Electric field generating device and control method thereof, and computer-readable storage medium

Abstract

This application relates to the field of surgery, and provides an electric field generating device, a control method thereof, and a computer-readable storage medium. The electric field generating device includes n electrodes, an electrical signal generator, and a control signal generator. The control signal generator is electrically connected to the electrical signal generator, and controls the electrical signal generator to output a first electrical signal to m electrodes among the n electrodes, and controls the electrical signal generator to output a second electrical signal to at least two electrodes among the n−m electrodes, and is used to generate an electric field between the electrodes having the first electrical signal and the electrodes having the second electrical signal. n is an integer greater than or equal to 3. The voltage of the second electrical signal is lower than the voltage of the first electrical signal. 1≦m<n, and m is an integer. According to this application, the coverage rate and flexibility of the target biological tissue by the electric field can be improved, and as a result, the inhibitory effect on the division of diseased cells can be enhanced.

Description

[Technical Field]

[0001] (CROSS-REFERENCE TO RELATED APPLICATIONS) This application claims priority to a Chinese patent application filed with the China Patent Office on October 22, 2021, bearing application number 202111231292.6 and entitled "Electric field generating device and control method thereof, and computer-readable storage medium," the entire contents of which are incorporated herein by reference. The present application relates to the field of surgery, and in particular to an electric field generating device and a control method thereof, and a computer-readable storage medium. [Background technology]

[0002] Electric field therapy is a treatment method performed using a portable, non-invasive medical device, which applies a low-intensity, medium-frequency, designed electric field to target biological tissue, for example, by proliferating microtubule proteins in diseased cells and disrupting mitosis in diseased cells, thereby inducing apoptosis of affected diseased cells and inhibiting their growth.

[0003] Currently, in a device for destroying diseased cells or inhibiting diseased cell division, an electric signal generator outputs a series of electric signals to an electrode pair, two electrodes of which are arranged opposite each other, thereby generating a perpendicular electric field between the opposite electrodes, which acts on a target biological tissue region containing the target biological tissue.

[0004] However, the inventors of the present application discovered that the electrode pair is located on the periphery of the target biological tissue region, and the target biological tissue (e.g., diseased cells) in the target biological tissue region is not necessarily within the range of the vertical electric field generated by the conventional electrode pair, or is not completely within the range of the conventional vertical electric field. In other words, the coverage range of the conventional vertical electric field is too fixed and narrow, so the coverage rate of the target biological tissue is limited, and as a result, the strength of the electric field on the target biological tissue is limited, resulting in an insufficient inhibitory effect on the division of the target biological tissue, such as diseased cells.

Summary of the Invention

Problems to be Solved by the Invention

[0005] This application focuses on the drawbacks of the conventional method and provides an electric field generator, its control method, and a computer-readable storage medium. Thereby, due to the limited intensity of the electric field covering the target biological tissue region, the intensity of the electric field covering the target biological tissue is also limited, resulting in insufficient inhibitory effect on the division of target biological tissues such as diseased cells in the prior art. This application solves the technical problems existing in the prior art.

Means for Solving the Problems

[0006] To achieve the above object, the first aspect of this application is an electric field generator, comprising: n electrodes arranged in a manner designed around the target biological tissue region; an electrical signal generator electrically connected to the n electrodes; a control signal generator electrically connected to the electrical signal generator, controlling the electrical signal generator to output a first electrical signal to m of the n electrodes, and controlling the electrical signal generator to output a second electrical signal to at least two of the n - m electrodes, and used to generate an electric field between the electrodes with the first electrical signal and the electrodes with the second electrical signal; where n is an integer greater than or equal to 3, the voltage of the second electrical signal is lower than the voltage of the first electrical signal, 1 ≤ m < n, and m is an integer. The application provides an electric field generator.

[0007] The second aspect of this application is a control method for an electric field generator applied to the electric field generator described in the first aspect, comprising: controlling the electrical signal generator to output a first electrical signal to m of the n electrodes, and controlling the electrical signal generator to output a second electrical signal to at least two of the n - m electrodes, and generating an electric field between the electrodes with the first electrical signal and the electrodes with the second electrical signal. n is an integer of 3 or more, 1 ≤ m < n, and m is an integer. The electric field generating device includes an electric signal generator and n electrodes that are electrically connected, and provides a control method for the electric field generating device in which the voltage of the second electric signal is lower than the voltage of the first electric signal.

[0008] A third aspect of the present application is a computer-readable storage medium storing a computer program, when the computer program is executed by a processor, the control method of the electric field generating device described above is realized. The control method of the electric field generating device is controlling the electric signal generator to output a first electric signal to m electrodes out of the n electrodes, and controlling the electric signal generator to output a second electric signal to at least two electrodes out of the n - m electrodes, to generate an electric field between the electrodes having the first electric signal and the electrodes having the second electric signal. n is an integer of 3 or more, 1 ≤ m < n, and m is an integer. The electric field generating device includes an electric signal generator and n electrodes that are electrically connected, and provides a computer-readable storage medium in which the voltage of the second electric signal is lower than the voltage of the first electric signal.

Advantages of the Invention

[0009] In the technical solution provided by this application, n electrodes are arranged in a designed manner around the target biological tissue region, and the electrical signal generator is controlled to output a first electrical signal to m electrodes out of the n electrodes, and the electrical signal generator is controlled to output a second electrical signal to at least two electrodes out of the n - m electrodes, where n is an integer greater than or equal to 3, 1 ≤ m < n, and m is an integer. In the embodiments of this application, based on the position of the target biological tissue within the target biological tissue region, the number of electrodes around the target biological tissue region can be flexibly selected, and by controlling which electrodes will have the second electrical signal, the coverage area of the electric field generated between the electrodes with the first electrical signal and the electrodes with the second electrical signal can be made to best match the position of the target biological tissue. Therefore, this embodiment can improve the degree of fit between the coverage area of the electric field and the position of the target biological tissue, the coverage rate of the target biological tissue by the electric field, flexibility or adaptability. As a result, the intensity of the electric field covering the target biological tissue can be increased, and the inhibitory effect on the division of the target biological tissue such as diseased cells can be further enhanced.

[0010] And between the electrodes with the first electrical signal and at least two electrodes with the second electrical signal, a plurality of electric fields can be generated, and the superposition of these electric fields strengthens the electric field intensity in the overlapping region of the electric fields. By reasonably selecting at least two electrodes with the second electrical signal, the coverage rate of the target biological tissue by the overlapping region of the electric fields can be improved, which contributes to further enhancing the inhibitory effect on the division of the target biological tissue such as diseased cells.

[0011] The accompanying aspects and advantages of this application are partially given in the following description, and they will become clear from the following description or will be understood through the implementation of this application.

[0012] The above-mentioned and / or additional aspects and advantages in this application will become clear and easy to understand from the following description in conjunction with the figures regarding the embodiments.

