conventional electrode (ie, an electrode without holes or notches) by distorting its surface area. Two or more holes or cutouts of one RF electrode may be asymmetrical. One or more holes and cutouts may be, for example, rectangular or circular. The opening may be any lumen and/or opening in the RF electrode area according to the plan of the applicator. The holes and/or cutouts may be regular, irregular, symmetrical and/or asymmetrical. The holes and/or cutouts may be filled with, for example, air, a dielectric and/or other electrically insulating material (eg, the dielectric material of a printed circuit board). When the RF electrode contains two or more holes or cutouts, the holes or cutouts may have a common point of symmetry and/or a line of symmetry. The distance between the two closest points located at the boundaries of two different holes and notches of the RF electrode can be from 0.1 mm to 50 mm, or from 0.1 mm to 15 mm, or from 0.1 mm to 10 mm, or from 0.1 mm to 8 mm. When the RF electrode at least partially overlaps the magnetic field generating device, the RF electrode may include enlarged holes and notches in a portion of the conductive surface located closer to the center of the magnetic field generating device.

[231] FIG. 13A depicts an exemplary RF electrode, wherein the RF electrode 101 has an electrode area 119a and defines one or more holes 117 in the conductive area of the RF electrode. Holes 117 may be elongated slots having a rectangular shape. Each hole 117 may be parallel to other holes.

[232] FIG. 13b shows another exemplary RF electrode, wherein the RF electrode 101 has an electrode area 119a and one or more holes 117a and 117b in the RF electrode conductive area. Holes 117a are not parallel to holes 117b.

[233] FIG. 13c depicts another exemplary RF electrode, wherein the RF electrode 101 has an electrode area 119a and a combination of one or more holes 117 in the conductive area, a notch 115 in the conductive area, and an RF electrode protrusion 114.

[234] FIG. 13d depicts another exemplary RF electrode, wherein the RF electrode 101 comprises a combination of one or more holes 117 in the conductive area and notches 115 in the electrode area. The lines represent a thin line (eg, a single conductor) of the RF electrode area 119a. The RF electrode may be a grid of conductive wires or a mesh of conductive wires. The protrusion 114 may define one or more notches 115 around the perimeter of the electrode.

[235] FIG. 13e shows another exemplary RF electrode containing projections and notches. The RF electrode 101 is characterized by an electrode area 119a, a boundary length 119b, and a plurality of protrusions shown as N _# . The protrusions may define notches of the protrusions (eg, notch 115, in which the notch may be an opening or a gap). The RF electrode 101 may include at least two, three, or five protrusions 114 (eg, 114a, 114b), or more. The protrusions 114 may be separated from each other by a notch 115. Similarly, the RF electrode 101 may include one, two, three or more notches of the protrusions. The first protrusion 114a and the second protrusion 114b of the plurality of protrusions may be arranged generally parallel to each other. The protrusions 114 may be spaced at regular intervals and regularly. The protrusions 114a, 114b may be in the form of rods or pins having a generally linear shape. The protrusions 114a and 114b may be made of a conductive material. Notch 115 may be filled with air, dielectric, or other electrically insulating material. The distance between the protrusions is such a distance that at least one circle 118a can hypothetically be inscribed in the notch 115 and between the two protrusions 114a and 114b. The at least one circle 118a may have a diameter in the range of 0.001 mm to 30 mm, or 0.005 mm to 15 mm, or 0.01 mm to 10 mm, or 0.01 mm to 8 mm, or 0.01 mm to 7 mm, or from 0.01 mm to 5 mm, or from 0.01 mm to 3 mm, or from 0.01 mm to 2 mm, wherein each circle may be characterized by at least one point of contact located on the first ledge 114a, and at least one touch point located on the second ledge 114b. Each circle 118a may be characterized by different touch points. The notch 115 may be symmetrical and/or asymmetrical along its length. Notch 115 may form a constant distance between projections 114a and 114b. The distance between the protrusions 114a and 114b may not be constant along the length of the protrusions. The smallest distance between the two nearest protrusions 114a, 114b may increase and/or decrease as the length of the protrusions increases.

[236] The protrusions 114 or notches 115 may be symmetrical, asymmetrical, irregular, and/or regular. The size, shape and/or symmetry of the individual protrusions 114 in the RF electrode 101 may be the same and/or different. For example, each protrusion 114 may have the same shape, size, and/or symmetry.

[237] The protrusions 114 may be distinguished by a hypothetical circle 118b inscribed directly in the protrusion. The hypothetical circle 118b inscribed in the projection 114 may have a diameter in the range of 0.001 mm to 30 mm, or 0.01 mm to 15 mm, or 0.2 mm to 10 mm, or 0.2 mm to 7 mm, or from 0.1 mm to 3 mm. A hypothetical inscribed circle may not intersect the boundary of the ledge it is inscribed in. The magnetic flux density, B, measured over at least a portion of the surface area of the RF electrode, may be in the range of 0.1 T to 5 T, or in the range of 0.2 T to 4 T, or in the range of 0.3 T to 3 T, or in the range of 0.5 T to 5 T, or in the range of 0.7 T to 4 T, or in the range of 1 T to 3 T. The magnetic flux density, V, measured over at least a portion of the surface area of the RF electrode, may be measured during therapy. The surface area of the RF electrode may include the conductive surface area of the RF electrode.

[238] The number of protrusions, N _# included in one RF electrode, means the maximum possible number of conductive areas, electrically insulated from each other, that can be formed between and/or formed by two parallel notches 111 on the surface of the RF electrode. The distance between two parallel notches 111 may be in the range of 1 mm to 50 mm, or 2 mm to 35 mm, or 5 mm to 20 mm. The number of projections, N _# , may range from 5 to 1000, or from 10 to 600, or from 20 to 400, or from 50 to 400, or from 100 to 400, or from 15 to 200, or from 30 to 100, or 40 to 150, or 25 to 75.

[239] The total number of protrusions in one RF electrode, regardless of the parallel notches 111, can range from 5 to 1000, or from 10 to 600, or from 20 to 400, or from 50 to 400, or from 100 to 400, or from 15 to 200, or 30 to 100, or 40 to 150, or 25 to 140.

[240] The total number of holes or notches in a single RF electrode, regardless of the parallel notches 111, can range from 5 to 1000, or 10 to 600, or 20 to 400, or 50 to 400, or 100 to 400, or 15 to 200, or 30 to 100, or 40 to 150, or 25 to 140.

[241] The number of holes, cutouts and/or protrusions in one RF electrode located under the coil, including its core, can be in the range from 5 to 1000, or from 10 to 600, or from 20 to 400, or from 50 to 400, or 100 to 400, or 15 to 200, or 30 to 100, or 40 to 150, or 25 to 140.

[242] The number of individual protrusions enclosed in one RF electrode may range from 1 to 8000, or from 2 to 8000, or from 5 to 8000, or from 3 to 5000, or from 5 to 1000, or from 5 to 500 , or from 10 to 500, or from 5 to 220, or from 10 to 100 on an area measuring 2 cm by 1 cm.

[243] The magnetic flux density, V, and/or the amplitude of the magnetic flux density measured during therapy on at least a portion of the RF electrode 101 may be in the range from 0.1 T to 5 T, from 0.2 T to 4 T , 0.3 T to 3 T, 0.7 T to 5 T, 1 T to 4 T, or 1.5 T to 3 T. The electrode can be determined using the density of the protrusions, ρ _p , according to equation 1,

Equation 1:

Where n denotes the number of protrusions crossing the magnetic field line of the magnetic flux density, B [T] , And l [cm] denotes the length of the magnetic field line intersected by these projections. Length l may be at least 1 cm, and the magnetic field line may be characterized by a magnetic flux density, B [T] , at least 0.3 T or 0.7 T. The density of the protrusions according to the therapeutic device can be at least a part of the RF electrode in the range of 0.3 cm^-1⋅Tl^-1 up to 72 cm^-1⋅Tl^-1 or from 0.4 cm^-1⋅Tl^-1 up to 10 cm^-1⋅Tl^-1, or from 0.4 cm^-1⋅Tl^-1 up to 7 cm^-1⋅Tl^-1, or from 0.5 cm^-1⋅Tl^-1 up to 6 cm^-1⋅Tl^-1, or from 0.8 cm^-1⋅Tl^-1 up to 5.2 cm^-1⋅Tl^-1.

[244] The protrusions may be wider (ie, thicker) where the magnetic flux density is lower, and thinner where the magnetic flux density is higher. In addition, the density of the protrusions, ρ _p , may be higher where the magnetic flux density is higher.

[245] The electrode area for one or more RF electrodes in one applicator or one additional therapeutic device can be in the range from 1 cm ² to 2500 cm ² or from 25 cm ² to 800 cm ² , or from 30 cm ² to 600 cm ² , or from 30 cm ² to 400 cm ² , or from 50 cm ² to 300 cm ² , or from 40 cm ² to 200 cm ² in accordance with the horizontal projection of the applicator.

[246] The RF electrode may have a boundary ratio. The boundary ratio can be defined as the ratio between the length of the closed curve and the area of the electrode. An example of a boundary relation is shown in Fig. 13e, where the length of the closed curve can be shown as the boundary length 119b, and the area of the RF electrode is shown by the area of the RF electrode 119a according to the plan view of the applicator. RF electrode area 119a is the area of the RF electrode minus the wires supplying the RF electrodes and the sum of the length of the closed curve of all holes and/or cutouts. The boundary length 119b is the sum of the length of the closed curve of the electrode and the lengths of the closed curves of all holes inscribed in the electrode, if present. The boundary RF ratio of the electrode can be in the range of 150 m ^-1 to 20000 m ^-1 or 200 m ^-1 to 10000 m ^-1 , or 200 m ^-1 to 4000 m ^-1 , or 300 m ^-1 to 10000 m ^-1 , or from 300 m ^-1 to 4000 m ^-1 , or from 500 m ^-1 to 4000 m ^-1 , or from 10 m ^-1 to 20000 m ^-1 , or from 20 m ^-1 to 10000 m ^{- 1} , or from 30 m ^-1 to 5000 m ^-1 .

[247] According to the plan view of the applicator, at least one RF electrode may have a boundary ratio in the range of 150 m ^-1 to 20,000 m ^-1 or 250 m ^-1 to 10,000 ^{m -1} , or 4000 m ^-1 , or from 300 m ^-1 to 1000 m ^-1 , or from 400 m ^-1 to 4000 m ^-1 , or from 400 m ^-1 to 1200 m ^-1 , or from 500 m ^-1 to 2000 m ^-1 , or 10 m ^-1 to 20000 m ^-1 , or 20 m ^-1 to 10000 m ^-1 , or 30 m ^-1 to 5000 m ^-1 at locations where the magnetic flux density, V, is at least part of the RF electrode surface may be in the range of 0.1 T to 7 T, or 0.3 T to 5 T, 0.5 T to 3 T, 0.5 T to 7 T, or in the range of 0.7 T to 5 T or in the range of 1 T to 4 T. By increasing the magnetic flux density, V, through the RF electrode area, the boundary ratio can also be increased.

[248] The relationship between the boundary ratio and the magnetic flux density, V, on the surface area of the RF electrode may be referred to as the charge ratio. The charge ratio may be related to a square surface area of the RF electrode of at least 1.5 ^cm2 and a magnetic flux density in the range of 0.1 T to 7 T or 0.3 T to 5 T or 0.5 T up to 3 T, or from 1 T to 5 T, or from 1.2 T to 5 T. The charge ratio of at least a portion of the RF electrode may range from 70 m ^-1 ⋅B ^-1 to 30000 m ^-1 ⋅B ^-1 or from 100 m ^-1 ⋅B ^-1 to 5000 m ^-1 ⋅B ^-1 , or from 100 m ^-1 ⋅B ^-1 to 2000 m ^-1 ⋅B ^-1 , or from 120 m ^-1 ⋅B ^-1 to 1200 m ^-1 ⋅B ^-1 , or from 120 m ^-1 ⋅B ^-1 up to 600 m ^-1 ⋅B ^-1 , or from 230 m ^-1 ⋅B ^-1 to 600 m ^-1 ⋅B ^-1 . The square surface area of the RF electrode may include a square-shaped surface area.

[249] At a large cutoff ratio and/or charge ratio, the induced undesirable physical effects in the RF electrode may become smaller, since the RF electrode may contain protrusions partially isolated from each other. With a large boundary ratio and/or charge ratio, the possible hypothetical circles inscribed in the protrusions should also be smaller, and therefore the induced eddy current loops should be smaller. Therefore, the induced eddy currents become smaller, and the induced unwanted physical effect induced in the RF electrode becomes smaller or minimized.

[250] The ratio between the area of one side of all RF electrodes (horizontal projection) and one side of all areas of the windings of all magnetic field generating devices (area A2, as shown in Fig. 9a), in one applicator and in accordance with its horizontal projection can range from 0.1 to 15, or from 0.5 to 8, or from 0.5 to 4, or from 0.5 to 2.

[251] As shown in FIG. 16, if one projection 114 crosses the magnetic field lines, B ₁ and B ₂ , where the absolute value |B ₁ | greater than the absolute value |B ₂ |, and |B ₁ | - |B ₂ |>0.05 T, then this protrusion can be divided by lines of force B ₁ and B ₂ into three areas. In other words, projection 114 shown in FIG. 16 can be divided into thirds S ₁ , S ₂ , S ₃ , which have the same length according to the direction of the magnetic field gradient, and S ₁ is subjected to a higher magnetic flux density than S ₃ . Area S ₁ may be placed at the highest magnetic flux density, S ₂ may be placed at an average magnetic flux density, and S ₃ may be placed at the lowest magnetic flux density. The maximum hypothetical inscribed circle k ₁ with diameter d ₁ inscribed in area S ₁ may have a smaller diameter than the maximum inscribed circle k ₂ with diameter d ₂ inscribed in area S ₃ . The diameter d ₂ may be greater than the diameter d ₁ by 2% to 1500%, or from 5% to 500%, or from 10% to 300%, or from 10% to 200%, or from 10% to 100%, or from 5% to 90%, or 20% to 70%, or 5% to 20% of the diameter d ₁ . In this case, the projections may be thinner where the magnetic flux density is higher, for example, so that a partially pyramidal projection shape can be formed. Additionally, the projections may be thinner where the magnetic flux density is higher.

[252] The RF electrode can be characterized by different sizes and shapes. According to the present invention, the bipolar electrodes may be parallel electrodes as shown in FIG. 14a-14e, or concentric electrodes as shown in FIG. 15a-15c. One type of RF electrodes 101 shown in FIG. 14a-14e and figs. 15a-15c, which may be located adjacent to the second side of the applicator, may be used as the RF electrodes 102 adjacent to the first side and/or in place of any other one or more RF electrodes.

[253] The shape and arrangement of the RF electrodes of the at least one applicator may be based on the size, shape, and symmetry of the body location (anatomy) to which the at least one applicator will be attached. Positioning and different shapes of the RF electrode can be helpful in preventing heat spots, providing uniform heating to as much of the body area being treated as possible, and avoiding the need to move around with one or more applicators.

[254] FIG. 14a shows an example of a symmetrical arrangement of RF electrodes. In FIG. 14b shows another example of a symmetrical arrangement of RF electrodes. In FIG. 14c shows another example of a symmetrical arrangement of RF electrodes. In FIG. 14d is a view of an applicator containing a symmetrical arrangement of RF electrodes. In FIG. 14e is a side view of an applicator containing an example of a symmetrical arrangement of RF electrodes.

[255] According to the examples of the RF electrodes shown in FIG. 14a-14e, the applicator may include at least one pair of parallel bipolar RF electrodes 101a and 101b separated by a gap 113. The RF electrodes are powered by wires 100a and 100b. As shown in FIG. 14a, 14b and 14d, the RF electrodes 101a, 101b may be symmetrical and mirror images. The shape of the individual RF electrodes 101a and 101b may be irregular, asymmetrical, and the length and/or area of at least 40%, 50%, 70%, 90%, or 99% of all protrusions in one RF electrode may differ. Through body anatomy and testing, it can be proven that RF electrodes of this kind can provide the most comfortable and effective therapy for areas of the body such as the abdomen, buttocks, arms and/or thighs.

[256] As shown in FIG. 14c, the RF electrodes 101a, 101b may be at least partially symmetrical with respect to at least one axis or center of symmetry, such as in line symmetry, point symmetry, and rotational symmetry. For example, each electrode may be semi-circular or C-shaped. In addition, the gap 113 between the RF electrodes 101a, 101b may be irregular in shape and/or provided in accordance with at least one axis of symmetry, such as a linear axis of symmetry with mirror symmetry. Thus, in the case where the electrodes 101a and 101b may be semi-circular, the gap 113 may be circular. The use of such a symmetrical electrode may be advantageous for treating an area of the body where such symmetry may be required to emphasize the symmetry of a body area (eg buttocks or thighs).

[257] The gap 113 between the RF electrodes 101a and 101b may contain air, a cooling fluid, oil, water, a dielectric material, a fluid, and/or any other electrical insulator, such as a substrate of a composite material used in printed circuit boards. The RF electrode 101a and 101b may be formed from copper foil and/or a layer deposited on such a substrate. The gap 113 can influence the shape of the electromagnetic field (eg, RF field) generated by the RF electrodes and the depth of penetration of the electromagnetic field into the tissue of the patient's body. In addition, the distance between the at least two RF electrodes 101a and 101b may form a gap 113, which may be at least partially circular, elliptical and/or parabolic in shape, as shown in FIG. 14a. The gap 113 may be properly shaped to position the RF electrodes at a constant distance, as shown in FIG. 14b.

[258] The gap 113 between the RF electrodes 101a and 101b may be configured to allow the magnitude of the magnetic field generated by the magnetic field generating device to pass in the range of 2% to 70%, or 5% to 50%, or 15% to 40%. The distance between proximate parts of at least two different RF electrodes in one applicator may be in the range of 0.1 cm to 25 cm, or 0.2 cm to 15 cm, or 2 cm to 10 cm, or 2 cm to 5 cm. cm.

[259] The gap 113 between the two RF electrodes may be formed in the RF plane of the bipolar electrodes, wherein the gap 113 may at least partially overlap the location at which the magnetic flux density generated by the magnetic field generating device has the highest absolute value. Gap 113 may be located at this location to optimize therapy effectiveness and minimize energy loss.

[260] It should be noted that a strong magnetic field with a high magnetic flux density derivative, dB/dt, can induce undesirable physical effects even in an RF electrode with projections, holes, and/or notches. Gap 113 may be set or located at a location where the absolute value of the magnetic flux density is highest. As a consequence, the plurality of RF electrodes located around gap 113 can then be affected by a lower amount of magnetic flux density.

[261] A plurality of RF electrodes (eg, two RF electrodes 101a and 101b) may be arranged on the substrate 113a as shown in FIG. 14d. Substrate 113a can be used as gap filler 113 between the RF electrodes and one or more notches 115. As shown in FIG. 14d and 25, substrate 113a and one or more RF electrodes may be curved into a desired shape and/or radius consistent with the region of the patient's body. The RF electrodes 101a or 101b may be curved along the bottom cover 125 of the applicator 800, in particular along the curved portion 126 of the bottom cover 125. As shown in FIG. 14d, the substrate 113a may define a substrate gap 113b for at least one sensor, such as a temperature sensor. The substrate gap 113b may further allow passage of one or more wires, cooling fluid, and/or implementation of another source of therapeutic energy, such as a phototherapy energy source (e.g., LED, laser diode) providing illumination or additional heating of the biological structure and/or body areas.

[262] FIG. 15a, 15b and 15c show two RF electrodes 101a and 101b, wherein at least one RF electrode 101a may at least partially surround the second RF electrode 101b. The RF electrodes 101a and 101b may be separated by a gap 113 containing, for example, a substrate 113a with the same insulating properties as described above with respect to FIGS. 14a-14e. The RF electrode 101b may include a lumen 116 to minimize magnetic field shielding and induce unwanted physical effects induced in the RF electrode 101b. The lumen 116 may be located in the plane of the RF electrode where the magnetic flux density of the magnetic field generated by the magnetic field generating device reaches its highest values during therapy. The lumen 116 may be circular or may have other shapes such as oval, square, triangular, or rectangular, among others. The lumen 116 may have an area of 0.05 cm ² to 1000 cm ² , or 0.05 cm ² to 100 cm ² , or 3 cm ² to 71 cm ² , or 3 cm ² to 40 cm ² , or 3 cm ² to 20 cm ² , or from 3 cm ² to 15 cm ² , or from 0.5 cm ² to 2.5 cm ² . RF electrodes may be fully or partially concentric.

[263] FIG. 15a shows RF electrodes 101a and 101b, which may be non-circular with at least one linear and/or point symmetry. The electrodes 101a and 101b shown may not have a center of symmetry. The illustrated RF electrode 101a may include a gap 116 at its center where the magnetic flux density is highest in order to minimize the magnetic field induction of an undesirable physical effect in the RF electrode.

[264] FIG. 15b shows two RF electrodes 101a and 101b, which may be circular in shape with rotational symmetry. RF electrodes 101a and 101b may have one center of symmetry. The illustrated RF electrode 101a may include a gap 116 at its center where the magnetic flux density is highest in order to minimize the magnetic field inducing undesirable physical effects in the RF electrode.

[265] FIG. 15c shows two RF electrodes 101a and 110b, which may not be symmetrical and may not have a center of symmetry.

[266] Another possibility of minimizing or eliminating undesirable physical effects induced in the RF electrode by a magnetic field may include reducing the thickness of the RF electrode.

[267] The thickness of the conductive layer of the RF electrode according to the present invention may be in the range of 0.01 mm to 10 mm, or 0.01 mm to 5 mm, or 0.01 mm to 3 mm, or 0.01 mm to 1 mm, or from 0.1 mm to 1 mm, or from 0.005 mm to 0.1 mm, or from 0.01 mm to 0.2 mm. One type of RF electrode can be made in a manner similar to printed circuit board (PCB) fabrication, wherein a thin conductive layer can be deposited in and/or on a substrate with insulating properties. The substrate may comprise one, two or more conductive layers of material such as copper, silver, aluminium, nickel and zinc alloys, austenitic stainless steel and/or other materials forming the RF electrode. The thickness of the substrate material may be in the range of 0.01 mm to 10 mm, or 0.01 mm to 5 mm, or 0.01 mm to 3 mm, or 0.01 mm to 2 mm, or 0.1 mm to 2 mm, or from 0.5 mm to 1.5 mm, or from 0.05 mm to 1 mm. The substrate material may be a sheet of polymer, ceramic, copolymer, phenolic resin layer, epoxy resin layer, fiberglass cloth, other textile web, polymeric cloth, and/or other material. The substrate may be at least partially flexible and/or rigid.

[268] The RF electrode may be a system of thin conductive wires, flat tracks, sheets, and the like.

[269] Another possibility of minimizing or eliminating undesirable physical effects induced in the RF electrode by a magnetic field may include forming the RF electrode from a conductive material, reducing the induction of undesirable physical effects and heating the RF electrode.

[270] RF electrodes can be made from special conductive materials that reduce the induction of undesirable physical effects in the RF electrode. Such materials may have a relative permeability in the range of 4 to 1,000,000, or 20 to 300,000, or 200 to 250,000, or 300 to 100,000, or 300 to 18,000, or 1,000 to 8,000. The RF electrode material may include carbon, aluminum , copper, nickel, cobalt, manganese, zinc, iron, titanium, silver, brass, platinum, palladium and/or other alloyable materials such as mu-metal, permalloy, electric steel, ferritic steel, ferrite, stainless steel of them. Additionally, to reduce the induction of eddy currents and heating of the RF electrode, and to minimize the energy loss of the time-varying magnetic field, the RF electrode can be made from mixed metal oxides and/or fixed powder from metal oxides, metal from mu-metal elements.

[271] In one or more RF electrodes delivering RF energy during therapy using the described therapeutic device, you can use at least one of the possibilities, at least two possibilities, and / or a combination of the possibilities of minimizing or eliminating undesirable physical effects, induced by a magnetic field, as described above. Also, one or more capability characteristics can be used to manufacture, manufacture, and operate a therapeutic device according to the present invention.

[272] A therapeutic device in which RF therapy is combined with magnetotherapy may comprise one or more therapy circuits. The RF therapy circuit may comprise a power supply, an RF electrode, and/or all of the electrical components described herein for an RF cluster. The magnetotherapy circuit may include a power supply, a magnetic field generating device, all electrical elements described in this document for a HIFEM magnetic cluster. A plurality of therapy circuits providing the same or different therapies may share a common power supply. Alternatively, each therapy circuit may contain its own power supply. The operation of all therapy circuits can be controlled by one master unit or one or more control units. The HMI, master unit, and/or one or more control units may be used to select, control, and/or adjust one or more therapy parameters for each applicator and/or each therapeutic energy source (eg, RF electrode or magnetic field generating device). The therapy parameters can be selected, controlled and/or adjusted by the HMI, the master unit and/or one or more control units independently for each applicator.

[273] FIG. 17 depicts exemplary electrical elements of magnetic circuit 400. An electrical signal passing through magnetic circuit 400 may be converted into one or more electrical signal pulses. These electrical pulses may be delivered to a magnetic field generating device to generate unit pulses of a time varying magnetic field. The individual electrical elements of the magnetic circuit may be a power source (PS), an energy storage device (ESD), a switch (SW), a magnetic field generating device (MFGD), and a magnetic circuit control unit (CUM). The magnetic circuit may contain a magnetic therapy cluster called a HIFEM cluster. The HIFEM cluster may contain, for example, ESD, SW and/or CUM. The magnetic circuit control unit CUM may be part of the control system. The control unit CUM of the magnetic cluster and/or other electrical element of the magnetic circuit may be a slave unit of the master unit. The HIFEM cluster, control system, and/or CUM may provide or manage electrical energy storage in the ESD by controlling the amount of electrical energy stored. The HIFEM cluster, control system and/or CUM may provide electrical signal modification, adjustment of the parameters of the electrical signal transmitted through the HIFEM cluster, safe operation of the circuit, and/or charging or recharging the ESD. For example, the HIFEM cluster or control system may provide for adjusting the magnetic flux density of the magnetic field generated by the MFGD by adjusting the voltage and/or current of electrical pulses transmitted to the MFGD. Modification of the electrical signal may include distorting the signal transmitted in the magnetic circuit, distorting the envelope in shape, amplitude and/or in the frequency domain, adding noise to the transmitted electrical signal, and/or otherwise reducing the quality of the transmitted electrical signal entering the magnetic circuit.

[274] The ESD power storage device can store electric power delivered to the magnetic field generating device in the form of an energetic electrical signal (for example, in the form of high power single pulses). The ESD may contain one, two, three or more capacitors. The ESD may also include one or more other electrical elements such as a safety element such as a voltage sensor, a high voltage indicator, and/or discharge resistors, as shown in FIG. 18a. The voltage sensor and the high voltage indicator can provide feedback information to the switch SW and the control unit CUM. The discharge resistor is a part that can ensure that at least one capacitor is discharged in the event of a dangerous situation. The discharge of one or more ESDs can be controlled by the control unit CUM. The electrical power released from the ESD may be delivered as a single pulse and/or a high power pulse to at least a portion of the magnetic circuit, such as a magnetic field generating MFGD.

[275] The capacitance of the power storage device may be in the range of 5 nF to 100 mF, or in the range of 25 nF to 50 mF, or in the range of 100 nF to 10 mF, or in the range of 1 μF to 1 mF, or in the range 5 µF to 500 µF, or in the range of 10 µF to 180 µF, or in the range of 20 µF to 80 µF.

[276] The power storage device can be charged from a voltage in the range of 250 V to 50 kV, 700 V to 5 kV, 700 V to 3 kV, or 1 kV to 1.8 kV.

[277] The energy storage device may provide a pulsed discharge current in the range of 100 A to 5 kA, 200 A to 3 kA, 400 A to 3 kA, or 700 A to 2.5 kA. This current may correspond to the value of the maximum magnetic flux density that the device generating the magnetic field generates.

[278] When discharging the power storage device, a high power current pulse with an energy ranging from 5 J to 300 J, 10 J to 200 J, or 30 J to 150 J can be generated.

[279] The switch SW may comprise any switching device such as a diode, a controlled resistor diode, a MOSFET, a JFET, an IGBT, a BJT, a thyristor, and/or a combination thereof. The switch may include a pulse filter to modify the electrical signal. The pulse filter can suppress the switching voltage ripple generated by the switch during ESD discharge.

[280] In order to generate a time-varying magnetic field of the magnetic circuit, the command to periodically turn on/off the SW and discharge the ESD power storage device into a magnetic field generating device, such as a coil, can be commanded.

[281] The inductance of the magnetic field generating device may be up to 1 H or in the range of 1 nH to 500 mH, 1 nH to 50 mH, 50 nH to 10 mH, 500 nH to 1 mH, or in the range of 1 µH to 500 µH, or in the range of 10 µH to 60 µH.

[282] A device that generates a magnetic field may not emit radiation (eg, gamma radiation).

[283] The magnetic circuit may include a series connection of the switch SW and the magnetic field generating device. The switch SW and the magnetic field generating device can be connected together in parallel with the ESD power storage device. The power storage device ESD can be charged using the power supply PS. Then, the power storage device ESD can be discharged through the switch SW into the magnetic field generating device MFGD. During the second half cycle of the LC resonance, the polarity of the power storage device ESD may be reversed from that of the power supply PS. As a consequence, double the voltage of the power supply may occur. In this way, the power supply and all the parts connected in a magnetic circuit can be designed for a high voltage load, and protective resistors can be placed between the power supply and the power storage device.

[284] The magnetic field generating device MFGD and the power storage device ESD may be connected in series. The magnetic field generating device MFGD may be arranged in parallel with the switch SW. The ESD energy storage device can be charged through a device that generates a magnetic field. In order to supply a single energy pulse to generate a magnetic single pulse (or a pulse to generate a magnetic pulse), the power supply is controlled short-circuited by the switch SW. Thus, high voltage loading of the terminals of the power supply PS during the second half cycle of the LC resonance associated with known devices is avoided. The voltage at the terminals of the power supply PS during the second half-cycle of the LC resonance may be equal to the voltage drop across the switch SW.

[285] The switch may be any kind of switching device. Depending on the type of switch, the power supply load can be reduced to a few volts, for example 1-10 volts. Therefore, there is no need to protect the power supply from a high voltage load, for example thousands of volts. Accordingly, the use of protective resistors and/or protection circuits can be reduced or eliminated.