Brief Description of the Drawings

[0013] [Figure 1] 1 is a framework schematic diagram of an electric field generating device according to an embodiment of the present application. [Figure 2] FIG. 1 is a framework schematic diagram of another electric field generating device according to an embodiment of the present application. [Figure 3] FIG. 10 is a schematic diagram of an electric field when using a six-electrode arrangement in another electric field generator according to an embodiment of the present application. [Figure 4] 1 is a schematic diagram of a two-dimensional model of a target biological tissue region according to an embodiment of the present application. [Figure 5a] FIG. 10 is a diagram illustrating the electric field strength distribution in a two-dimensional model of a target biological tissue region in accordance with an embodiment of the present application, with a single grounded electrode. [Figure 5b] 1 is a diagram illustrating the electric field strength distribution in a two-dimensional model of a target biological tissue region according to an embodiment of the present application, in the case of one type of dual-electrode grounding. [Figure 5c] 10 is a diagram illustrating the electric field strength distribution in another case of dual-electrode grounding in a two-dimensional model of a target biological tissue region according to an embodiment of the present application. [Figure 6] 1 is a schematic diagram of a three-dimensional model of a human thoracic cavity according to an embodiment of the present application. [Figure 7] FIG. 2 is a diagram illustrating a two-layer structure of a single electrode in a three-dimensional model of a human thoracic cavity according to an embodiment of the present application. [Figure 8a] 1 is a diagram showing the distribution of electrode arrays on the anterior chest, back, and sides of a human thoracic cavity for lung cancer treatment in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application. [Figure 8b] FIG. 1 is a diagram showing the distribution of an electrode array on the back of a human thoracic cavity for lung cancer treatment in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application. [Figure 9a] 1 is a first distribution map of the sizes and positions of four virtual tumor models in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application. [Figure 9b] 1 is a second distribution map of the sizes and positions of four virtual tumor models in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application. [Figure 9c]10 is a third distribution map of the sizes and positions of four virtual tumor models in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application. [Figure 9d] 10 is a fourth distribution map of the sizes and positions of four virtual tumor models in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application. [Figure 10] FIG. 2 is a curve diagram showing the relationship between electric field strength and volume of a three-dimensional model of a human thoracic cavity according to an embodiment of the present application. [Figure 11a] FIG. 1 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity for a tumor T1 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application when a single electrode array is grounded on the back of the human body. [Figure 11b] FIG. 1 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity for a tumor T1 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application when a dual-electrode array is grounded on the left side and back of the human body. [Figure 11c] FIG. 1 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity for a tumor T1 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application when the bipolar electrode array is grounded on the back of the human body. [Figure 12a] FIG. 10 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity for a tumor T2 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application, when a single electrode array is grounded on the back of the human body. [Figure 12b] FIG. 10 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity for a tumor T2 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application, when a dual-electrode array is grounded on the left side and back of the human body. [Figure 12c] FIG. 10 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity for a tumor T2 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application when the bipolar electrode array is grounded on the back of the human body. [Figure 13a] FIG. 10 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity for a tumor T3 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application, when a single electrode array is grounded on the back of the human body. [Figure 13b] FIG. 10 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity for a tumor T3 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application, when a dual-electrode array is grounded on the right side and back of the human body. [Figure 13c] FIG. 10 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity when the bipolar electrode array is grounded on the back of the human body, for a tumor T3 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application. [Figure 14a] FIG. 10 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity for a tumor T4 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application, when a single electrode array is grounded on the back of the human body. [Figure 14b] FIG. 10 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity for a tumor T4 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application, when a dual-electrode array is grounded on the right side and back of the human body. [Figure 14c] FIG. 10 is a schematic diagram showing the electric field distribution on the horizontal plane of the thoracic cavity for a tumor T4 in a three-dimensional model of the human thoracic cavity according to an embodiment of the present application when the bipolar electrode array is grounded on the back of the human body. DETAILED DESCRIPTION OF THE INVENTION

[0014] The present application provides an electric field generating device, a control method thereof, and a computer-readable storage medium, which solves the technical problem existing in the prior art, that is, the strength of the electric field covering the target biological tissue area is limited, and therefore the strength of the electric field covering the target biological tissue is also limited, resulting in an insufficient inhibitory effect on the division of the target biological tissue, such as diseased cells.

[0015] The present application will be described in detail below. Examples of embodiments of the present application are shown in the drawings, and the same or similar numbers throughout the drawings refer to the same or similar parts, or parts having the same or similar functions. Furthermore, if a detailed description of known technologies is unnecessary for the features of the present application shown, such description will be omitted. The examples described with reference to the drawings are illustrative and are used only to interpret the present application, and should not be construed as limitations on the present application.

[0016] As will be understood by those skilled in the art, unless otherwise defined, all terms (including technical and scientific terms) used herein have the same meaning as commonly understood by those of ordinary skill in the art to which this application pertains, and terms defined in general dictionaries should also be understood as meanings consistent with the context of the prior art, and should not be interpreted in an idealized or overly formal way unless specifically defined herein.

[0017] Those skilled in the art should understand that the singular forms "a," "an," "the," and "the" as used herein can include the plural, unless expressly stated otherwise. Furthermore, the term "comprising" as used herein refers to the presence of stated features, integers, steps, operations, elements, and / or components, but should be understood as not excluding the presence or addition of one or more other features, integers, steps, operations, elements, components, and / or groups thereof. When an element is said to be "connected" or "coupled," it may be directly connected or coupled to another element, or intermediate elements may be present. Furthermore, as used herein, "connected" or "coupled" may also include wireless connections or couplings. Furthermore, the term "and / or" as used herein includes all units, any one unit, or all combinations of at least one listed item associated with each other.

[0018] The inventors of the present application have discovered that the electrode pair is located on the periphery of the target biological tissue region, and the target biological tissue (e.g., diseased cells) in the target biological tissue region is not necessarily within the range of the vertical electric field generated by the conventional electrode pair, or is not completely within the range of the conventional vertical electric field. In other words, the coverage range of the conventional vertical electric field is too fixed and narrow, so the coverage rate of the target biological tissue is limited, and as a result, the strength of the electric field on the target biological tissue is limited, resulting in an insufficient inhibitory effect on the division of the target biological tissue, such as diseased cells.

[0019] The target electric field generating device and the control method thereof provided in the present application aim to solve the above technical problems in the prior art.

[0020] The following detailed description will be given of the technical solutions of the present application and how they solve the above-mentioned technical problems through specific examples. These specific examples can be combined with each other, and the same or similar concepts or processes may not be repeated in some examples. The following description of the embodiments of the present application will be given with reference to the drawings.

[0021] The electric field generating devices provided by the examples of the present application are for surgical applications and are applied to surgical medical instruments.

[0022] As shown in FIG. 1 , the electric field generator provided by the embodiment of the present application includes n electrodes 10, an electric signal generator 25, and a control signal generator 40. Specifically, the n electrodes 10 are arranged in a designed manner around a target biological tissue region, where n is an integer greater than or equal to 3. The target biological tissue region includes target biological tissue and normal biological tissue. The target biological tissue includes diseased cells, tumors, lesions, etc., and lesions refer to parts of the body where disease has occurred or localized diseased tissue where pathogenic microorganisms exist. For example, if a part of the lung is destroyed by tuberculosis bacteria, that part is considered to be a pulmonary tuberculosis lesion. Normal biological tissue refers to biological tissue that does not contain diseased cells, tumors, or lesions, and can be considered to be tissue other than the target biological tissue.