[286] FIG. 18b depicts exemplary electrical elements of an RF circuit 480. The RF circuit may deliver an adjusted and/or modified electromagnetic signal (electrical signal) to an RF electrode (RFE). The RF circuit may contain a power supply (PS), a therapeutic cluster for RF therapy (the area marked as RF), an RF cluster control unit (CURF), a power amplifier (PA), a filter, a standing wave ratio meter in combination with a power meter (meter SWR and power), tuning element (tuning), divider, insulator, balancing element (SYM), preconditioner and RF electrode (RFE). An RF therapy cluster may comprise, for example, an RF cluster control unit (CURF), a power amplifier (PA), a filter, a standing wave ratio meter in combination with a power meter (SWR and power meter), and/or a tuning element (tuning). The RF circuit control unit CURF may be part of the control system. The RF circuit control unit CURF and/or other electrical element of the RF circuit may be a slave unit of the master unit. One or more electrical elements described as part of the RF circuit may be omitted, some electrical elements may be combined into one element with a similar function, and/or some of the electrical elements may be added to increase the functionality of the circuit.

[287] An RF circuit power supply may provide an electrical signal with a voltage in the range of 1 V to 5 kV, or 5 V to 140 V, or 10 V to 120 V, or 15 V to 50 V, or 20 V to 50 V.

[288] CURF can control the operation of any electrical element of the RF circuit. CURF can adjust or modify the parameters of the electrical signal transmitted through the RF circuit. Signal parameters such as voltage, phase, frequency, envelope, current value, signal amplitude, and/or others can be influenced by individual RF electrical elements in the circuit that can be controlled by the CURF, the control system, and/or the electrical properties of the individual RF electrical elements. chains. Electrical elements that affect the signal in the RF circuit can be, for example, a power supply (PS), a power amplifier (PA), a filter, a SWR and power meter, a tuner, a divider, an isolator, a balun element that converts an unbalanced signal into a balanced one. a signal (SYM), a pre-matching device and/or an RF electrode that generates RF waves. Modification of the electrical signal may include distorting the signal transmitted in the RF circuit, distorting the envelope in shape, amplitude and/or in the frequency domain, adding noise to the transmitted electrical signal, and/or otherwise reducing the quality of the transmitted electrical signal entering the RF circuit.

[289] The power amplifier PA may generate an RF signal at a frequency corresponding to the generation of RF waves by the RF electrode. The power amplifier can be a MOSFET, LDMOS, or vacuum tube. The PA may be configured to increase the amplitude of the delivered signal and/or the modified signal to an electrical signal (eg, an RF signal).

[290] The filter may include one or more filters that can suppress an unwanted frequency of the signal transmitted from the power amplifier. One or more filters may filter and provide therapy with a specific frequency band. One or more filters may be used to filter an electrical signal, such as an electrical signal in an RF circuit, according to the frequency domain of the signal in order to pass only the desired frequencies. The filter may be configured to filter out unsuitable signal frequencies based on settings in the filter's internal software and/or hardware. The filter may operate in accordance with communication with another one or more electrical elements, such as CURF. One or more filters may be located between the RF power supply, the PSRF, and the RFE.

[291] The SWR and power meter can measure the RF power output and evaluate the quality of the impedance match between the power amplifier and the applicator. The SWR and power meter may include a SWR meter that can measure the standing wave ratio in the wave transmission direction. The SWR and power meter may include a power meter that can measure the amplitude of such standing waves. The SWR and power meter may communicate with the CURF and/or the tuning element. The SWR and power meter can provide feedback information to prevent the formation of a standing wave in the patient's body, provide improved signal adjustment by the tuning element, and provide safer therapy and more efficient transfer of energy to the biological structure in a more targeted manner.

[292] The tuning element may provide improved impedance matching. The tuning element may comprise, for example, a capacitor, an LC circuit and/or an RLC. The tuning element may provide controlled tuning of the capacitance of the RF circuit system, wherein the RF circuit system includes individual electrical elements of the RF circuit, as well as the tissue of the patient currently undergoing therapy under the action of the delivered RF waves. Tuning of the RF circuit may be provided before and/or during therapy. The tuning element can also be called a matching device.

[293] A symmetric element SYM can convert a signal from an unbalanced input signal to a balanced output signal. The SYM may be a balun and/or a balun transformer containing a twisted coaxial cable to balance the signal between the RF electrodes. The SYM element may provide signal balancing between the first and second bipolar RF electrodes, for example, by generating a phase shift of λ/2 RF signal sent through coaxial cables to the first and second bipolar RF electrodes.

[294] The splitter may split the RF signal transmitted/delivered to the RF circuit over the coaxial cable. The divided signal may have the same phase for each part of the divided signal, and/or the separated signals may have a constant phase shift from one another. For example, the splitter may deliver one portion of the RF signal to the first RF electrode and a second portion of the RF signal to the second RF electrode of the bipolar electrode. The divider may be shared between two or more independent RF circuits, or each RF circuit may contain its own divider.

[295] The insulator may be combined with the divider and/or located before and/or after the divider in relation to the transmission of the RF signal to the RF electrodes. The insulator may be electrical isolation of at least a portion of the RF circuit from the magnetic circuit. An isolator can be used to minimize the influence of the magnetic circuit on the RF circuit.

[296] The pre-matching device can be used in devices that use coaxial cables. The preconditioner may comprise a small coil, a capacitor and/or a resistor.

[297] An RF electrode (RFE) acting as a source of therapeutic energy may comprise one or more unipolar RF electrodes, one or more monopolar RF electrodes, and/or one or more pairs of bipolar RF electrodes.

[298] The RF circuit power supply PS, power amplifier PA, filter, SWR and power meter, tuning, SYM, divider, isolator and/or preconditioner can be at least partially and/or completely replaced by an HF generator that supplies the rest of the circuits, including in the RF electrode, high-frequency electrical signal.

[299] FIG. 24 shows one example of a balancing element SYM. An input coaxial cable 130 delivers an electrical signal (eg, an RF signal) to a splitter 131, which can split the RF signal into two branches. The divider 131 may also include an insulating element such as one, two, three or more capacitors connected in series, forming an insulating length in the range of 4 mm to 100 mm or 20 mm to 50 mm. The SYM can be installed or provided with different lengths of coaxial cables directed to or leading to a pair of bipolar RF electrodes. The difference in length between the coaxial cables 132 and 133 at location l ₁ may range from 0.4λ to 0.6λ, or from 0.46λ to 0.55λ, where λ may be the wavelength of the directional RF signal in the coaxial cable 132 and / or coaxial cable 133. The length of the coaxial cable 132 can be in the range from 1 cm to 5 m, from 5 cm to 90 cm or from 10 cm to 50 cm. The length of the coaxial cables 132+135b can be in the range of λ/4 ±10 % or ±5% or their products by a positive integer. The length of the coax cable 133 can range from 2 m to 12 m or from 2.2 m to 8 m. cables 133+135a can be in the range 3λ/4 ±10% or ±5%. Briefly, the coaxial cables 132+135b are offset relative to the coaxial cables 133+135a by λ/2 ±10% or ±5%. This part of the SYM may cause a 180° phase shift of the RF signal delivered to one of the RF electrodes 101a and 101b. The RF electrodes 101a and 101b may be part of the same applicator, or the RF electrode 101a may be part of the first applicator and the RF electrode 101b may be part of the second applicator. Connector 134 may be used to connect one or more applicators to the main unit. Part l ₂ may be an applicator connecting tube. The length of the coaxial cables 135a and 135b in this connecting tube can range from 1 m to 6 m or from 1.1 m to 4 m, or λ/4 ±10% or ±5%. The interface element 136 may be a conductive connection of the conductive shield portions of the coaxial cables 135a and 135b. The interface element 136 may have a surface area in the range of 0.5 cm ² to 100 cm ² , 1 cm ² to 80 cm ² , or 1.5 cm ² to 50 cm ² . The coupler 136 may comprise a highly conductive material such as copper, silver, gold, nickel, or aluminum, and the impedance of the coupler 136 may be close to zero. The interface element 136 may be, or a capacitor, resistor and/or inductor may be placed between the interface element and the electrode.

[300] The RF circuit and/or magnetic circuit may be at least partially located in one or more applicators. The wire connection between the applicator, the additional therapeutic device and/or the main unit can also be considered part of the RF circuit element and/or the magnetic circuit due to the impedance, resistivity and/or length of the wire connection. One or more elements of the magnetic circuit shown in FIG. 17, the RF circuit shown in FIG. 18b and 18a may be omitted, ordered in a different order, and/or two or more electrical elements may form one separate combined electrical element. Adjustment of the signal delivered to the RF circuit may be at least partially provided by or within another circuit or therapeutic device, such as a magnetic and/or other circuit.

[301] In FIG. 18a shows an exemplary electrical circuit 180 of the therapeutic device. This exemplary circuit contains two independent power supplies, including a RF therapy power supply (PSRF) and a magnetotherapy power supply (PSM), connected to the same power supply network (PN). The PSRF may deliver an electromagnetic signal to two independent RF therapy clusters RF A and/or RF B. The PSM may deliver an electromagnetic signal to one or more HIFEM A and/or HIFEM B magnet therapy clusters. other parts of the therapeutic device such as, among others, a human machine interface (HMI) or host unit. Each magnetic circuit and/or RF circuit can contain its own control units (CUM A, CUM B, and CURF A, CURF B) CURF A and CURF B can be cluster control units for RF therapy A (RF A) and cluster for RF therapy B (RF B).

[302] Control units may comprise one or more PCBs or microprocessors. One or more control units may communicate with each other and/or a master unit, which may be selected as a master unit for other control units when communication is established between master and slave units. The master unit may be the first or only control unit to communicate with the HMI. The master unit may control the CUM A and CUM B units. The master unit may be a control unit containing one or more PCB boards and/or microprocessors. The master unit, control unit A (CUM A) or control unit B (CUM B) can be connected to the HMI. In addition, the master unit may be an HMI or be connected to an HMI.

[303] In FIG. 18a shows two parts of a therapeutic device, where the first part can provide RF therapy and the second part can provide magnetic therapy. The two parts of the therapeutic device can be isolated from one another. The therapeutic device may comprise one or more isolated electrical elements and/or parts of the therapeutic device, and the individual circuits are separated from one another by a voltage shielding barrier, a distance-based barrier, and/or a radiation barrier. Examples of insulated parts can be shown in Fig. 18a with a dashed line. It is also possible that individual electrical elements of the therapeutic device may be isolated from at least one part of the therapeutic device. Insulation of such parts and/or electrical elements can be provided by a material with a high dielectric constant, distance to individual parts and/or electrical elements, a system of capacitors or resistors. In addition, any shielding known from electronics, physics, aluminum blocks and/or other methods can be used.

[304] RF therapy and/or magnetotherapy may be provided by at least one, two, three, four or more therapy circuits (which may be located in the main unit) and/or applicators, wherein one therapy circuit may comprise an RF cluster or magnetic cluster. Each applicator A and B (AP A and AP B) may contain at least one electrical element from one, two or more therapy circuits. Each applicator may contain at least one, two or more different therapeutic energy sources, such as one or more RF electrodes providing RF therapy and one or more magnetic field generating devices providing magnetotherapy. As shown in FIG. 18a, the therapeutic device may include a first applicator (AP A) and a second applicator (AP B). The first applicator (AP A) may include a first RF electrode (RFE A) from the first RF circuit and a first magnetic field generating device (MFGD A) from the first magnetic circuit. The second applicator (AP A) may include a second RF electrode (RFE B) from a second RF circuit and a second magnetic field generating device (MFGD B) from a second magnetic circuit. In another example, the first applicator may comprise a first magnetic field generating device and a first pair of bipolar RF electrodes, while the second applicator may comprise a second magnetic field generating device and a second pair of bipolar RF electrodes. The two applicators may be separately connected to the main unit and may be separately positioned near a body region before or during therapy when connected to a body region in contact with that body region.

[305] In FIG. 18a also shows other individual parts of the therapy device, such as the RF therapy cluster (RF A), the RF therapy cluster (RF B), the HIFEM A therapy magnetotherapy cluster, the HIFEM B therapy magnetotherapy cluster in a magnetic circuit, the power supply for RF therapy (PSRF), power supply for magnetotherapy (PSM), applicator A (AP A), applicator B (AP B). All parts except applicators can be located in the main unit. The splitter, balun (SYM A) and balun (SYM B) shown are parts of two RF circuits. The divider shown in Fig. 18a may be common to RF circuits. The RF therapy power supply (PSRF) may comprise a continuous circuit RF power supply (SPSRF), an auxiliary RF circuit power supply (APS RF), a power grid filter PNFLT, and/or a power supply unit (PU). Individual electrical elements may not be included with other electrical elements in the PSRF. The magnetotherapy power supply (PSM) may comprise an auxiliary power supply A (APS A), an auxiliary power supply B (APS B), a permanent magnetic circuit power supply (SPSM), a power pump generator (PP), an on-board power supply A (BPS). A) and/or on-board power supply B (BPS B). Individual electrical items may not be included in the PSM along with other electrical items. The therapy cluster for magnetotherapy HIFEM A of the magnetic circuit may comprise a control unit A (CUM A), an energy storage device A (ESD A), a switch A (SW A), an emergency protection element (SE) and/or a switching filter (PF). The magnetic therapy cluster HIFEM B in the magnetic circuit may comprise a control unit B (CUM B), an energy storage device B (ESD B) and/or a switch B (SW B). And although not shown in FIG. 18a, the HIFEM B magnetic therapy cluster may also contain a pulse filter (PF) and/or an emergency protection element (SE). Individual electrical elements can be isolated from each other. However, individual electrical elements and/or parts of circuits may be combined and/or may be used in conjunction with other parts of the circuit. As an example, one control unit may be at least partially shared with two or more RF circuits and/or magnetic circuits, and one control unit may regulate the power supply, the power supply network or the power supply source providing power for the RF circuit as well as the magnetic circuit. . Another example may be at least one auxiliary power supply and/or a permanent power supply used in conjunction with at least two RF and/or magnetic circuits.

[306] The HIFEM A magnetotherapy cluster may provide magnetotherapy independently of the HIFEM B magnetotherapy cluster. some of the HIFEM therapy clusters may share separate electrical elements such as a control box, an energy storage device, a pulse filter, and/or others.

[307] As shown in FIG. 18a, a HIFEM magnetic therapy cluster, such as HIFEM A, may comprise a control unit, such as CUM A. A control unit, such as CUM A, may control the charging and/or discharging of an energy storage device, such as ESD A, process feedback information connection and/or adjust the parameters of individual electrical elements and/or therapeutic clusters for HIFEM magnetotherapy. Additionally, a control unit (e.g. CUM A) can control the adjustment of parameters or the operation of electrical elements, for example BPS A from the PSM part of the circuit, switch, PF, ESD A from the therapy cluster for HIFEM A magnetotherapy and / or processing information from sensors in the applicator AP A and/or AP B. A control unit (eg CUM A) may also communicate with another one or more magnetic and/or RF circuits and/or contain a master unit. The power supply PSM, the power storage device ESD and/or the switch SW can be at least partially controlled by a magnetic circuit control unit, such as CUM A. A control unit (eg CUM A) or a master unit and/or one or more separate electrical circuit elements can be regulated by any electrical element based on the mutual connection between them. The master unit may be configured to adjust therapy parameters for magnetotherapy and/or RF therapy based on feedback information provided from sensors and/or based on communication with other control units, such as the master unit. One control unit, CUM or CURF, can independently control one or more circuits providing magnetotherapy and/or RF therapy. At least one control unit may use peer-to-peer communication and/or master-slave communication with other control units (eg, CUM A may be a slave control unit of a master control unit).

[308] The therapeutic device may contain one, two, three or more ESDs, with each ESD may contain one, two, three or more capacitors. One ESD can provide energy to one, two, three or more therapeutic energy sources such as magnetic field generating devices providing magnetotherapy. Each coil can be connected to its own respective ESD or more than one ESD. The ESD may include one or more other electrical elements, such as a safety element SE such as a voltage sensor, a high voltage indicator, and/or discharge resistors, as shown in FIG. 18a. A voltage sensor and a high voltage indicator may provide feedback information to a switch SW and/or a control unit such as CUM A. A discharge resistor as part of the SE may ensure that at least one capacitor is discharged in the event of a dangerous situation. The discharge of one or more ESDs can be controlled by a control unit such as CUM A or CUM B. The signal delivered from the ESD power storage device via switch SW to the magnetic field generating device can be modified by a pulse filter (PF). The PF may be part of the switch SW and/or may be located between the switch SW and a magnetic field generating device such as MFGD A. The PF may suppress switching voltage ripple generated by the switch during ESD discharge. The proposed circuit may periodically turn on/off the SW and discharge the ESD power storage device into a magnetic field generating device, such as MGFD A, to generate a time-varying magnetic field. As shown in FIG. 18a, one or more electrical elements of the magnetic circuit and/or RF circuit may be omitted and/or combined with each other. For example, one or more separate PSRF and/or PSM electrical elements may be combined into one, but the independence of the individual circuits may be reduced. In addition, the electrical elements PF, SE and/or others may be an independent electrical element. In addition, individual circuits for therapy, such as RF circuits, may differ from each other, as seen in FIG. 18a and 18b, electrical elements such as filter, SWR and power meter, tuning, divider, isolator, SYM and/or preconditioner can be omitted and/or combined into one element. The exclusion and/or combination of individual electrical components can result in reduced efficiency of energy transfer to the patient without tuning, large energy losses due to the absence of SYM, pre-matching device and/or tuning, incorrect operation of signal regulation in the circuit, and incorrect feedback information in the absence of a meter. SWR and power, divider and isolator, and/or therapeutic device may be hazardous to the patient in the absence of a filter, SWR and power meter, SYM, and/or tuning element.

[309] The control units CUM A and CUM B can serve as slave units of the master unit, which can instruct both CUM A and CUM B control units to discharge electric current to the respective magnetic field generating devices (for example, MFGD A and MFGD B ). Therefore, the control of each control unit CUM A and CUM B is independent. Alternatively, CUM B may be a slave of CUM A while CUM A itself may be a slave of a master. Therefore, when the host unit instructs CUM A to discharge electric current into a magnetic field generating device (for example, MFGD A), CUM A can instruct CUM B to discharge electric current into another magnetic field generating device (for example, MFGD B) located in another applicator. In another alternative, an additional control unit may be located between the master unit and the control units CUM A and CUM B, with each additional control unit providing bit synchronization, for example. With these approaches, magnetic field pulses can be applied synchronously or simultaneously.

[310] When the therapeutic device comprises more than one magnetic field generating device and the therapy method involves the use of more than one magnetic field generating device (eg, coils), each coil may be connected to a respective magnetic circuit. However, one coil can be connected to multiple magnetic circuits. In addition, the power supply PSM can be used for at least two magnetic field generating devices.

[311] A power supply source, such as a PSM and/or PSRF, can deliver electrical power to at least one or at least one separate electrical element of the RF circuit, magnetic circuit, and/or other part of the therapeutic device, such as the HMI master unit, energy storage device (eg ESD A and/or ESD B), control unit (eg CUM A and/or CUM B) and/or switch (eg SW A or SW B). The power supply may include one or more elements that convert electricity from the connection to the power supply network PN, as shown in FIG. 18a. Some separate electrical elements of the power supply, RF circuit and/or magnetic circuit may be designed as one common electrical element and need not be designed as separate electrical elements depicted in FIG. 18a. Each RF and/or magnetic circuit may comprise its own power supply and/or at least one electrical element of the power supply supplying power to only one of the RF and/or magnetic circuits. In addition, at least part of one source of energy supply can supply energy to at least two different circuits before and/or during at least part of the therapy. The power supply may include one or more parts shared with separate electrical circuits, which may be at least partially electrically isolated from one another.

[312] One or more electrical power supply elements for RF therapy (e.g., permanent magnetic circuit power supply (SPSM), auxiliary power supplies, APS A and/or APS B, power pump generator PP, on-board power supply, BPS A and /or BPS B) can deliver electricity to the individual electrical elements of the RF circuit and/or the magnetic circuit directly and/or indirectly. Directly supplied electrical power is delivered through a conductive connection between two electrical elements, with no other electrical element in the circuit in series connection between the directly supplied electrical elements. Insulation and/or other electrical components of circuits such as resistors, isolating capacitors, etc. may not be considered electrical components. Indirectly powered electrical elements may be powered by one or more other elements that deliver power through some other element configured to change power delivery parameters such as current value, frequency, phase, amplitude, and/or others.

[313] The power supply PSM, illustrated in more detail in FIG. 18a may comprise a connection to a power supply network PN. The PN may provide filtering and/or other adjustment of the input electrical signal from the power supply network, such as frequency and current value. The PN can also be used as an insulating element forming a barrier between the therapeutic device and the power supply network. The PN may include one or more capacitors, resistors, and/or filters that filter the signal returned from the therapeutic device. A PN may contain a connector or a connection to a connector. PN can be connected to a socket or power system. The PSM may comprise one or more permanent power supplies (eg permanent magnetic circuit power supply, SPSM), auxiliary power supplies (eg APS A and/or APS B), one or more power pump generators PP; and/or one or more on-board power supplies (eg, BPS A and/or BPS B). As shown in FIG. 18a, the therapeutic device may comprise at least two electrically isolated magnetic and/or RF circuits that can be controlled at least partially independently, for example, the intensity of the magnetic field generated by the magnetic field generating devices MFGD A and MFGD B may differ. , which are connected to the HIFEM A and HIFEM B magnetic therapy clusters. The constant power supply (SPSM) can provide a constant output voltage under different conditions of the power supply network. The permanent power supply SPSM may be connected to an auxiliary power supply (eg, APS A and/or APS B). Two auxiliary power supplies can be combined to form one electrical element. The DC output voltage generated by the DC power supply and/or auxiliary power supply may be in the range of 1 V to 1000 V, or 20 V to 140 V, or 50 V to 700 V, or 120 V to 500 V, or from 240 V to 450 V.

[314] One or more auxiliary power supplies can supply power to one or more individual circuit control units. The APS may power one or more on-board power supplies BPS, such as BPS A and/or BPS B. The APS may also power the HMI host and/or other elements of the therapy device. Due to the presence of the APS, at least one control unit and/or master unit can provide accurate independent processing/adjustment of the electrical signal in the RF and/or magnetic circuit, and/or also a separate electrical element of the therapeutic device can be protected from overload. An on-board power supply unit (eg, BPS A and/or BPS B element) can be used as a power source for at least one magnetic circuit element (eg, power storage device, ESD A and/or B). Alternatively, one or more elements of the power supply PSM may be combined and/or omitted.

[315] The power supply may serve as a high voltage generator supplying voltage to the magnetic circuit and/or the RF circuit. The voltage provided by the power supply may be in the range of 500 V to 50 kV, or 700 V to 5 kV, or 700 V to 3 kV, or 1 kV to 1.8 kV. The power supply is configured to deliver sufficient electricity to, for example, any electrical element (eg ESD A energy storage device) and magnetic field generating device (eg MFGD A). A device that generates a magnetic field can periodically generate a time-varying magnetic field with parameters sufficient to induce muscle contraction.

[316] Referring to FIG. 18a, the RF circuits comprise their own power supply PSRF, which may be at least partially different from the PSM. The PSRF may include an electrical PNFLT element that suppresses electromagnetic radiation from internal parts of the PN and/or from any part of the RF circuit. The PNFLT electrical element may be a power line filter. However, a PNFLT may also be part of a PN. The PSRF may comprise an SPSRF that delivers a constant output voltage under various power grid conditions to an RF auxiliary power supply, an APS RF, an RF circuit control unit, a power supply PU, and/or other electrical components that use a DC power supply. As further shown in FIG. 18a, the APS RF may contain its own mechanism to convert AC to DC independent of the SPSRF. The APS RF may be configured to power the therapeutic cluster control unit for RF therapy RF A and/or the master unit, while the SPSRF may independently power the therapeutic cluster control unit for RF therapy RF B. The RF circuit power supply unit PU may power one or more RF circuits or at least one electrical element of the RF circuit, such as power amplifiers and/or other electrical elements of RF therapy cluster RF A and/or RF therapy cluster RF B, generating and/or regulating high frequency signal.

[317] At least one electrical element described as PSM, PSRF, APS, SPSM and/or SPSRF can be used in conjunction with at least one RF circuit and a magnetic circuit.

[318] The control units CURF may act as a slave unit of the master unit, which may instruct the CURF to deliver the RF signal through the RF circuit to the RF electrode. In the case of two CURF control units, both control units act as slave units of the master unit, which can instruct both CURF units to deliver the RF signal to the respective RF electrodes. Therefore, the control of each control unit from the possible set of CURFs is independent. Alternatively, the first CURF may be a slave of the second CURF, while the first CURF itself may be a slave of the master. Therefore, when the host instructs the first CURF to discharge an electrical current into the first RF electrode, the first CURF may instruct the second CURF to discharge an electrical current into the second RF electrode located in the other applicator. In another alternative, an additional control unit may be located between the master unit and the plurality of control units CURF, whereby such an additional control unit may provide, for example, bit synchronization. Using both of these principles, RF field pulses can be applied in a synchronous or pulsed manner.

[319] Managing the magnetic therapy clusters HIFEM A and HIFEM B shown in FIG. 17, 18a and 18b can be done with one or more sliders or scroll controls associated with the HMI parts labeled HIFEM A and HIFEM B 718 shown in FIG. 7. Using the associated intensity scrollers, intensity bars, and/or intensity sliders on the HMI, the user can control the speed or adjust the speed of one or more electrical elements of the HIFEM A and/or HIFEM B magnetic therapy clusters.

[320] In addition, managing the therapeutic cluster for RF therapy RF A and the therapeutic cluster for RF therapy RF B, which are shown in FIG. 17, 18a and 18b can be done with sliders, bars or intensity scrollers associated with the HMI parts labeled RF A and RF B 712 shown in FIG. 7. Using the associated intensity scrolling elements, intensity bars and/or intensity sliders displayed on the HMI, the user can control the speed or adjust the speed of one or more electrical elements of the therapy clusters for RF therapy RF A and/or RF B Furthermore, using the associated intensity scrollers, intensity bars, and/or intensity sliders, the user can control the rate or speed of electrical signal transmission through or between one or more of the electrical elements of the therapeutic clusters for RF therapy RF A or RF B, or between them.

[321] The therapeutic device may comprise two or more applicators, with each applicator containing one magnetic field generating device and one or two RF electrodes. The inductance of the first magnetic field generating device located in the first applicator may be equal to the inductance of the second magnetic field generating device located in the second applicator. In addition, the number of turns, the area with winding and/or the area without winding of the first magnetic field generating device in the first applicator may be equal to the number, the area with winding and/or the area without winding of the second magnetic field generating device in the second applicator. The first magnetic field generating device in the first applicator may provide the same magnetic field as the second magnetic field generating device in the second applicator. Equal magnetic fields provided by a plurality of magnetic field generating devices during the same or different therapy sessions can be characterized by equal therapy parameters, for example, the number of pulses in a sequence, the number of pulses in a packet, equal amplitude of the magnetic flux density of single pulses, the same shape of the envelope, and others. However, a reasonable deviation is acceptable, for example, from the amplitude of the magnetic flux density in the same magnetic field. The amplitude deviation of the magnetic flux density or the average magnetic flux density when measured by a magnetic flux meter or an oscilloscope can be in the range from 0.1% to 10% or from 0.1% to 5%.

[322] Alternatively, the inductance of the magnetic field generating devices in both applicators may be different. In addition, the magnetic fields provided by a plurality of magnetic field generating devices during the same or different therapy sessions can be characterized by different therapy parameters.

[323] When a therapeutic device contains two or more applicators, each applicator may contain one magnetic field generating device and one or two RF electrodes. The size or area of one RF electrode located in the first applicator may be identical to another RF electrode located in the second applicator. The first applicator and the second applicator may provide the same RF fields delivered during the same or different therapy sessions, and the same RF fields may have the same therapy parameters such as wavelength, phase, time duration, and RF field intensity.

[324] Alternatively, the size and area of the RF electrodes in both applicators may be different. In addition, the magnetic fields provided by a plurality of magnetic field generating devices during the same or different therapy sessions can be characterized by different therapy parameters.

[325] FIG. 19 shows an exemplary composition of a magnetic field (eg, a time-varying magnetic field) provided by a magnetic field generating device. In addition, in FIG. 19 may also show the composition of the RF field. Therefore, in particular in the description of FIG. 19, the term "single pulse" may refer to "magnetic single pulse" or "RF single pulse". Likewise, the term "pulse" may refer to "magnetic pulse" or "RF pulse". In addition, the term "sequence" may refer to "magnetic sequence". The term "magnetic sequence" may include a sequence of magnetic pulses, whereby a sequence of magnetic pulses can be understood as a plurality of successive magnetic pulses in which one pulse follows another. Since a magnetic pulse may comprise a single unit pulse, the term "magnetic sequence" may also include a sequence of magnetic unit pulses. The term "package" may refer to "magnet package".

[326] As shown in FIG. 19, a single pulse may refer to a period of time applying therapy energy (e.g., a magnetic field) at an intensity sufficient to induce at least a partial therapeutic effect, e.g., at least partial contraction of a muscle, contraction of a muscle, temperature change of a biological structure, and/ or nerve stimulation. The magnetic single pulse may provide one biphasic waveform as shown in FIG. 19. The magnetic single pulse may provide for the amplitude of the magnetic flux density.

[327] A magnetic pulse may refer to a time span containing a single pulse and a passive time span of the pulse. The magnetic pulse can refer to the time span of one magnetic single pulse and the passive time span, i.e. the length of time between two single pulses from one edge/falling edge to the next edge/falling edge. Passive pulse duration may include both no application of therapy energy to the patient and/or application of therapy energy insufficient to elicit at least a partial therapeutic effect due to insufficient therapy energy intensity (e.g., magnetic flux density) and/or frequency. delivered energy for therapy. This period of time may be referred to as the pulse duration. As shown in FIG. 19, each pulse may provide one biphasic duration for a period of time referred to as the single pulse duration. Alternatively, the single pulses may be single phase.

[328] As further shown in FIG. 19, a plurality of pulses may form a sequence. A sequence may refer to a plurality of pulses, wherein one sequence may contain at least two pulses, and the pulses follow each other. The sequence may last for a period of time T ₁ as shown in FIG. 19.

[329] The magnetic sequence contains a plurality of magnetic pulses ranging from 2 magnetic pulses to 200,000 magnetic pulses, or from 2 magnetic pulses to 150,000 magnetic pulses, or from 2 magnetic pulses to 100,000 magnetic pulses. The magnetic sequence may cause several at least partial muscle contractions or muscle contractions following one another, at least one incomplete muscle spasm contraction, at least one supramaximal contraction, or at least one complete tetanic muscle contraction. During the application of one sequence, the magnetic field can provide one contraction of the muscle, followed by relaxation of the muscle. During the application of one sequence, muscle relaxation may be followed by another muscle contraction. During one sequence, the muscle cycle (which may include muscle contraction followed by muscle relaxation) may be repeated at least two, three, four, or more times.