[0023] The electrical signal generator 25 is electrically connected to the n electrodes 10 .

[0024] The control signal generator 40 is electrically connected to the electrical signal generator 25, controls the electrical signal generator 25 to output a first electrical signal to m electrodes out of n electrodes 10, and controls the electrical signal generator 25 to output a second electrical signal to at least two electrodes out of n - m electrodes, and is used to generate an electric field between the electrodes having the first electrical signal and the electrodes having the second electrical signal. The voltage of the second electrical signal is lower than the voltage of the first electrical signal, 1 ≦ m < n, and m is an integer.

[0025] Optionally, the first electrical signal and the second electrical signal may be output by one electrical signal generator or may be output by each of two electrical signal generators.

[0026] Optionally, the n electrodes 10 may be attached to a target site of a human body or an animal body according to a designed method.

[0027] Optionally, there is at least one electrode having the first electrical signal, there are at least two electrodes having the second electrical signal, and the number of electrodes having the first electrical signal is less than the number of electrodes having the second electrical signal.

[0028] Alternatively, the control signal generator 40 may be a CPU (Central Processing Unit), a general-purpose processor, a DSP (Digital Signal Processor), an ASIC (Application Specific Integrated Circuit), an FPGA (Field-Programmable Gate Array) or other programmable logic device, a transistor logic device, a hardware component, or any combination thereof, which may implement or execute various exemplary logic blocks, modules, and circuits described in the present disclosure. The control signal generator 40 may also be a combination for implementing computational functions, including, for example, a combination of one or more microprocessors, a combination of a DSP and a microprocessor, etc.

[0029] In an embodiment of the present application, the number of electrodes around the target biological tissue region can be flexibly selected based on the position of the target biological tissue within the target biological tissue region, and which electrodes have the second electrical signal can be controlled so that the coverage area of ​​the electric field generated between the electrode having the first electrical signal and the electrode having the second electrical signal can best match the position of the target biological tissue. Therefore, this embodiment can improve the compatibility between the coverage area of ​​the electric field and the position of the target biological tissue, the coverage rate of the target biological tissue by the electric field, flexibility, or adaptability, thereby increasing the strength of the electric field covering the target biological tissue and further improving the inhibitory effect on the division of the target biological tissue, such as diseased cells.

[0030] Furthermore, multiple electric fields can be generated between the electrode having the first electric signal and at least two electrodes having the second electric signal, and these electric fields overlap to enhance the electric field strength in the overlapping region of the electric fields. By rationally selecting the at least two electrodes having the second electric signal, the coverage rate of the overlapping region of the electric fields can be improved, which contributes to further improving the inhibitory effect on the division of the target biological tissue, such as diseased cells.

[0031] In some embodiments, as shown in FIG. 1 , the electrical signal generator 25 includes a first electrical signal generating circuit 20 electrically connected to the n electrodes for outputting a first electrical signal, and a second electrical signal generating circuit 30 electrically connected to the n electrodes for outputting a second electrical signal.

[0032] In some embodiments, as shown in FIG. 2 , the electric field generating device further includes a first switch component 50 and a second switch component 60, wherein the first electric signal generating circuit 20 is electrically connected to the n electrodes 10 via the first switch component 50, the control signal generator 40 is electrically connected to the first switch component 50, the second electric signal generating circuit 30 is electrically connected to the n electrodes 10 via the second switch component 60, and the control signal generator 40 is electrically connected to the second switch component 60, and the control signal generator 40 is used to generate an electric field between the electrode having the first electric signal and the electrode having the second electric signal by controlling the first switch component 50 to transmit the first electric signal to m electrodes of the n electrodes 10 and by controlling the second switch component 60 to transmit the second electric signal to at least two electrodes of the nm electrodes.

[0033] In some embodiments, as shown in FIG. 2 , the first switch component 50 includes n first switch units 501, the second switch component 60 includes n second switch units 60, the n first switch units 501 are electrically connected to the n electrodes 10 in a one-to-one relationship and are electrically connected to both the first electrical signal generating circuit 20 and the control signal generator 40, and the n second switch units 601 are electrically connected to the n electrodes 10 in a one-to-one relationship and are electrically connected to both the second electrical signal generating circuit 30 and the control signal generator 40.

[0034] Optionally, the n first switch units include first switch unit numbered 1 to first switch unit numbered n, the n second switch units include second switch unit numbered 1 to second switch unit numbered n, and the n electrodes include electrode numbered 1 to electrode numbered n.

[0035] The first switch unit numbered 1 to the first switch unit numbered n, and the second switch unit numbered 1 to the second switch unit numbered n are electrically connected to the electrode numbered 1 to the electrode numbered n, respectively. That is, the first switch unit numbered 1 and the second switch unit numbered 1 are both electrically connected to the electrode numbered 1, the first switch unit numbered 2 and the second switch unit numbered 2 are both electrically connected to the electrode numbered 2, ... and the first switch unit numbered n and the second switch unit numbered n are both electrically connected to the electrode numbered n.

[0036] Optionally, as shown in Figure 3, the electric field generator also includes a multiplex analog switch unit 70, which is electrically connected to all of the n first switch units 501, the n second switch units 601, and the control signal generator 40, and is used to switch the transmission path of the control signal output from the control signal generator 40. The multiplex analog switch unit 70 has advantages such as fast switching speed, no chattering, low power consumption, small size, reliable operation, and easy control.

[0037] In some embodiments, the electric field generator further includes at least one of: the first electric signal comprises an alternating voltage signal, a pulse voltage signal, or a square wave voltage signal; the second electric signal comprises a steady voltage signal or an oscillating voltage signal; the absolute value of the voltage amplitude of the first electric signal is between 0 and 500 volts; the absolute value of the voltage amplitude of the second electric signal is between 0 and 10 volts; the electric field strength is between 0.1 volts / centimeter and 10 volts / centimeter; and the frequency of the electric field is between 50 kilohertz and 500 kilohertz, and m is 1.

[0038] A steady voltage signal refers to a voltage whose magnitude does not change, while an oscillating voltage signal refers to a voltage whose total absolute value of positive or negative deviations does not exceed 10% of the rated value.

[0039] Optionally, the first electric signal generating circuit 20 includes an AC electric signal generating circuit, a pulse electric signal generating circuit, or a square wave electric signal generating circuit, where the AC electric signal generating circuit is used to output an AC voltage signal, the pulse electric signal generating circuit is used to output a pulse voltage signal, and the square wave electric signal generating circuit is used to output a square wave voltage signal.

[0040] In some embodiments, the absolute value of the voltage amplitude of the second electrical signal is 0 volts, 1 volt, or 5 volts.

[0041] As shown in Figure 3, n = 6 is set for illustrative purposes only, but of course n may be other values, such as 20, 30, 50, etc., and there is no limit to the number. The electric field generator applies an electric field to a target biological tissue region 80, which may be a target region of a patient. In Figure 3, all six electrodes (electrode 101, electrode 102, electrode 103, electrode 104, electrode 105, and electrode 106) are positioned outside of the target biological tissue region 80 (e.g., electrodes 101-106 may be positioned against the patient's body).

[0042] Specifically, the first electrical signal generating circuit 20 is electrically connected to six electrodes and is used to output a first electrical signal to the six electrodes, and the second electrical signal generating circuit 30 is electrically connected to six electrodes and is used to output a second electrical signal to the six electrodes.

[0043] Selectively, the control signal generator 40 controls one first switch unit 501 to transmit a first electrical signal to the electrode 101, controls all other first switch units 501 to turn off, and simultaneously controls the second switch unit 601 electrically connected to the electrode 101 to turn off, and controls the remaining second switch units 601 to transmit a second electrical signal to the electrodes 102 to 106.

[0044] That is, by controlling the electrodes 101 to have a first electric signal and the electrodes 102 to 106 to have a second electric signal, a first electric field is generated between the electrodes 101 and 102, a second electric field between the electrodes 101 and 103, a third electric field between the electrodes 101 and 104, a fourth electric field between the electrodes 101 and 105, and a fifth electric field between the electrodes 101 and 106. Here, the first electric signal applied to the electrode 101 is controlled to be a high voltage signal (for example, in the range of 0 to 500 V), and the second electric signals applied to the electrodes 102 to 106 are controlled to be low voltage signals (for example, 0 to 10 V). In other words, there are multiple potential differences between electrode 101 and electrodes 102 to 106, and multiple electric fields are generated, thereby expanding the coverage area of ​​the electric field in the target area of ​​the patient, and as a result, the strength of the electric field covering the target area of ​​the patient is improved, and the strength of the electric field covering the target biological tissue is also improved, and since the target biological tissue area includes the target biological tissue and normal biological tissue, the inhibitory effect on the division of the target biological tissue, such as diseased cells, is enhanced.

[0045] Of course, the present application is not particularly limited thereto; it is also possible to control the electrodes 101 and 102 to have a first electrical signal and the electrodes 103 to 106 to have a second electrical signal, or to control the electrode 101 to have a first electrical signal and the electrodes 103 and 105 to all have a second electrical signal, or to control the electrode 101 to have a first electrical signal and the electrodes 102, 104, and 106 to all have a second electrical signal, or to control the electrode 101 to have a first electrical signal and the electrodes 103, 104, and 105 to all have a second electrical signal, etc.

[0046] In an embodiment of the present application, the number of electrodes around the target biological tissue region can be flexibly selected based on the position of the target biological tissue within the target biological tissue region, and which electrodes have the second electrical signal can be controlled so that the coverage area of ​​the electric field generated between the electrode having the first electrical signal and the electrode having the second electrical signal can best match the position of the target biological tissue. Therefore, this embodiment can improve the compatibility between the coverage area of ​​the electric field and the position of the target biological tissue, the coverage rate of the target biological tissue by the electric field, flexibility, or adaptability, thereby increasing the strength of the electric field covering the target biological tissue and further improving the inhibitory effect on the division of the target biological tissue, such as diseased cells.

[0047] Furthermore, multiple electric fields can be generated between the electrode having the first electric signal and at least two electrodes having the second electric signal, and these electric fields overlap to enhance the electric field strength in the overlapping region of the electric fields. By rationally selecting the at least two electrodes having the second electric signal, the coverage rate of the overlapping region of the electric fields can be improved, which contributes to further improving the inhibitory effect on the division of the target biological tissue, such as diseased cells.

[0048] Optionally, still referring to Figure 3, one first switch unit 501 is controlled to transmit the first electrical signal to electrode 101, and all of the other first switch units 501 are controlled to be turned off, and simultaneously, the second switch unit 601 electrically connected to electrode 101 is controlled to be turned off, and the remaining second switch units 601 are controlled to be turned on sequentially according to the designed sequence, so as to transmit the second electrical signal to electrodes 102 to 106 sequentially according to the designed sequence. That is, electrode 101 continuously has the first electrical signal, while electrodes 102 to 106 have the second electrical signal sequentially according to the designed sequence (i.e., the second electrical signal is alternated among electrodes 102 to 106 in the designed sequence).

[0049] Optionally, the design order may include clockwise, counterclockwise, n-pointed star, or various jump or offset orders.

[0050] Optionally, the time interval during which each second switch unit 601 is sequentially turned on or off according to a design sequence is not less than 20 milliseconds and not more than 500 milliseconds.

[0051] Alternatively, electrode 101 may have a first electrical signal during a first time period, electrode 102 may have a second electrical signal during a second time period, electrode 103 may have a second electrical signal during a third time period, electrode 104 may have a second electrical signal during a fourth time period, electrode 105 may have a second electrical signal during a fifth time period, and electrode 106 may have a second electrical signal during a sixth time period. The first, second, third, fourth, fifth, and sixth time periods may be the same, different, or partially the same. This can be determined according to actual circumstances and is not particularly limited in this application.

[0052] In this embodiment, electrode 101 continuously applies a first electrical signal, while the remaining electrodes 102-106 sequentially apply a second electrical signal according to a designed sequence, and the voltage of the second electrical signals applied to the remaining electrodes 102-106 is controlled to be lower than the voltage of the first electrical signal. Compared to alternately applying a first electrical signal to each of the electrodes, this embodiment loads the first electrical signal to one electrode, the second electrical signal to the remaining electrodes, and alternates the second electrical signal between the remaining electrodes, thereby reducing power consumption and thereby reducing the power consumption of the electric field generator and extending the battery standby time for powering the electric field generator.

[0053] The electric fields generated by the electric field generator are used to destroy diseased cells or inhibit their division; these electric fields are referred to in this application as TTFs (Tumor Treating Fields), and TTFs can inhibit the growth of rapidly proliferating active cells (e.g., cancer cells) and destroy those active cells.

[0054] Optionally, still referring to FIG. 3, to prevent the electric field generating device from overheating, control the six first switch units 501 to be sequentially turned on according to the design sequence, and transmit the first electrical signal to the corresponding electrodes sequentially in the design sequence. At the same time, control the six second switch units 601 electrically connected to the corresponding electrodes to be sequentially turned off according to the design sequence, and sequentially turn on the second switch units 601 that are not turned off according to the design sequence, so as to sequentially transmit the second electrical signal to the electrodes that have not received the first electrical signal in the design sequence.

[0055] Optionally, the design sequence includes clockwise, counterclockwise, n-pointed star shape, or a sequence with various jumps and displacements.

[0056] Optionally, the time interval for each second switch unit 601 to be sequentially turned on or off according to the design sequence is 20 milliseconds or more and 500 milliseconds or less.