[330] The package may refer to a single sequence delivered over a period of time, T ₁ , and a period of time, T ₂ , which may represent a period of time when no therapeutic effect is elicited. The period of time, T ₂ , may be a period of time providing passive therapy when therapy energy is not being applied to the patient's body and/or the therapy energy being applied is not sufficient to produce a therapeutic effect. The period of time, T ₃ , shown in FIG. 19 may represent the burst time duration.

[331] The magnetic sequence of a time-varying magnetic field may be followed by a static magnetic field, and/or the magnetic sequence may be followed by a time-varying magnetic field with a frequency and/or magnetic flux density insufficient to cause at least partial muscle contraction or contraction. muscles. For example, the packet may provide at least one at least partial muscle contraction followed by no muscle contraction. In another example, the packet may provide at least one muscle contraction followed by no muscle contraction. The therapy may include a number of magnetic packs in the range of 15 to 25,000, or in the range of 40 to 10,000, or in the range of 75 to 2,500, or in the range of 150 to 1,500, or in the range of 300 to 750, or up to 100,000. in subsequent bursts, it can progressively increase/decrease in increments of 1 Hz to 200 Hz, or 2 Hz to 20 Hz, or 5 Hz to 15 Hz, or more than 5 Hz. Alternatively, the amplitude of the magnetic flux density may vary in subsequent bursts such that it progressively increases/decreases in increments of at least 1%, 2%, 5%, or more relative to the frequency of the previous pulses. During the application of one packet, the magnetic field can provide one muscle contraction followed by muscle relaxation. During the application of one packet, muscle relaxation may be followed by another muscle contraction. During one packet, the cycle of muscle work (which may include contraction of the muscle followed by relaxation of the muscle) may be repeated at least two, three, four, or more times.

[332] In addition, with the use of pulsed magnetic field energy for therapy, the therapy duty cycle depicted in FIG. 19. The therapy duty cycle may refer to the ratio between active therapy time T ₁ and the sum of active and passive therapy time in one cycle, T ₃ .

[333] An exemplary therapy fill factor is depicted in FIG. 19. A duty factor of 10% means that T ₁ active therapy lasts 2 s and passive therapy T ₂ lasts 18 s. In this therapy example, the period including the active and passive therapy period, T ₃ , is 20 seconds long. The therapy fill factor can be defined as the ratio between T ₁ and T ₃ . The therapy fill factor can range from 1:100 (meaning 1%) to 24:25 (meaning 96%), or from 1:50 (meaning 2%) to 4:6 (meaning 67%), or 1:50 (meaning 2%) to 1:2 (meaning 50%), or 1:50 to 1:3 (meaning 33%), or 1:50 (meaning 2%) to 1:4 (meaning 25%), or 1:20 (meaning 5%) to 1:8 (meaning 12.5%), or 1:100 (meaning 1%) to 1:8 ( which means 12.5%), or at least 1:4 (which means 25%).

[334] An exemplary application of a burst rate of 4 Hz may be a time-varying magnetic field applied to a patient at a repetition rate of 200 Hz and a duty cycle of 50% therapy in sequences lasting 125 ms, i. each sequence contains 25 pulses. An alternative exemplary application of a packet repetition rate of 6 packets per minute could be a time-varying magnetic field applied to the patient at a repetition rate of 1 Hz and a duty cycle of 30% therapy in sequences lasting 3 seconds, i.e. each sequence contains 3 pulses.

[335] FIG. 19 also shows an exemplary composition of the magnetic component delivered by the RF electrode.

[336] When a plurality of applicators (eg, two) are used in a therapeutic device, each applicator may contain one device that generates a magnetic field. Since each magnetic field generating device may provide one corresponding magnetic field, multiple applicators may contain different magnetic fields. In this case, the amplitude of the magnetic flux density of the magnetic single pulses or pulses may be the same or different, as indicated by the user using the HMI and/or one or more control units.

[337] Single pulses of one magnetic field provided by one magnetic field generating device (eg, a magnetic coil) may be generated and applied in synchronism with single pulses of another magnetic field provided by another magnetic field generating device. During a therapy session with a therapeutic device comprising two magnetic field generating devices, unit pulses of one magnetic field provided by one magnetic field generating device may be generated in synchronism with single pulses of a second magnetic field provided by another magnetic field generating device. Synchronous generation may include simultaneous generation.

[338] Synchronous generation of magnetic single pulses can be achieved by synchronous operation of switches, energy storage devices, magnetic field generating devices, and/or other electrical elements of a plurality of magnetotherapy circuit elements. However, the synchronous operation of the electrical elements of the magnetotherapy circuit can be programmed, adjusted or controlled by the user using an HMI, a master unit and/or several control units.

[339] FIG. 27a shows the simultaneous type of synchronous generation of magnetic pulses by two exemplary magnetic field generating devices. The magnetic field generating device A (MFGD A) may generate a first magnetic field including a plurality of two-phase magnetic single pulses 271a. Magnetic field generating device B (MFGD B) can generate a second magnetic field including a plurality of magnetic single pulses 271b. The magnetic single pulses of both magnetic fields are generated for a duration of 272 single pulses of the magnetic single pulses 271a of the first magnetic field. In addition, single pulses of both magnetic fields are generated during the duration of 273 single pulses of the first magnetic field. Simultaneous generation of the magnetic field means that the magnetic unit pulse 271a of the first time-varying magnetic field is generated at the same time as the magnetic unit pulse 271b of the second time-varying magnetic field.

[340] Synchronous generation of magnetic fields may include generating the first pulse of the first time-varying magnetic field such that the first pulse lasts for a period of time, and this period of time lasts from the beginning of the first unit pulse of the first time-varying magnetic field to the beginning of the next order of the unit pulse of the first time-varying magnetic field, and generating the second pulse of the second time-varying magnetic field by the second magnetic field-generating device such that the second pulse lasts from the beginning of the first unit pulse of the second time-varying magnetic field to the start of the next unit pulse in order pulse of the second time-varying magnetic field. Synchronous magnetic field generation means that the first single pulse of the second time-varying magnetic field is generated during the time span of the first pulse.

[341] In FIG. 27b shows an example of synchronous generation of magnetic single pulses. The magnetic field generating device A (MFGD A) may generate a first magnetic field including a plurality of two-phase magnetic single pulses 271a. Magnetic field generating device B (MFGD B) can generate a second magnetic field including a plurality of magnetic single pulses 271b. Magnetic single pulses 271b of the second magnetic field may be generated during the duration 273 of the pulse of the first magnetic field, but beyond the duration 272 of the single pulse of the first magnetic field.

[342] FIG. 27c shows another example of the synchronous generation of magnetic pulses. The magnetic field generating device A (MFGD A) may generate a first magnetic field including a plurality of two-phase magnetic single pulses 271a. Magnetic field generating device B (MFGD B) can generate a second magnetic field including a plurality of magnetic single pulses 271b. Magnetic single pulse 271b of the second magnetic field can be generated during the duration of 273 pulses of the first magnetic field. In addition, the magnetic single pulse 271b of the second magnetic field can be generated during the duration 272 of the single pulse for the pulse of the first magnetic field. The beginning of the magnetic single pulse 271b of the second magnetic field can be relative to the beginning of the single pulse 271a of the first magnetic field at a distance of a time interval called the shift 274 of the single pulse. The single pulse shift can range from 51 to 10 ms, or from 5 µs to 1000 µs, or from 1 µs to 800 µs.

[343] FIG. 27d shows another example of synchronous generation of magnetic unit pulses. The magnetic field generating device A (MFGD A) may generate a first magnetic field including a plurality of two-phase magnetic single pulses 271a. Magnetic field generating device B (MFGD B) can generate a second magnetic field including a plurality of magnetic single pulses 271b. The magnetic single pulse 271b of the second magnetic field can be generated within the duration 273 of the pulse of the first magnetic field. The magnetic single pulse 271b of the second magnetic field may be generated beyond the duration 272 of the single pulse of the first magnetic field. The beginning of the magnetic unit pulse 271b of the second magnetic field may be located relative to the end of the magnetic unit pulse 271a of the first magnetic field at a distance of a period of time called the period 275 of the distance of the unit pulse. The single pulse distance period may be in the range of 51 to 10 ms, or 5 µs to 1000 µs, or 1 µs to 800 µs.

[344] In addition to synchronous generation, magnetic unit pulses of a plurality of magnetic fields can be generated separately. Generating magnetic single pulses of magnetic fields separately may include generating single pulses of one magnetic field outside the pulse duration of another magnetic field.

[345] FIG. 27e shows an example of generating magnetic single pulses separately. The magnetic field generating device A can generate a first magnetic field including a plurality of two-phase magnetic unit pulses 271a having a unit pulse duration 272a. Each magnetic single pulse 271a is part of a pulse characterized by a pulse duration 273a. The duration 272a of the single pulse of the first magnetic field may be part of the duration 273a of the first magnetic field pulse. The sequence of the first magnetic field may be characterized by a duration of 276a of the sequence. The magnetic field generating device B may generate another magnetic field including a different sequence of a plurality of magnetic unit pulses 271b having a unit pulse duration of 272b. Each magnetic single pulse 271b is part of a pulse characterized by a pulse width 273b. The duration 272b of a single pulse of the second magnetic field may be part of the duration 273b of the pulse of the second magnetic field. The sequence of the second magnetic field may be characterized by a duration of 276b sequence. The sequence characterized by the sequence length 276a is generated by the magnetic field generating device A at a time different from the sequence characterized by the sequence duration 276b which is generated by the magnetic field generating device B. Both sequences may be separated by a separation period 277 which may range from 1 ms to 30 s. During the separation period 277, no magnetic field generating device may be active, which means that the power storage device providing current pulses may not store energy.

[346] All examples of synchronous or separate generation of magnetic single pulses can be used during one therapy session. In addition, the unit pulse shift and/or the period of the distance between the units may be calculated for any magnetic unit pulse 271b of the second or other magnetic field, which may be located in accordance with any of the examples shown in FIG. 27B-27E. The unit pulse shift and/or the period of distance between units can be measured and calculated based on the measurement with an oscilloscope. The synchronous generation of magnetic pulses can lead to and extrapolate to the synchronous generation of magnetic pulses and/or sequences by two or more magnetic field generating devices. Likewise, the separate generation of magnetic pulses can lead to and extrapolate to the synchronous generation of magnetic pulses and/or sequences by two or more magnetic field generating devices.

[347] For the formation or formation of a magnetic envelope or RF envelope, you can use the adjustment or control provided by the master unit and/or one or more control units. For example, magnetic single pulses or RF single pulses of each single pulse or multiple single pulses can be amplitude-modulated to provide different envelopes. Similarly, the amplitude of the RF energy can be modulated in amplitude to form different envelopes. The master block and/or one or more control blocks may be configured to generate one or more of the envelopes described herein. Magnetic envelopes and/or RF envelopes of various shapes (also referred to herein as envelopes) may be perceived differently by the patient. The envelope (or all of the envelopes shown in the figures in this application) may be a curve fitted by the amplitude of the magnetic flux density of the single pulses, pulses or sequences and/or the amplitudes of the RF power output of the single pulses of RF waves.

[348] The envelope may be a magnetic envelope formed from magnetic single pulses. The magnetic envelope formed from the single pulses may comprise a plurality of single pulses, eg at least two, three, four or more consecutive magnetic single pulses. Successive magnetic single pulses of such a magnetic envelope can follow each other. In the case of such an envelope, the duration of the envelope may begin with the first single pulse and end with the last single pulse of the plurality of single pulses. The envelope can contain one sequence of magnetic single pulses. The envelope may be a curve fitted by the amplitudes of the magnetic flux density of the unit pulses. Therefore, the envelope formed by the magnetic single pulses can determine the shape of the sequence in accordance with the modulation of the magnetic flux density, repetition rate and/or the duration of a single pulse of magnetic single pulses. Accordingly, the envelope may be an RF envelope formed by RF pulses and their modulation of the RF pulse envelope, repetition rate, or RF pulse width of the RF wave.

[349] The envelope may be a magnetic envelope formed by magnetic pulses. The magnetic envelope formed by the pulses may comprise a plurality of pulses (eg, at least two, three, four or more consecutive magnetic pulses), with the pulses following each other without any missed pulses. In this case, the duration of the envelope may begin with a single pulse of the first pulse and end with a passive time duration of the last single pulse of the plurality of pulses. Therefore, the envelope formed by the magnetic pulses can determine the shape of the sequence in accordance with the modulation of the magnetic flux density, repetition rate and/or duration of a single pulse. The envelope can contain one sequence of magnetic pulses. The sequence consists of magnetic pulses in a pattern that is repeated at least twice during the course of the protocol. The magnetic envelope may be a curve fitted by the pulse magnetic flux density amplitudes.

[350] The envelope may be a magnetic envelope formed from magnetic sequences. The magnetic envelope formed from the sequences may comprise a plurality of sequences (eg, at least two, three, four, or more consecutive magnetic sequences), with the sequences following one another with some time duration between the sequences. In this case, the duration of the envelope may begin with a single pulse of the first pulse of the first sequence and end with a passive time duration of the plurality of pulses. Multiple sequences in one envelope can be separated by missing pulses containing single pulses. The number of skipped pulses can range from 1 to 20 or 1 to 10.

[351] the Envelope can be modulated by different values of the offset magnetic flux density. The offset value can be in the range of 0.01T to 1T, or 0.1T to 1T, or 0.2T to 0.9T. The offset value may correspond to a non-zero value of the magnetic flux density.

[352] During a single therapy session, a therapeutic device may apply a different number of envelopes. Two or more magnetic field envelopes can be combined to form a possible resulting shape.

[353] In the above examples, the envelope may start from the first single pulse. In addition, the envelope is continued by the duration of the first corresponding pulse containing the first unit pulse. In addition, the envelope may end with a passive time duration of the last pulse, whereby the last pulse may follow the first pulse. This possibility is shown in the following figures, which show exemplary magnetic pulse envelope shapes. As shown in the following figures, the shape of the envelope can be provided by modulating the magnetic flux density. The shape of the RF envelope can be provided by modulating the power amplitude or single pulses of RF waves.

[354] FIG. 28 is an exemplary depiction of an ascending envelope 281 formed from magnetic spikes 282, with one magnetic spike 282 followed by one passive magnetic pulse time period. The amplitude of the magnetic flux density of successive single pulses in an increasing envelope increases. The amplitude of the magnetic flux density of one single pulse is higher than the amplitude of the magnetic flux density of the previous single pulse. Similarly, the amplitude of the magnetic flux density of the second single pulse is higher than the amplitude of the magnetic flux density of the first single pulse. Increasing amplitude can be used to prepare the muscle. The duration 283 of the rising envelope 281 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. Similarly, the amplitude of the RF waves can be modulated in amplitude to form a rising envelope 281.

[355] FIG. 29 is an exemplary depiction of a decaying envelope 291 formed from magnetic single pulses 292. The magnetic flux density amplitude of successive single pulses in the decaying envelope decreases. The amplitude of the magnetic flux density of one single pulse is lower than the amplitude of the magnetic flux density of the previous single pulse. Similarly, the amplitude of the magnetic flux density of the second single pulse is lower than the amplitude of the magnetic flux density of the first single pulse. The duration 293 of the decaying envelope 291 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. Likewise, the amplitude of the RF waves can be modulated in amplitude to form a decaying envelope 291 .

[356] FIG. 30 is an illustrative representation of a rectangular envelope 302 formed from magnetic single pulses 303. The amplitude of the magnetic flux density of the unit pulses in the rectangular envelope may be constant. However, the amplitude of the magnetic flux density of successive single pulses may fluctuate around a predetermined value of the amplitude of the magnetic flux density in the range from 0.01% to 5%. The amplitude of the magnetic flux density of the first single pulse may be equal to the amplitude of the magnetic flux density of the second single pulse, with the second single pulse following the first single pulse. The duration 304 of the rectangular envelope 302 starts from the first single pulse of the first pulse until the end of the passive time period of the last pulse. The rectangular envelope can be used to induce muscle contraction or muscle twitching. Similarly, to form a rectangular envelope 302, the amplitude of the RF waves can be modulated in amplitude.