[0057] Optionally, the time when each electrode has the first electrical signal and the time when it has the second electrical signal can be set according to the actual situation and is not particularly limited in this application.

[0058] That is, the electrodes 101 to 106 have the first electrical signal and the second electrical signal sequentially according to the design sequence, so as to further reduce the power consumption of the electric field generating device and prevent the electric field generating device from overheating.

[0059] Based on the same inventive concept, in the embodiments of this application, a control method for an electric field generating device applied to the electric field generating device in any one of the above selectable embodiments is provided. The control method for the electric field generating device is controlling the electrical signal generator to output a first electrical signal to m electrodes out of n electrodes, and controlling the electrical signal generator to output a second electrical signal to at least two electrodes out of n - m electrodes, including generating an electric field between the electrodes having the first electrical signal and the electrodes having the second electrical signal. n is an integer greater than or equal to 3,
≦m<n, and m is an integer. The electric field generating device includes an electrical signal generator and n electrodes that are electrically connected, and the voltage of the second electrical signal is lower than the voltage of the first electrical signal.

[0060] According to the control method of the electric field generating device provided by the embodiments of the present application, the n electrodes are arranged in a manner designed around the target biological tissue region, and the electrical signal generator is controlled to output a first electrical signal to m electrodes among the n electrodes, and the electrical signal generator is controlled to output a second electrical signal to at least two electrodes among the n - m electrodes, where n is an integer greater than or equal to 3, 1 ≤ m < n, and m is an integer. In the embodiments of the present application, based on the position of the target biological tissue within the target biological tissue region, the number of electrodes around the target biological tissue region can be flexibly selected, and by controlling which electrodes have the second electrical signal, the coverage area of the electric field generated between the electrodes having the first electrical signal and the electrodes having the second electrical signal can be made to best match the position of the target biological tissue. Therefore, this embodiment can improve the degree of fit between the coverage area of the electric field and the position of the target biological tissue, the coverage rate of the target biological tissue by the electric field, flexibility or adaptability. As a result, the intensity of the electric field covering the target biological tissue can be increased, and the inhibitory effect on the division of the target biological tissue such as diseased cells can be further enhanced.

[0061] Between the electrodes having the first electrical signal and at least two electrodes having the second electrical signal, a plurality of electric fields can be generated, and the superposition of these electric fields strengthens the electric field intensity in the electric field superposition region. By reasonably selecting at least two electrodes having the second electrical signal, the coverage rate of the target biological tissue by the electric field superposition region can be improved, which contributes to further enhancing the inhibitory effect on the division of the target biological tissue such as diseased cells. [[ID=​​In some embodiments, controlling an electrical signal generator to output a first electrical signal to m electrodes of the n electrodes, and controlling the electrical signal generator to output a second electrical signal to at least two electrodes of the nm electrodes to generate an electric field between the electrode having the first electrical signal and the electrode having the second electrical signal, comprises: controlling a first switch component to transmit a first electrical signal to m of the n electrodes and a second switch component to transmit a second electrical signal to at least two of the nm electrodes, thereby generating an electric field between the electrode having the first electrical signal and the electrode having the second electrical signal; The electric signal generator includes a first electric signal generating circuit and a second electric signal generating circuit, and the electric field generating device further includes a first switch component and a second switch component, the first switch component being electrically connected to all of the first electric signal generating circuit, the control signal generator, and the n electrodes, and the second switch component being electrically connected to all of the second electric signal generating circuit, the control signal generator, and the n electrodes.

[0063] In some embodiments, controlling a first switch component to transmit a first electrical signal to m of the n electrodes and controlling a second switch component to transmit a second electrical signal to at least two of the nm electrodes to generate an electric field between the electrode having the first electrical signal and the electrode having the second electrical signal comprises: The method includes controlling a first switch unit numbered 1 to transmit a first electrical signal to electrode numbered 1 of the n electrodes, controlling all of first switch units numbered 2 to n to turn them off, and simultaneously turning off a second switch unit numbered 1 electrically connected to electrode numbered 1, and controlling at least two second switch units numbered 2 to n to transmit a second electrical signal to at least two of the n electrodes excluding electrode numbered 1.

[0064] The first switch component includes n first switch units, the second switch component includes n second switch units, the n first switch units include first switch unit numbered 1 to first switch unit numbered n, the n second switch units include second switch unit numbered 1 to second switch unit numbered n, and the n electrodes include electrode numbered 1 to electrode numbered n.

[0065] The first switch unit numbered 1 to the first switch unit numbered n, and the second switch unit numbered 1 to the second switch unit numbered n are electrically connected to the electrode numbered 1 to the electrode numbered n, respectively. That is, the first switch unit numbered 1 and the second switch unit numbered 1 are both electrically connected to the electrode numbered 1, the first switch unit numbered 2 and the second switch unit numbered 2 are both electrically connected to the electrode numbered 2, ... and the first switch unit numbered n and the second switch unit numbered n are both electrically connected to the electrode numbered n.

[0066] 3, n=6, but n may be other numbers, such as 20, 30, 50, etc., and is not limited to this number. An electric field generator applies an electric field to a target biological tissue region 80, which may be a target region of a patient. In FIG. 3, six electrodes (electrode 101, electrode 102, electrode 103, electrode 104, electrode 105, and electrode 106), i.e., electrodes numbered 1 through 6, are all positioned outside the target biological tissue region 80 (e.g., electrodes 101 through 106 may be configured to be positioned against the patient's body). In FIG. 3, six first switch units 501, i.e., first switch unit 1 through first switch unit 6, are shown, and six second switch units 601, i.e., second switch unit 1 through second switch unit 6.

[0067] Specifically, the first electrical signal generating circuit 20 is electrically connected to six electrodes and is used to output a first electrical signal to the six electrodes, and the second electrical signal generating circuit 30 is electrically connected to six electrodes and is used to output a second electrical signal to the six electrodes.

[0068] Selectively, the control signal generator 40 controls one first switch unit 501 to transmit a first electrical signal to the electrode 101, controls all other first switch units 501 to turn off, and simultaneously controls the second switch unit 601 electrically connected to the electrode 101 to turn off, and controls the remaining second switch units 601 to transmit a second electrical signal to the electrodes 102 to 106.

[0069] In other words, by controlling electrode 101 to have a first electric signal and electrodes 102 to 106 to have a second electric signal, a first electric field is generated between electrodes 101 and 102, a second electric field is generated between electrodes 101 and 103, a third electric field is generated between electrodes 101 and 104, a fourth electric field is generated between electrodes 101 and 105, and a fifth electric field is generated between electrodes 101 and 106.

[0070] Here, the first electrical signal applied to electrode 101 is controlled to be a high-voltage signal (e.g., in the range of 0 to 500 V), and the second electrical signal applied to electrodes 102 to 106 is controlled to be a low-voltage signal (e.g., 0 to 10 V). That is, multiple potential differences exist between electrode 101 and electrodes 102 to 106, generating multiple electric fields. These electric fields overlap, strengthening the electric field strength in the overlapping region. Rational selection of at least two electrodes having the second electrical signal can improve the coverage of the target biological tissue by the overlapping region of the electric fields, thereby contributing to further improving the inhibitory effect on the division of target biological tissue, such as diseased cells.