[357] FIG. 31 is an illustrative representation of a combined envelope 311, which can be thought of as a combination of a rising envelope and a rectangular envelope. The combined envelope 311 contains magnetic single pulses 312. The amplitude of the magnetic flux density of the single pulses in the combined envelope may be increasing in the range of 1% to 95%, or 5% to 90%, or 10% to 80% of the time duration of the entire combined envelope. The amplitude of the magnetic flux density of successive single pulses in the rectangular part of the combined envelope can fluctuate around a predetermined value of the amplitude of the magnetic flux density in the range from 0.01% to 5%. The duration 313 of the combined envelope 311 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. The combined envelope shown in Fig. 31 can be used to prepare the muscle and induce muscle contraction or muscle twitches. Similarly, the amplitude of the RF waves can be modulated in amplitude to form the envelope 311.

[358] FIG. 32 is an illustrative representation of a combined envelope 321, which can be thought of as a combination of a rectangular envelope and a decaying envelope. The combined envelope 321 contains magnetic single pulses 322. The amplitude of the magnetic flux density of the single pulses in the combined envelope may be decreasing in the range from 1% to 95%, or from 5% to 90%, or from 10% to 80% of the time duration of the entire combined envelope. The amplitude of the magnetic flux density of successive single pulses in the rectangular part of the combined envelope can fluctuate around a predetermined value of the amplitude of the magnetic flux density in the range from 0.01% to 5%. The duration 323 of the combined envelope 321 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. The combined envelope shown in Fig. 32 can be used to induce muscle contraction or muscle twitches and then complete muscle stimulation. Similarly, to form the combined envelope 321, the amplitude of the RF waves can be modulated in amplitude.

[359] FIG. 33 is an illustrative representation of a triangular envelope 331, which can be understood as a combination of an ascending envelope immediately followed by a descending envelope. The triangular envelope 331 may include magnetic spikes 332. The triangular shape of the envelope may not be symmetrical. In addition, the straightness of one or more triangular shaped lines may be interrupted by another type of envelope mentioned herein, such as a rectangular envelope. One triangular envelope can follow directly another triangular envelope or be connected to another triangular envelope. When connecting two triangular envelopes, the resulting envelope can have a sawtooth shape. The duration 333 of the triangular envelope 331 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. Similarly, to form a triangular envelope 331, the amplitude of the RF waves can be modulated in amplitude.

[360] FIG. 34 is an exemplary depiction of a trapezoidal envelope 341. Trapezoidal envelope 341 may comprise magnetic spikes 342. The trapezoidal envelope may comprise a rise (rise) time period, T _R , a soak time period, T _H , and a fall (fall) time period, T _F . During the rise time period, the amplitude of the magnetic flux density of successive single pulses increases. In addition, during the period of time of increase, the amplitude of the magnetic flux density of one single pulse is higher than the amplitude of the magnetic flux density of the previous single pulse. During the dwell time, the amplitude of the magnetic flux density of successive single pulses may fluctuate around a predetermined value of the amplitude of the magnetic flux density in the range from 0.01% to 5%. During the decay time period, the amplitude of the magnetic flux density of successive single pulses decreases. In addition, during the decay time period, the amplitude of the magnetic flux density of one single pulse is lower than the amplitude of the magnetic flux density of the previous single pulse. The soak period may be interrupted by another soak time period which is characterized by a different predetermined magnetic flux density value. The duration 343 of the trapezoidal envelope 341 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. Similarly, to form a trapezoidal envelope 341, the amplitude of the RF waves can be modulated in amplitude.

[361] The trapezoidal envelope may be perceived by the patient as the most comfortable for stimulating muscle tissue. Trapezoidal envelope refers to the natural course of muscle contraction, i.e. muscle contraction may be time-varying. The strength of the natural contraction of the muscle increases, is maintained at the highest value, and decreases. The trapezoidal envelope corresponds to the natural contraction of the muscle, i.e. the muscle contraction force can correspond to the magnetic flux density. The magnetic flux density during the duration of the trapezoidal envelope increases, persists and decreases. The same shape of the envelope can be characterized by an RF electrode formed from RF single pulses, characterized by the corresponding amplitude.

[362] The trapezoidal envelope may be interrupted at least once by one or more single pulses, pulses, bursts, and/or sequences that do not conform to the shape of the trapezoidal envelope, but after this interruption, the trapezoidal envelope may continue.

[363] In addition, the trapezoidal envelope may contain multiple sequences, such as two, three, four or more sequences. In the case of a trapezoidal envelope, the envelope can contain three sequences. The first sequence may contain single pulses with increasing magnetic flux density. The magnetic flux density of one single pulse may be higher than the magnetic flux density of the second single pulse following the first single pulse. The second sequence contains single pulses with a constant magnetic flux density. However, the operation of the therapeutic device may not provide an exactly constant magnetic flux density for each single pulse, so the magnetic flux density may fluctuate in the range from 0.1% to 5%. The third sequence may contain single pulses with decreasing magnetic flux density. The magnetic flux density of one single pulse may be lower than the magnetic flux density of the second single pulse following the first single pulse.

[364] In addition, the trapezoidal envelope may contain multiple packets, such as two, three, four or more packets. In the case of a trapezoidal envelope, the envelope can contain three packets. The first packet may contain single pulses with increasing magnetic flux density. The magnetic flux density of one single pulse may be higher than the magnetic flux density of the second single pulse following the first single pulse. The second packet may contain single pulses with a constant magnetic flux density. However, the operation of the therapeutic device may not provide an exactly constant magnetic flux density for each single pulse, so the magnetic flux density may fluctuate in the range from 0.1% to 5%. The third packet may contain single pulses with decreasing magnetic flux density. The magnetic flux density of one single pulse may be lower than the magnetic flux density of the second single pulse following the first single pulse.

[365] FIG. 20 shows another exemplary trapezoidal envelope. The vertical axis may represent magnetic flux density and the horizontal axis may represent time. The trapezoidal envelope may be a curve fitted to the magnetic flux density amplitudes of the single pulses that are applied during the sequence, where T _R is the time period of magnetic flux density increase, referred to as the increase transient duration, i.e. the amplitude of the magnetic flux density may increase. T _H - time period of maximum magnetic flux density, i.e. the amplitude of the magnetic flux density may be constant. T _F is the time period of the decrease in the magnetic flux density, i.e. the amplitude of the magnetic flux density may decrease. The sum of T _R , T _H and T _F may be the duration of the trapezoidal envelope, which may correspond to muscle contraction.

[366] A trapezoidal envelope can reduce power consumption. Due to the lower power consumption, the trapezoidal shape may allow improved cooling of the magnetic field generating device. In addition, due to the lower temperature of the device generating the magnetic field, resistance losses can be reduced. Different repetition rates can cause different types of muscle contractions. Each type of muscle contraction can consume different amounts of energy.

[367] FIG. 35 is an exemplary depiction of a trapezoidal envelope 351 comprising a rise time period, T ₁ , a first fall time period, T ₂ , and a second fall time period, T ₃ . The trapezoidal envelope 351 contains magnetic single pulses 352. The rise time period contains single pulses with increasing magnetic flux density amplitude. The first decay time period and the second decay time period comprise single pulses with decreasing magnetic flux density amplitude. In the example shown, the first fall time period follows the rise time period and precedes the second fall time period. The magnetic flux density amplitude of successive single pulses is shown as decreasing more steeply during the second decay time period. Alternatively, the magnetic flux density amplitude of successive single pulses decays more steeply during the first decay time period. The duration 353 of the trapezoidal envelope 351 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. Accordingly, the envelope may be magnetic envelopes formed from RF single pulses. Similarly, to form a trapezoidal envelope 351, the amplitude of the RF waves can be modulated in amplitude.

[368] FIG. 36 is an exemplary depiction of a trapezoidal envelope 361 comprising a first rise time period, a second rise time period, and a fall time period. The trapezoidal envelope 361 comprises magnetic spikes 362. The first rise time period and the second rise time period contain single pulses with increasing magnetic flux density amplitude. The first rise time period and the second rise time period comprise single pulses with increasing magnetic flux density amplitude. In the example shown, the second rise time period follows the first rise time period and precedes the fall time period. The amplitude of the magnetic flux density of successive single pulses is shown as increasing more steeply during the first time period of the increase. Alternatively, the magnetic flux density amplitude of successive single pulses rises more steeply during the second rise time period. The duration 363 of the trapezoidal envelope 361 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. Similarly, to form a trapezoidal envelope 361, the amplitude of the RF waves can be modulated in amplitude.

[369] FIG. 37 is an illustrative representation of a stepped envelope 371 comprising a first rise time period, T ₁ , a first soak time period, T ₂ , a second rise time period, a second soak time period, and a fall time period. The stepped envelope 371 comprises magnetic spikes 372. During the first and second rise times, the amplitude of the magnetic flux density of successive spikes may increase. During the decay time period, the amplitude of the magnetic flux density of successive single pulses may decrease. During the holding time period, the amplitude of the magnetic flux density of successive single pulses may be constant or fluctuate around a predetermined value of the magnetic flux density amplitude in the range from 0.01% to 5%. The duration 373 of the stepped envelope 371 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. Similarly, the amplitude of the RF waves can be modulated in amplitude to form the stepped envelope 371.

[370] FIG. 38 is an illustrative representation of a stepped envelope 381 comprising a first rise time period, T ₁ , a first soak time period, T ₂ , a first fall time period, T ₃ , a second soak time period, T ₄ , and a second fall time period, T ₅ . Stepped envelope 381 comprises magnetic spikes 382. During the rise time period, the amplitude of the magnetic flux density of successive spikes may increase. During the first and second decay time periods, the amplitude of the magnetic flux density of successive single pulses may decrease. During the holding time period, the amplitude of the magnetic flux density of successive single pulses may be constant or fluctuate around a predetermined value of the magnetic flux density amplitude in the range from 0.01% to 5%. The duration 383 of the stepped envelope 381 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. Similarly, the amplitude of the RF waves can be modulated in amplitude to form the envelope 381.

[371] FIG. 39 is an exemplary view of another type of trapezoidal envelope 391 containing magnetic spikes 392. The trapezoidal envelope may comprise a rise time period, T ₁ , a dwell time period, T ₂ , and a fall time period, T ₃ . During the rise time period, the amplitude of the magnetic flux density of successive single pulses increases. In addition, during the period of time of increase, the amplitude of the magnetic flux density of one single pulse is higher than the amplitude of the magnetic flux density of the previous single pulse. During the dwell time, the amplitude of the magnetic flux density of successive single pulses may fluctuate around a predetermined value of the amplitude of the magnetic flux density in the range from 0.01% to 5%. During the decay time period, the amplitude of the magnetic flux density of successive single pulses decreases. In addition, during the decay time period, the amplitude of the magnetic flux density of one single pulse is lower than the amplitude of the magnetic flux density of the previous single pulse. The soak period may comprise another soak time period, T ₄ , characterized by a different predetermined magnetic flux density value. The duration 393 of the envelope 391 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. Similarly, to form the envelope 391, the amplitude of the RF waves and/or RF pulses can be modulated in amplitude.

[372] The envelope may comprise a combined modulation of magnetic flux density and repetition rate. In FIG. 40 shows an illustrative representation of a rectangular envelope 401 with a constant magnetic flux density amplitude. Rectangular envelope 401 may include magnetic spikes 402. The time periods T _RR2 and T _RR3 show the bursts having a higher repetition rate than the rest of the magnetic spikes during T _RR1 of the rectangular envelope shown. The time periods T _RR2 and T _RR3 shown may provide stronger muscle contraction than the remaining time periods in the shown rectangular envelope. However, all of the envelopes shown may contain modulation in the repetition rate region. The duration 403 of the rectangular envelope 401 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. Accordingly, the envelope may be magnetic envelopes formed from RF single pulses. Their amplitude can also form an amplitude called the RF envelope. Similarly, to form the envelopes 401, the amplitude and/or repetition frequency RF of the unit pulses can be modulated in amplitude.

[373] As mentioned, the envelope may be formed from magnetic sequences separated by one or more missed pulses. In FIG. 41 shows an envelope formed from magnetic sequences containing magnetic pulses 412. As shown, the first sequence containing a sequence of single pulses with increasing magnetic flux density has a duration T ₁ . The second sequence, containing single pulses with a constant or fluctuating magnetic flux density, is characterized by a duration T ₂ . The third sequence, containing single pulses with decreasing magnetic flux density, is characterized by duration T ₃ . The envelope 411 containing a plurality of sequences is characterized by a trapezoidal shape. The lengths of time between the durations T ₁ and T ₂ or the durations T ₂ and T ₃ may represent time intervals in which missed pulses containing missed single pulses could be located. The duration 413 of the envelope 411 starts from the first single pulse of the first pulse to the end of the passive time duration of the last pulse. Similarly, the amplitude of the RF waves or RF pulses can be modulated in amplitude to form the envelopes 411.

[374] During therapy, magnetic envelopes can be combined. In FIG. 42 shows an example of a combination of magnetic envelopes. Increasing envelope 422, characterized by an increasing shape, contains a sequence of magnetic single pulses 421. Increasing envelope 422 may be characterized by a duration T _E1 . Rectangular envelope 423 contains a sequence of magnetic single pulses 421. Rectangular envelope may be characterized by a duration T _E2 . Decreasing envelope 424 contains a sequence of magnetic single pulses 421. Decreasing envelope 424 may be characterized by a duration T _E3 . The resulting sub-period of a therapy protocol formed by combining the first, second, and third envelopes may provide the same or similar therapeutic effect as the trapezoidal envelope shown, for example, in FIG. 34 and FIG. 20. The resulting sub-period of the therapy protocol is characterized by a duration of 425 from the first single pulse of the first pulse to the end of the passive time duration of the last pulse of the therapy sub-period. Similarly, the amplitude of the RF waves and/or RF single pulses can be modulated in amplitude to form a combination of envelopes.

[375] FIG. 43 shows another example of a combination of magnetic envelopes, in which the decay period is characterized by a magnetic flux density other than a rectangular envelope. This example can show that a combination of magnetic envelopes can provide envelopes with different magnetic flux densities. An ascending envelope 432, characterized by an ascending shape, contains a sequence of magnetic single pulses 431. The ascending envelope may be characterized by a duration T _E1 . Rectangular envelope 433 contains a sequence of magnetic single pulses 431. Rectangular envelope may be characterized by a duration T _E2 . The decaying envelope contains a sequence of magnetic single pulses 431. The decaying envelope 434 may be characterized by a duration T _E3 . The resulting sub-period of a therapy protocol formed by combining the first, second, and third envelopes may provide the same or similar therapeutic effect as the trapezoidal envelope shown, for example, in FIG. 34 and FIG. 20. The resulting sub-period of the therapy protocol is characterized by a duration of 435 from the first single pulse of the first pulse to the end of the passive time duration of the last pulse of the therapy sub-period. Similarly, the amplitude of RF waves or RF single pulses can be modulated in amplitude to form a combination of envelopes.