[0071] Of course, the present application is not particularly limited thereto; it is also possible to control the electrodes 101 and 102 to have a first electrical signal and the electrodes 103 to 106 to have a second electrical signal, or to control the electrode 101 to have a first electrical signal and the electrodes 103 and 105 to all have a second electrical signal, or to control the electrode 101 to have a first electrical signal and the electrodes 102, 104, and 106 to all have a second electrical signal, or to control the electrode 101 to have a first electrical signal and the electrodes 103, 104, and 105 to all have a second electrical signal, etc.

[0072] In an embodiment of the present application, the number of electrodes around the target biological tissue region can be flexibly selected based on the position of the target biological tissue within the target biological tissue region, and which electrodes have the second electrical signal can be controlled so that the coverage area of ​​the electric field generated between the electrode having the first electrical signal and the electrode having the second electrical signal can best match the position of the target biological tissue. Therefore, this embodiment can improve the compatibility between the coverage area of ​​the electric field and the position of the target biological tissue, the coverage rate of the target biological tissue by the electric field, flexibility, or adaptability, thereby increasing the strength of the electric field covering the target biological tissue and further improving the inhibitory effect on the division of the target biological tissue, such as diseased cells.

[0073] In some embodiments, controlling a first switch component to transmit a first electrical signal to m of the n electrodes and controlling a second switch component to transmit a second electrical signal to at least two of the nm electrodes to generate an electric field between the electrode having the first electrical signal and the electrode having the second electrical signal comprises: The method includes controlling a first switch unit numbered 1 to transmit a first electrical signal to electrode numbered 1 of the n electrodes, controlling all of first switch units numbered 2 through n to turn them off, and simultaneously turning off a second switch unit numbered 1 electrically connected to the electrode numbered 1, controlling at least two second switch units numbered 2 through n to turn them on sequentially according to a designed sequence, and transmitting a second electrical signal sequentially to at least two electrodes of the n electrodes excluding the electrode numbered 1 according to the designed sequence.

[0074] The first switch component includes n first switch units, the second switch component includes n second switch units, the n first switch units include first switch unit numbered 1 to first switch unit numbered n, the n second switch units include second switch unit numbered 1 to second switch unit numbered n, and the n electrodes include electrode numbered 1 to electrode numbered n.

[0075] The first switch unit numbered 1 to the first switch unit numbered n, and the second switch unit numbered 1 to the second switch unit numbered n are electrically connected to the electrode numbered 1 to the electrode numbered n, respectively. That is, the first switch unit numbered 1 and the second switch unit numbered 1 are both electrically connected to the electrode numbered 1, the first switch unit numbered 2 and the second switch unit numbered 2 are both electrically connected to the electrode numbered 2, ... and the first switch unit numbered n and the second switch unit numbered n are both electrically connected to the electrode numbered n.

[0076] In this embodiment, one electrode of the n electrodes continuously receives a first electric signal, while the remaining electrodes sequentially receive a second electric signal according to a designed sequence, and the voltage of the second electric signal of the remaining electrodes is controlled to be lower than the voltage of the first electric signal. Compared to alternately loading the first electric signal at all voltages, this embodiment loads the first electric signal to one electrode, loads the second electric signal to the remaining electrodes, and alternates the second electric signal between the remaining electrodes, thereby reducing power consumption and thereby reducing the power consumption of the electric field generator.

[0077] Optionally, still referring to Figure 3, one first switch unit 501 is controlled to transmit the first electrical signal to electrode 101, and all of the other first switch units 501 are controlled to be turned off, and simultaneously, the second switch unit 601 electrically connected to electrode 101 is controlled to be turned off, and the remaining second switch units 601 are controlled to be turned on sequentially according to the designed sequence, so as to transmit the second electrical signal to electrodes 102 to 106 sequentially according to the designed sequence. That is, electrode 101 continuously has the first electrical signal, while electrodes 102 to 106 have the second electrical signal sequentially according to the designed sequence (i.e., the second electrical signal is alternated among electrodes 102 to 106 in the designed sequence).

[0078] Optionally, the design order may include clockwise, counterclockwise, n-pointed star, or various jump or offset orders.

[0079] Optionally, the time interval during which each second switch unit 601 is sequentially turned on or off according to a design sequence is not less than 20 milliseconds and not more than 500 milliseconds.

[0080] Alternatively, electrode 101 may have a first electrical signal during a first time period, electrode 102 may have a second electrical signal during a second time period, electrode 103 may have a second electrical signal during a third time period, electrode 104 may have a second electrical signal during a fourth time period, electrode 105 may have a second electrical signal during a fifth time period, and electrode 106 may have a second electrical signal during a sixth time period. The first, second, third, fourth, fifth, and sixth time periods may be the same, different, or partially the same. This can be determined according to actual circumstances and is not particularly limited in this application.

[0081] In this embodiment, electrode 101 continuously applies a first electrical signal, while the remaining electrodes 102-106 sequentially apply a second electrical signal according to a designed sequence, and the voltage of the second electrical signals applied to the remaining electrodes 102-106 is controlled to be lower than the voltage of the first electrical signal. Compared to alternately applying a first electrical signal to each of the electrodes, this embodiment loads the first electrical signal to one electrode, the second electrical signal to the remaining electrodes, and alternates the second electrical signal between the remaining electrodes, thereby reducing power consumption and thereby reducing the power consumption of the electric field generator and extending the battery standby time for powering the electric field generator.

[0082] In some embodiments, controlling a first switch component to transmit a first electrical signal to m of the n electrodes and controlling a second switch component to transmit a second electrical signal to at least two of the nm electrodes to generate an electric field between the electrode having the first electrical signal and the electrode having the second electrical signal comprises: when m is 1, the method includes controlling n first switch units to be sequentially turned on in accordance with the design sequence, so that n electrodes receive a first electrical signal in accordance with the design sequence, and controlling n second switch units to be sequentially turned off in accordance with the design sequence, and further controlling each combination of second switch units to be sequentially turned on in accordance with the design sequence, so that a combination of electrodes corresponding to each combination of second switch units receives a second electrical signal in accordance with the design sequence, wherein the combination of second switch units includes at least two second switch units among the n-1 second switch units that are not turned off, and the combination of electrodes includes at least two electrodes that do not receive the first electrical signal; The first switch component includes n first switch units, and the second switch component includes n second switch units.

[0083] In this embodiment, the n electrodes are controlled to have a first electrical signal (high voltage signal) and a second electrical signal (low voltage signal) in sequence according to a designed order, thereby further reducing the power consumption of the electric field generator and preventing overheating of the electric field generator.

[0084] 3, for example, to prevent the electric field generating device from overheating, the six first switch units 501 are controlled to be turned on sequentially in a designed order, so that the first electrical signal is transmitted to the corresponding electrodes sequentially in the designed order, and at the same time, the six second switch units 601 electrically connected to the corresponding electrodes are controlled to be turned off sequentially in the designed order, and the second switch units 601 that are not turned off are turned on sequentially in the designed order, so that the second electrical signal is transmitted to the electrodes that do not receive the first electrical signal sequentially in the designed order.

[0085] Optionally, the design order may include clockwise, counterclockwise, n-pointed star, or various jump or offset orders.

[0086] Optionally, the time interval during which each second switch unit 601 is sequentially turned on or off according to a design sequence is not less than 20 milliseconds and not more than 500 milliseconds.

[0087] Optionally, the time when each electrode has the first electrical signal and the time when each electrode has the second electrical signal can be set according to the actual situation, and is not particularly limited in the present application.

[0088] That is, the electrodes 101 to 106 sequentially receive the first and second electric signals according to the design sequence, thereby further reducing the power consumption of the electric field generator and preventing the electric field generator from overheating.

[0089] In some embodiments, the time interval during which each second switch unit 601 is sequentially turned on or off according to the designed sequence is not less than 20 milliseconds and not more than 500 milliseconds.

[0090] The target biological tissue region includes target biological tissue and normal biological tissue, and the target biological tissue includes diseased cells, tumors, lesions, etc.

[0091] To further verify the technical effect of the present application, in an example where the target biological tissue is a tumor, two-dimensional modeling is performed on the target biological tissue and n electrodes arranged around it, and three-dimensional modeling is performed on the human thoracic cavity and the tumor within the human thoracic cavity.

[0092] 2D model: The finite element modeling process is as follows:

[0093] First, a geometric model is constructed in COMSOL. A circle with a diameter of 40 mm (millimeters) is created as the tumor (target biological tissue 81), and a square with a side length of 200 mm is created as the target biological tissue region 80. The center of the square is overlapped with the center of the tumor, and the part outside the square represents normal biological tissue 82 other than the tumor. Straight lines with a length of 80 mm (h1 in Figure 4 is 80 mm) are placed as electrodes at the centers of each of the four sides of the square. The constructed model is shown in Figure 4, and the four electrodes are identified as electrode 107, electrode 108, electrode 109, and electrode 110, respectively.

[0094] Setting of electrical parameters of the material: The tumor region (target biological tissue 81) has a conductivity of 0.24 S / m (Siemens per meter) and a dielectric constant of 2000, while the surrounding normal biological tissue 82 has a conductivity of 0.11 S / m and a dielectric constant of 1980.

[0095] Application of voltage waveform: In this embodiment, a continuous sine wave with a frequency of 150 kHz (kilohertz) and a peak-to-peak value of 120 V (volts) is applied, i.e., the first electric signal generating circuit serves as an AC electric signal generating circuit and outputs an AC voltage signal, the frequency of which is 150 kHz (kilohertz) and the peak-to-peak value of which is 120 V (volts).

[0096] The first electric signal output from the first electric signal generating circuit is a high-voltage signal, and the second electric signal output from the second electric signal generating circuit is a low-voltage signal.

[0097] Electrode 107 is set as a power receiving terminal used to receive the first electrical signal output from the first electrical signal generating circuit, and electrodes 108 to 110 are set as ground terminals used to receive the second electrical signal output from the second electrical signal generating circuit.

[0098] Based on the above configuration, see the following three cases:

[0099] 1. In the case of single-electrode grounding, electrode 107 is set to receive a first electrical signal (high voltage signal) output from a first electrical signal generating circuit, and electrode 108 is set to receive a second electrical signal (low voltage signal) output from a second electrical signal generating circuit. In other words, electrode 107 receives the power supply voltage, and electrode 108 is grounded.

[0100] As shown in the electric field strength distribution diagram for the single grounded electrode in Figure 5a, calculations reveal that the average electric field strength in the tumor region is 1.6075 V / cm (volts per centimeter).

[0101] 2. In the case of dual-electrode grounding 1, electrode 107 receives a first electrical signal (high voltage signal) output from a first electrical signal generating circuit, and electrodes 108 and 109 both receive a second electrical signal (low voltage signal) output from a second electrical signal generating circuit. That is, electrode 107 receives the power supply voltage, and electrodes 108 and 109 are both grounded.

[0102] As shown in the electric field strength distribution diagram for the dual-electrode grounding case in Figure 5b, the calculation revealed that the average electric field strength in the tumor region was 1.6775 V / cm, which was an improvement of 4.35% compared with the single-electrode grounding case.

[0103] 3. In the case of dual-electrode grounding 2, electrode 107 receives a first electrical signal (high voltage signal) output from a first electrical signal generating circuit, and electrodes 108 and 110 both receive a second electrical signal (low voltage signal) output from a second electrical signal generating circuit. That is, electrode 107 receives the power supply voltage, and electrodes 108 and 110 are both grounded.

[0104] As shown in the electric field strength distribution diagram for the dual-electrode grounding case in Figure 5c, the calculation revealed that the average electric field strength in the tumor region was 1.6775 V / cm, which was an improvement of 4.35% compared with the single-electrode grounding case.

[0105] The average electric field strengths for different tumors are shown in Table 1. JPEG0007783470000001.jpg34170

[0106] From the above, it can be seen that for a constant number of electrodes with high voltage signals, the more electrodes with low voltage signals, the greater the average electric field strength in the tumor region.

[0107] In this embodiment, the coverage range of the electric field in the target biological tissue can be expanded, and the strength of the electric field covering the target biological tissue area can be increased, thereby improving the strength of the electric field covering the target biological tissue and enhancing the inhibitory effect on the division of target biological tissue such as diseased cells.

[0108] 3D model: The finite element modeling process is as follows:

[0109] Construction of the human thoracic cavity: First, the rough shape of each actual tissue part is constructed using Rhino3D NURBS 7, and then the boundary contours are corrected by comparing slices from multiple CT (Computed Tomography) images, finally recreating a real human body model. The modeling content includes skin, fat, muscle, skeleton, lungs, heart, and liver, but some overly detailed tissues (such as connective tissue and pleura) that have similar electrical parameters and are difficult to model are integrated into the muscle tissue. The final constructed model is shown in Figure 6.

[0110] Construction of Individual Electrodes: Each electrode is modeled as a two-layer structure (i.e., first layer 91 and second layer 92 in Figure 7), where the larger layer (first layer 91 in Figure 7) is a gel layer placed close to the skin, with a diameter of 21 mm and a thickness between 0.5 and 2 mm, while the smaller layer (second layer 92 in Figure 7) is an insulating layer with a diameter of 20 mm and a thickness of 1 mm. A ceramic with a high dielectric constant (approximately 10,000) was selected for the insulating layer, and the electric field is transmitted to the human body via the ceramic and gel layers.

[0111] Electrode array construction: The electrode array is composed of multiple electrodes, and can be composed of multiple different electrode arrays, for example, 5 electrodes, 10 electrodes, 15 electrodes, or other numbers of electrodes. Figures 8a and 8b show the layout of an electrode array applied to human thoracic lung cancer treatment, and Figure 8a shows the layout of an initial electrode array.