[376] FIG. 44 shows two exemplary magnetic field envelopes with an example of a period between the envelopes, i.e. time period between envelopes. The period of time between the envelopes may include the time of absence of magnetic stimulation. However, the time period between the envelopes may contain magnetic spikes providing insufficient or unrecognized muscle stimulation (including, for example, muscle contraction and muscle relaxation). Magnetic spikes generated during the period of time between envelopes can also form an envelope. Magnetic spikes providing insufficient or unrecognized muscle stimulation can be generated by discharging the energy storage device into a magnetic field generating coil to discharge the residual capacity. The power storage device may then be charged by the power supply to a higher electric current and/or voltage to provide the magnetic field generating device with single high power current pulses. A rectangular envelope 442, characterized by a duration T ₁ , may contain magnetic peaks 441. A trapezoidal envelope 444, characterized by a duration T ₂ , may contain magnetic peaks 441. The time period between envelopes, characterized by a duration T _EP , may contain an envelope 443 (for example, having decreasing shape) given by the magnetic flux density of the magnetic unit pulses 441 within the time period between the envelopes. Alternatively, the period of time between envelopes may comprise single pulses providing muscle twitches. Accordingly, the envelope may be magnetic envelopes formed from RF single pulses. Their amplitude can also form an amplitude called the RF envelope. The period of time between the RF envelopes may include a no heat time.

[377] RF therapy (RF field) can generate a source of therapeutic energy (eg, RF electrode) in continuous action, pulse action or action, including cycles. Continuous action is ensured during continuous RF therapy. Impulse action is provided during impulse RF therapy.

[378] During the continuous action of the RF electrode may generate an RF field for the entire therapy or a single duration during therapy on command from the master unit of one or more control units. The RF electrode can generate an RF wave having a sinusoidal shape. In other words, the RF electrode can generate a radio frequency waveform characterized by a sinusoidal waveform. According to the amplitudes of the RF wave, other shapes are possible, such as sawtooth, triangular or square.

[379] Continuous RF therapy may have one of the highest synergistic effects with the provision of magnetotherapy due to the continuous heating of the target biological structures of the patient, the highest polarization effect of the patient's biological structures, and the deep penetration of the magnetic field and the strong influence of the magnetic field on the patient's tissue to promote muscle contraction.

[380] In the course of pulsed RF generation, the electrode may generate an RF field for two or more active time periods of therapy, and these time periods may be separated by passive time periods. The active time period of the pulsed RF therapy may represent a period of time during which the RF electrode is active and generates an RF field. The active time period may range from 1 s to 15 minutes, or from 30 s to 10 minutes, or from 5 s to 900 s, or from 30 s to 300 s, or from 60 s to 360 s. The passive time period of pulsed RF therapy may represent a period of time during which the RF electrode is inactive and does not generate an RF field. The passive time period of the pulsed RF therapy may range from 1 s to 15 minutes, or from 10 s to 10 minutes, or from 5 s to 600 s, or from 5 s to 300 s, or from 10 s to 180 s. During therapy, the generation of impulses and its parameters may change.

[381] The user can select, control, or regulate various therapy protocols of the therapeutic device using the control unit or the master unit of the therapeutic device. In addition, the master unit and/or the control unit may select, manage, or regulate body area therapy protocols or another option selected by the user. Additionally, the master unit and/or the control unit may select, control or regulate various therapy parameters in accordance with the feedback provided by any of the above sensors.

[382] A therapy protocol may comprise a selection of one or more therapy parameters and their predetermined values assigned to the respective protocol. In addition, the therapy protocol may contain various types of combined therapy in the form of magnetotherapy and RF therapy.

[383] With regard to therapy parameters, a user may control or adjust various therapy parameters of the therapeutic device using a control system comprising a master unit or one or more control units of the therapeutic device. The master unit and/or control unit may control or adjust therapy parameters in accordance with the therapy protocol, body region, or other capability selected by the user. Additionally, the master unit and/or the control unit may control or regulate various therapy parameters in accordance with the feedback provided by any of the aforementioned sensors. The master unit or one or more control units can provide adjustment of magnetic field therapy parameters, including magnetic flux density, magnetic flux density amplitude, single pulse duration, pulse width, single pulse repetition rate, pulse repetition rate, sequence duration, number of single pulses. and/or pulses in the sequence, the duration of the package, the composition of the magnetic package, the composition of the magnetic sequence, the number of envelopes, the duty cycle, the shape of the envelopes and/or the maximum derivative of the magnetic flux density. The master unit or one or more control units may provide adjustment of RF field therapy parameters, including RF field frequencies, RF field duty cycle, RF field intensity, energy flow provided by the RF field, RF field power, RF field power amplitude, and/or the power amplitude of the RF waves, wherein the RF waves may refer to the electrical component of the RF field. Therapy parameters can be controlled or adjusted within the following ranges.

[384] Additionally, therapy parameters may include, for example, therapy time, magnetic field generating device temperature, RF electrode temperature, applicator temperature, cooling tank temperature, target body area selection, number of applicators attached, cooling fluid temperature (measured in conduit fluid, connecting tube, applicator or cooling container with an appropriate temperature sensor), a selected area of the body and / or others.

[385] Different magnetic flux density, pulse duration, composition of sequences and/or packages can have different effects on muscle tissue. One part of magnetotherapy can induce, for example, muscle training to increase muscle strength, muscle volume, muscle tone, and other parts of magnetotherapy can cause muscle relaxation. The signal provided by the RF electrode can be modulated with respect to the capacitance of the circuit formed by the two bipolar RF electrodes and the patient's body, preventing the generation of standing RF waves in the applicator and/or the patient's body, or other. The RF field modulation can be provided in the frequency domain, intensity domain, pulse width, and/or other parameters. The goal of a single radiofrequency therapy, magnetotherapy and/or their combination is to achieve the most comprehensive and/or effective therapy of the target biological structure. Time domain modulation can provide active and passive periods of stimulation. A dormant period may occur when the RF therapy and/or magnetotherapy includes a period of no muscle stimulation and/or no change in temperature or other therapeutic effect provided by the RF field in the target biological structure. During the dormant period, no magnetic field and/or RF field may be generated. In addition, during the dormant period, a magnetic field and an RF field may be generated, but the intensity of the magnetic field and/or RF field may not be sufficient to provide a therapeutic effect in at least one of the target biological structures.

[386] The magnetic flux density of the magnetic field may be in the range of 0.1 T to 7 T, or in the range of 0.5 T to 7 T, or in the range of 0.5 T to 5 T, or in the range of 0, 5 T to 4 T, or in the range of 0.5 T to 2 T. This definition may include the amplitude of the magnetic flux density of the magnetic field. The magnetic flux density ranges shown can be used to induce muscle contraction. The magnetic flux density and/or the amplitude of the magnetic flux density can be measured using a flux meter or an oscilloscope.

[387] The repetition rate may refer to the triggering frequency of the magnetic unit pulses. The repetition rate can be obtained from the time duration of the magnetic pulse. The frequency of repetition of magnetic single pulses can be in the range from 0.1 Hz to 700 Hz, or from 1 Hz to 700 Hz, or from 1 Hz to 500 Hz, or in the range from 1 Hz to 300 Hz, or from 1 Hz to 150 Hz . If each magnetic pulse contains one magnetic unit pulse, the magnetic pulse repetition frequency is equal to the magnetic unit repetition frequency. The duration of magnetic single pulses can be in the range from 1 µs to 10 µs, or from 3 µs to 3 ms, or from 3 µs to 3 ms, or from 3 µs to 1 ms, or from 10 µs to 2000 µs, or from 50 µs up to 1000 µs, or from 100 µs to 800 µs. The pulse repetition rate can be measured by recording measurements with an oscilloscope.

[388] The sequence duration can range from 1 ms to 300 s, or from 1 ms to 80 s, or from 2 ms to 60 s, or from 4 ms to 30 s, or from 8 ms to 10 s, or from 25 ms to 3 s. The time between two successive sequences can range from 5 ms to 100 s, or from 10 ms to 50 s, or from 200 ms to 25 s, or from 500 ms to 10 s, or from 750 ms to 5 s, or from 300 ms to 20 s. The repetition rate can be measured by recording measurements with an oscilloscope.

[389] The burst duration may range from 10 ms to 100 seconds, or from 100 ms to 15 s, or from 500 ms to 7 s, or from 500 ms to 5 s. The repetition rate may be in the range of 0.01 Hz to 150 Hz, or 0.02 Hz to 100 Hz, or in the range of 0.05 Hz to 50 Hz, or 0.05 Hz to 10 Hz, or 0, 05Hz to 2Hz. The repetition rate can be measured by recording measurements with an oscilloscope.

[390] Another parameter for providing magnetotherapy and inducing muscle contraction is the derivative of the magnetic flux density, which has the form dB/dt , where: dB is the derivative of the magnetic flux density [T] and dt is the derivative with respect to time [s]. The derivative of the magnetic flux density refers to the magnetic field. The derivative of the magnetic flux density can be defined as the amount of electrical current induced in the tissue and therefore can serve as one of the key parameters in causing muscle contraction. The higher the derivative of the magnetic flux density, the stronger the muscle contraction. The derivative of the magnetic flux density can be calculated from the above equation.

[391] The maximum value of the derivative of the magnetic flux density can be up to 5 MT/s or range from 0.3 kT/s to 800 kT/s, from 0.5 kT/s to 400 kT/s, from 1 kT/s s to 300 kT/s, from 1.5 kT/s to 250 kT/s, from 2 kT/s to 200 kT/s, from 2.5 kT/s to 150 kT/s.

[392] The frequency of the RF field (e.g., RF waves) may be in the range of hundreds of kHz to tens of GHz, for example, in the range of 100 kHz to 3 GHz, or 500 kHz to 3 GHz, or 400 kHz to 900 MHz, or 500 kHz to 900 MHz, or approximately 13.56 MHz, 40.68 MHz, 27.12 MHz, or 2.45 GHz.

[393] The energy flux provided by an RF field (eg, an RF wave) can range from 0.001 W/cm ² to 1500 W/cm ² , or from 0.001 W/cm ² to 15 W/cm ² , or from 0 .01 W / cm ² to 1000 W / cm ² , or from 0.01 W / cm ² to 5 W / cm ² , or from 0.08 W / cm ² to 1 W / cm ² , or from 0.1 W / cm ² to 0.7 W / cm ² . The term "about" should be interpreted as being in the range of 5% of the specified value.

[394] The voltage of the electromagnetic signal provided by the RF therapy circuit power supply may be in the range of 1 V to 5 kV, or 5 V to 140 V, or 10 V to 120 V, or 15 V to 50 V, or from 20 V to 50 V.

[395] The temperature in the biological structure, the temperature at the surface of the treated area of the body, the temperature in the body area, the temperature inside the applicator, the temperature of the RF electrode, and/or the temperature of the magnetic field generating device can be measured, for example, using a temperature sensor 816, which implemented in the applicator shown in Fig. 8s. The temperature of the RF electrode and/or magnetic field generating device can be maintained within the range of 38°C to 150°C, 38°C to 100°C or 40°C to 80°C, 40°C to 60° C or 41°C to 60°C, or 42°C to 60°C. The temperature on the surface of the treated area of the body, the temperature in the treated organism and/or biological structure may rise to a temperature in the range of 38°C to 60°C or 40°C to 52°C or 41°C to 50°C C, or 41°C to 48°C, or 42°C to 48°C, or 42°C to 45°C. The temperatures described above can be reached within 5 s to 600 s, 10 s to 300 s, or 30 s to 180 s after the start of the RF therapy and/or magnetotherapy. After that, the temperature value can be maintained at a constant level during therapy with a maximum temperature deviation in the range of 5°C, 3°C or 2°C, or 1°C.

[396] At the beginning of therapy, the initial temperature in the patient's skin and/or in the biological structure may rise to an initial temperature in the range of 42°C to 60°C or 45°C to 54°C, or 48°C to 60° C, or from 48°C to 52°C, and/or up to a temperature of 3°C or 5°C, or 8°C above the temperature at which the apoptosis process begins, but not higher than 60°C. After 45 s to 360 s, or 60 s to 300 s, or 120 s to 400 s, or 300 s to 500 s after the initial temperature has been reached, the intensity of the RF field may be reduced and the temperature on the patient's skin and/or the temperature in the biological structure can be maintained at a temperature in the range of 41°C to 50°C or 42°C to 48°C. According to another method of therapy, the temperature of the biological structure during therapy can be at least twice lowered or increased in the range from 2°C to 10°C, from 2°C to 8°C or from 3°C to 6°C, while while at least one applicator is attached to the same area of the patient's body, such as the abdomen, buttock, arm, leg, and/or other area of the body.

[397] The temperature in a biological structure can be calculated in accordance with a mathematical model, a correlation function, in combination with at least one or more measured properties. These measured properties may include the temperature at the patient's skin, the capacitance between the RF electrodes, the current-voltage response of the RF bipolar electrodes, and/or the current-voltage response of the electrical components connected to the RF electrodes.

[398] The duration of therapy can be from 5 minutes to 120 minutes, or from 5 minutes to 60 minutes, or from 15 minutes to 40 minutes. Within one week, one, two or three treatments of one area of the body may be provided. In addition, one pause between two consecutive therapies may be one, two or three weeks.

[399] The sum of the energy flux density of RF therapy and magnetic therapy applied to the patient during therapy may be in the range from 0.03 mW/mm ² to 1.2 W/mm ² , or in the range from 0.05 mW/mm ² to 0.9 W/mm ² , or in the range from 0.01 mW/mm ² to 0.65 W/mm ² . The portion of the magnetotherapy energy flux density during the simultaneous application of RF therapy and active magnetotherapy can be in the range of 1% to 70%, 3% to 50%, 5% to 30%, or 1% to 20% of the therapy time.

[400] The output power of RF energy (i.e., RF fields) provided by a single RF electrode may range from 0.005 W to 350 W, or from 0.1 W to 200 W, or from 0.1 W to 150 W .

[401] In FIG. 21 depicts the different types of muscle contraction that can be provided with a therapeutic device and achieved by applying a magnetic field or a combination of a magnetic field and an RF field. Muscle contraction may differ in energy consumption and muscle targeting, such as muscle strengthening, muscle volume increase/decrease, muscle endurance, muscle relaxation, muscle warm-up and/or other effects. The vertical axis may represent the strength of muscle contraction and the horizontal axis may represent time. The arrows may represent magnetic single pulses and/or pulses applied to the patient's muscle.

[402] A low pulse repetition rate of a time-varying magnetic field, such as in the range of 1 Hz to 15 Hz, can cause twitching. The low repetition rate may be low enough to allow complete relaxation of the muscle being treated. The energy consumption of the treated muscle may be low due to the low repetition rate. However, a low repetition rate can cause the muscle to actively relax, for example, between two contractions.

[403] The intermediate repetition rate of the pulses of the time-varying magnetic field can cause incomplete tetanic contraction of the muscle, while the intermediate repetition frequency can be in the range from 15 Hz to 29 Hz. An incomplete tetanic muscle contraction can be set at a repetition rate in the range of 10 Hz to 30 Hz. The muscle may not fully relax. The muscle may contract partially. The force of muscle contraction can be increased at a constant applied magnetic flux density.

[404] A higher repetition rate of pulses of a time-varying magnetic field can cause full tetanic contraction of the muscle. Higher repetition rates may be in the range of, for example, 30 Hz to 150 Hz, or 30 Hz to 90 Hz, or 30 Hz to 60 Hz. Full tetanic contraction of the muscle can cause the strongest, supramaximal muscle contraction. A supramaximal muscle contraction may be stronger than a volitional muscle contraction. Energy consumption may be higher. The enhancement effect may increase. In addition, it is believed that at repetition rates of at least 30 Hz, fat cells may decrease in volume and/or number.

[405] An even higher frequency of repetition of pulses of the time-varying magnetic field, above 90 Hz, can suppress and/or block the transmission of pain excitation at different levels of the nervous system and/or pain receptors. The higher repetition rate may be at least 100 Hz, at least 120 Hz, or at least 140 Hz, or in the range of 100 Hz to 230 Hz, or 120 Hz to 200 Hz, or 140 Hz to 180 Hz. Applying a time-varying magnetic field to a patient's muscle can cause an analgesic effect.

[406] A higher repetition rate of pulses of a time-varying magnetic field in the range from 120 Hz to 300 Hz or from 150 Hz to 250 Hz, or from 180 Hz to 350 Hz, or above 200 Hz can cause the effect of muscle relaxation.

[407] The quality of muscle contraction caused by a time-varying magnetic field can be characterized by such parameters as the contractile force of muscle contraction, the length of the muscle-tendon pair, the relative shortening of the muscle, or the speed of muscle shortening.

[408] The contractile force of muscle contraction can reach a contractile force value of at least 0.1 N/cm ² and up to 250 N/cm ² . The contractile force can be in the range of 0.5 N/ ^cm2 to 200 N/ ^cm2 , or in the range of 1 N/ ^cm2 to 150 N/ ^cm2 , or in the range of 2 N/cm2 ^to 100 N/cm ² .

[409] The length of a muscle-tendon pair can be up to 65% of the length of a muscle-tendon pair at rest. The length of a muscle-tendon pair can be in the range of 1% to 65% of the length of a muscle-tendon pair at rest, or in the range of 3% to 55% of the length of a muscle-tendon pair at rest, or in the range of 5% to 50% length of the muscle-tendon pair at rest.

[410] During muscle contraction, the muscle can shorten up to 60% of the length of the muscle at rest. Muscle shortening can range from 0.1% to 50% of muscle length at rest, or in the range of 0.5% to 40% of muscle length at rest, or in the range of 1% to 25% of muscle length at rest .

[411] The muscle can contract at speeds up to 10 cm/s. The speed of muscle shortening can be in the range of 0.1 cm/s to 7.5 cm/s, or in the range of 0.2 cm/s to 5 cm/s, or in the range of 0.5 cm/s to 3 cm /With.

[412] A time-varying magnetic field may be applied to a patient to induce a muscle-shaping effect by contracting the muscle. The muscle may acquire increased tone and/or volume. Muscle strength may also increase.

[413] With regard to the types of combination therapy using RF therapy and magnetotherapy, the therapeutic device can be configured to provide different therapeutic energies (eg, RF field and magnetic field) at different times during the same therapy session. The user can control or regulate therapy using the HMI. The HMI may be connected to a master unit and/or one or more control units. In addition, the master unit and/or the control unit may control or regulate the application of different therapeutic energies in accordance with the therapy protocol, body area, or other possibility selected by the user. Additionally, the master unit and/or the control unit may control or regulate the application of different therapeutic energies in accordance with the feedback provided by any of the aforementioned sensors. Therefore, the master unit and/or one or more control units may control or regulate therapy and energy delivery for therapy (eg, RF therapy and magnetotherapy) at different times during a single therapy session. All shown types of application of magnetotherapy and RF therapy can be provided by the therapeutic device.

[414] One type of combined application of magnetotherapy in conjunction with RF therapy may be simultaneous application. In the course of simultaneous application, both magnetotherapy and RF therapy can be applied simultaneously during all or most of the therapy session. In one example, simultaneous application can be achieved by applying one or more parts of the magnetic field in conjunction with applying a constant RF field. In another example, pulsed magnetotherapy can be applied during continuous RF therapy. In another example, simultaneous application can be achieved by continuous application of RF therapy, for example, in conjunction with one or two long sequences of magnetic pulses. In this case, the long sequence of magnetic pulses should contain magnetic pulses characterized by a repetition rate with values in the range from 1 Hz to 15 Hz or from 1 Hz to 10 Hz. When using only one of the two magnetic sequences for the entire therapy session, the duration of such sequences can range from 5 seconds to 90 minutes, or from 10 seconds to 80 minutes, or from 15 minutes to 45 minutes.

[415] Muscle contraction induced by a time-varying magnetic field in conjunction with or during concurrent RF therapy may involve more affected muscle fibers. In addition, the target biological structure (eg, muscle) can contract more strongly when applying a lower magnetic flux density of the magnetic field compared to the situation in the absence of simultaneous RF therapy.

[416] Simultaneous application of RF therapy and magnetotherapy to one area of the body can improve the dissipation of heat generated by RF therapy. This effect is based on increased blood circulation in the treated area of the body or in the vicinity of the treated area. In addition, induced muscle work can increase the uniformity of heating and dissipation of heat induced and delivered by the RF field.

[417] Another type of combined application of magnetotherapy in conjunction with RF therapy can be a separate application. During separate application, both magnetotherapy and RF therapy can be applied at different times during the therapy session. RF therapy may be provided before, after and/or between magnetic envelopes, packets, sequences, pulses and/or single magnetic therapy pulses.

[418] The ratio between the application time of magnetic therapy and the application time of RF therapy can be in the range of 0.2% to 80%, or 2% to 60%, or 5% to 50%, or 20% to 60%. The application time of magnetotherapy for this calculation is the sum of all pulse durations during therapy.

[419] Another type of combined application of magnetotherapy in conjunction with RF therapy may be a dependent application. The application of one therapeutic energy may be dependent on a trigger parameter or one or more therapy parameters of another therapeutic energy. The dependent application may be triggered or controlled in response to feedback from one or more sensors. For example, triggering the application of RF therapy may depend on triggering magnetotherapy or triggering a sequence, packet, and/or envelope. In the absence of heat dissipation provided by the work of the muscle (including contraction and/or relaxation of the muscle), there may be a health risk due to unwanted tissue damage caused by overheating. In another example, the start of the application of magnetotherapy may depend on the start, length of time or intensity of RF therapy. The magnetotherapy can preferably be started after sufficient heating of the biological structure. Magnetic therapy providing at least partial muscle contraction or muscle contraction can improve blood and lymph flow, massage adjacent tissues, and improve distribution of heat induced in the patient's body by RF therapy.

[420] The therapy protocol can be divided into two or three therapy parts. The number of therapy parts for one protocol can range from 2 to 50, or from 2 to 30, or from 2 to 15.

[421] Each therapy part of the therapy protocol may have different therapy parameters and/or types of combined magnetotherapy and RF therapy, as described above.

[422] One part of therapy can last for a part time, where the part time can range from 10 seconds to 30 minutes, or from 15 seconds to 25 minutes, or from 20 seconds to 20 minutes. Different parts may have different therapeutic effects in one or more of the biological structures being treated, such as muscle and adipose tissue. For example, one part of the therapy may provide a high intensity muscle exercise in which the muscle contractions are intense and provide a large number of such contractions, while during one part of the therapy a higher frequency of repetition of magnetic pulses with a high energy flux density can be used. Another part of the therapy may have the effect of relaxing the muscle, wherein a low and/or high magnetic pulse repetition rate may be used and/or a lower magnetic flux density of the magnetic field may also be used.

[423] The therapy protocol may include different RF therapy output power settings on command or under the control of a control system of the therapeutic device. One setting may be a constant power output, while the power output over the course of a therapy protocol may be the same. Another setting may be the fluctuating output power of the RF therapy. The output power of the RF therapy may fluctuate around a predetermined output power in the range of 0.1% to 5% of the predetermined output power. Another setting may be a variable RF energy output, wherein the RF therapy output is varied during the course of the therapy protocol. The change in the output power of the RF therapy may be provided in one or more steps of changing the output power, wherein the step of changing the output power may include one change in the value of the output power of the RF therapy applied by one or more RF electrodes. The change in RF therapy output power from one value to another value during the output power change step may be in the range of 0.1W to 50W, or 0.1W to 30W, or 0.1W to 20W. The output power step can be characterized by a time duration ranging from 0.1 s to 10 min, or from 0.1 s to 5 min.

[424] With regard to the change in the output power of RF energy, the output power of RF energy can be characterized by different values during different periods of time of the protocol of therapy. Therefore, RF therapy may be characterized by one power output during a first period of time, followed by a step of changing the output power, and a second time period characterized by a different output of RF therapy. The first time period characterized by one RF therapy output power may range from 1 second to 15 minutes, or from 10 seconds to 10 minutes. The second time period, characterized by a different output power of the RF therapy, may be in the range of 1 second to 45 minutes, or 4 seconds to 59 minutes, or 5 seconds to 35 minutes. For example, RF therapy may be characterized by a power output value of approximately 20 watts during the first time and 10 watts during the second period of time.

[425] The first illustrative protocol of therapy may include two parts of therapy. The first part of the therapy may include magnetic pulse envelopes, which envelopes may comprise pulses characterized by a repetition rate in the range of 1 Hz to 10 Hz. The envelopes of the first part of the therapy can be rectangular or trapezoidal. The duration of the first part of therapy can be from 3 minutes to 15 minutes. The second part of the therapy may include magnetic pulse envelopes, which envelopes may comprise pulses characterized by a repetition rate in the range of 15 Hz to 45 Hz. The envelopes of the second part of the therapy can be rectangular or trapezoidal. The duration of the first part of therapy can be from 3 minutes to 15 minutes. Parts of the therapy can be repeated one after the other. RF therapy can be applied continuously throughout the therapy protocol. RF therapy may include one or two steps of changing the power output.

[426] A second exemplary therapy protocol may include three parts of therapy. The first part of the therapy may include magnetic pulse envelopes, which envelopes may comprise pulses having a repetition rate in the range of 5 Hz to 50 Hz. The envelopes of the first part of the therapy can be rectangular or trapezoidal. The duration of the first part of therapy can be from 3 minutes to 15 minutes. The second part of the therapy may include magnetic pulse envelopes, which envelopes may comprise pulses characterized by a repetition rate in the range of 15 Hz to 45 Hz. The envelopes of the second part of the therapy can be rectangular or trapezoidal. The duration of the first part of therapy can be from 3 minutes to 15 minutes. The third part of the therapy may include magnetic pulse envelopes, which envelopes may comprise pulses characterized by a repetition rate in the range of 10 Hz to 40 Hz. The envelopes of the third part of the therapy can be rectangular or trapezoidal. The duration of the third part of therapy can be from 3 minutes to 15 minutes. Parts of the therapy can be repeated one after the other. RF therapy can be applied continuously throughout the therapy protocol. RF therapy may include one or two steps of changing the power output. One step of changing the output power can be initiated in the range from 1 minute to 20 minutes after starting the therapy protocol. In one example, one step of changing the power output may be initiated three minutes after the start of the therapy protocol.

[427] All examples, embodiments and methods can be used individually or in any combination.

[428] Described new systems and methods. The present invention is to be understood in its broadest sense, and thus various changes and substitutions can, of course, be made without departing from the spirit and scope of the present invention. Therefore, the present invention should not be limited in any way except for the following claims and their equivalents.

[429] A list of abbreviations associated with FIG. 17, 18 and 18a. (A/B) means that the corresponding list item can be shown with the corresponding letter. For example, ESD (A/B) means that at least one figure shows ESD A and/or ESD B.

[430] PS Power Supply

[431] ESD (A/B) Energy Storage Device

[432] SW (A/B) Switch

[433] HIFEM (A/B) magnetic therapy cluster

[434] MFGD (A/B) magnetic field generating device

[435] CUM (A/B) magnetic circuit control unit

[436] APS RF Auxiliary Power Supply RF Circuit

[437] PU power supply

[438] SPSRF Permanent Power Supply RF Circuit

[439] PNFLT Power Line Filter

[440] PSRF power supply for RF therapy

[441] RF (A/B) therapeutic cluster for RF therapy

[442] SYM (A/B) balancing element

[443] AP (A/B) Applicator

[444] RFE (A/B) RF electrode

[445] APS (A/B) Auxiliary Power Supply

[446] PSM Power Supply for Magnetic Therapy

[447] BPS (A/B) on-board power supply

[448] SPSM Permanent Magnetic Circuit Power Supply

[449] PN power supply network

[450] PF Pulse Filter

[451] SE safety element

[452] PA Power Amplifier

[453] CURF RF circuit control unit.

Claims (30)

1. A therapeutic device for providing magnetotherapy and radiofrequency therapy to an area of the patient's body, containing: a power storage device configured to store electricity; a device that generates a magnetic field; a switching device configured to discharge electricity from the energy storage device to the magnetic field generating device so that a time-varying magnetic field is generated that causes muscle contraction in the patient's body region, while the time-varying magnetic field is characterized by a magnetic flux density in the range from 0.5 to 7 T and a repetition frequency in the range from 0.1 to 700 Hz; And a radio frequency electrode configured to generate a radio frequency field for heating tissue in the area of the patient's body, wherein the RF electrode is configured to be positioned between the magnetic field generating device and the patient's body region. 2. The device according to claim 1, characterized in that the device generating the magnetic field and the radio frequency electrode are separated by an air gap. 3. The device according to claim 1, characterized in that the device generating the magnetic field and the RF electrode are separated by an insulating material. 4. The device according to claim. 1, characterized in that the distance between the device generating the magnetic field and the radio frequency electrode is in the range from 0.5 to 50 mm. 5. The device according to claim. 1, characterized in that the radio frequency electrode contains a conductive wire. 6. The device according to claim. 1, characterized in that the radio frequency electrode contains a conductive layer characterized by a thickness in the range from 0.01 to 5 mm. 7. The device according to claim. 1, characterized in that the radio frequency electrode is the first radio frequency electrode of a bipolar pair of radio frequency electrodes. 8. The device according to claim. 1, characterized in that the radio frequency electrode contains carbon. 9. The device according to claim. 1, characterized in that the radio frequency electrode is located on the substrate, and the substrate contains a polymeric material. 10. The device according to claim. 1, characterized in that the radio frequency electrode is located on the substrate, and the substrate contains a ceramic material. 11. A therapeutic device for providing magnetotherapy and radiofrequency therapy to an area of the patient's body, comprising: a power storage device configured to store electricity; applicator containing: a housing containing an upper casing and a lower casing; a device that generates a magnetic field, placed inside the housing; And a radio frequency electrode disposed between the magnetic field generating device and the lower case; And a switching device configured to discharge electricity from the energy storage device to the magnetic field generating device, so that the magnetic field generating device generates a time-varying magnetic field to induce contraction of a muscle in a region of the patient's body, wherein the time-varying magnetic field the field is characterized by a magnetic flux density in the range from 0.5 to 7 T and a repetition frequency in the range from 0.1 to 700 Hz, and; wherein the radio frequency electrode is configured to generate a radio frequency field to heat tissue in the patient's body. 12. The device according to claim 11, characterized in that the radio frequency electrode is connected to a power amplifier configured to generate a radio frequency signal characterized by a frequency in the range from 100 kHz to 3 GHz. 13. The device according to claim. 11, characterized in that the radio frequency electrode is the first radio frequency electrode of a bipolar pair of radio frequency electrodes located in the applicator. 14. The device according to claim. 11, characterized in that it further comprises a control system containing a microprocessor, while the applicator further comprises a temperature sensor, and the temperature sensor is configured to communicate with the control system. 15. The device according to claim. 11, characterized in that the radio frequency electrode contains a conductive layer characterized by a thickness in the range from 0.01 to 10 mm. 16. The device according to claim 11, characterized in that the RF electrode comprises a conductive layer deposited on an insulating substrate. 17. The device according to claim 11, characterized in that the device generating the magnetic field and the RF electrode are separated by an insulating material.

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