[0112] As shown in FIG. 8a, electrode arrays used in lung cancer treatment are divided into three types: a precordial electrode array (first electrode array 201 located on the precordial region of the human body in FIG. 8a), a dorsal electrode array (second electrode array 202 located on the dorsal region of the human body in FIG. 8a), and a lateral electrode array (third electrode array 203 located on the lateral region of the human body in FIG. 8a). Because the precordial and dorsal regions have large skin areas, the precordial and dorsal electrode arrays each contain many electrodes. Specifically, the precordial electrode array (i.e., first electrode array 201) and the dorsal electrode array (second electrode array 202) each contain 20 electrodes. On the other hand, because the placement locations on both sides of the human body are limited, the electrode arrays placed on both sides of the body contain fewer electrodes. That is, a third electrode array 203 containing 13 electrodes is placed on each side of the human body. 8a, a first electrode array 201 is placed on the front chest of the human body, a second electrode array 202 is placed on the back of the human body, a third electrode array 203 is placed on the left side of the body, and another third electrode array 203 is placed on the right side of the body. That is, four electrode arrays (i.e., first electrode array 201, second electrode array 202, third electrode array 203, third electrode array 203) are placed on the front chest, back, left side, and right side of the human body.

[0113] Tumor Model Construction: A total of four virtual tumor models were constructed, as shown in Figures 9a, 9b, 9c, and 9d. The target biological tissues 81 in Figures 9a, 9b, 9c, and 9d are designated as tumors T1, T2, T3, and T4, respectively. The sizes and locations of the four tumors are indicated by dotted circles in Figures 9a, 9b, 9c, and 9d. Tumor T1 in Figure 9a is located in the middle lobe of the right lung and has a diameter of 40 mm. Tumor T2 in Figure 9b is located in the middle lobe of the right lung, tumor T3 in Figure 9c is located in the middle lobe of the left lung, and tumor T4 in Figure 9d is located in the lower lobe of the left lung. The diameters of tumors T2, T3, and T4 are all 60 mm.

[0114] After the model construction was completed, meshing was performed using HyperMesh 14.0, and individual meshes of different tissues, such as electrodes, gel, skin, fat, skeleton, muscle, lungs, heart, liver, and tumor, were extracted. These were then imported one by one into COMSOL Multiphysics 5.5, and the current module was used to solve the electromagnetic quasi-static equations of Maxwell's equations.

[0115] Material electrical parameter settings: As shown in Table 2, the electrical conductivity and permittivity of each tissue component are set to the corresponding values.

[0116] JPEG0007783470000002.jpg29170

[0117] Simulation power settings: Frequency domain simulation is adopted. The frequency is set to 150 kHz, and the normal current density on each electrode is 100 mA / cm. 2 (milliamperes per square centimeter).

[0118] Electric field intensity evaluation method: COMSOL was used to calculate the electric field intensity-volume histogram (EVH) of the tumor site. This is shown in Figure 10, where the horizontal axis is the magnitude of the electric field intensity (V / cm) and the vertical axis is the volume occupancy rate (%) within the tumor. Points on the curve indicate the volume occupancy rate within the tumor that has a value greater than the electric field intensity value corresponding to that point. The area under the entire curve represents the amount of electric field intensity coverage within the tumor site. This area is obtained by integrating the curve, and this area value is E AUC It is written as:

[0119] The first electric signal output from the first electric signal generating circuit is a high-voltage signal, and the second electric signal output from the second electric signal generating circuit is a low-voltage signal.

[0120] The anterior chest electrode array is set as a power receiving terminal used to receive the first electrical signal output from the first electrical signal generating circuit, and the back electrode array, left electrode array, and right electrode array are set as ground terminals used to receive the second electrical signal output from the second electrical signal generating circuit.

[0121] In tumor T1 and tumor T2, the simulation results show that the coverage of the electric field intensity E AUC The values ​​are compared as shown in Table 3, and the two cases in Table 3 are as follows:

[0122] 1. Single electrode array grounding: The precordial electrode array (first electrode array 201 shown in FIG. 8a) is set to receive a first electrical signal (high voltage signal) output from a first electrical signal generating circuit, and the back electrode array (second electrode array 202 shown in FIG. 8a) is set to receive a second electrical signal (low voltage signal) output from a second electrical signal generating circuit. In other words, the precordial electrode array receives the power supply voltage, and the back electrode array is grounded.

[0123] 2. In the case of dual electrode array grounding: The precordial electrode array (first electrode array 201 shown in FIG. 8a) is set to receive a first electrical signal (high voltage signal) output from a first electrical signal generating circuit, and the dorsal electrode array (second electrode array 202 shown in FIG. 8a) and the left-side electrode array (third electrode array 203 shown in FIG. 8a) are both set to receive a second electrical signal (low voltage signal) output from a second electrical signal generating circuit. In other words, the precordial electrode array receives the power supply voltage, and the dorsal electrode array and the left-side electrode array are both grounded.

[0124] From the results in Table 3, the electric field strength coverage amount E AUC The value of is the electric field strength coverage amount E when the single electrode array is grounded. AUC This is higher than the value of , which indicates that the electric field intensity coverage has improved. As can be seen from Table 3, for tumor T1, the electric field intensity coverage E AUC increases by 1.22% compared to when the single-electrode array was grounded. Also, for tumor T2, the electric field intensity coverage E AUC increases by 1.23% compared to when the single electrode array is grounded.

[0125] Schematic diagrams showing the electric field distribution in the horizontal plane of the human thoracic cavity for tumor T1 are shown in Figures 11a and 11b, with the tumor center selected as the location. As is clear from the figures, the electric field intensity located on the left side of the body in Figure 11b (the left part of the figure) is stronger than the electric field intensity located on the left side in Figure 11a.

[0126] Schematic diagrams showing the electric field distribution in the horizontal plane of the human thoracic cavity for tumor T2 are shown in Figures 12a and 12b, with the tumor center selected as the location. As is clear from the figures, the electric field intensity located on the left side of the body in Figure 12b (the left part of the figure) is stronger than the electric field intensity located on the left side in Figure 12a.

[0127] JPEG0007783470000003.jpg36170

[0128] In tumors T3 and T4, the simulation results show that the electric field intensity coverage E AUC The values ​​are compared as shown in Table 4, and the two cases in Table 4 are as follows:

[0129] 1. Single electrode array grounding: The precordial electrode array (first electrode array 201 shown in FIG. 8a) is set to receive a first electrical signal (high voltage signal) output from a first electrical signal generating circuit, and the back electrode array (second electrode array 202 shown in FIG. 8a) is set to receive a second electrical signal (low voltage signal) output from a second electrical signal generating circuit. In other words, the precordial electrode array receives the power supply voltage, and the back electrode array is grounded.

[0130] 2. In the case of dual electrode array grounding: The precordial electrode array (first electrode array 201 shown in FIG. 8a) is set to receive a first electrical signal (high voltage signal) output from a first electrical signal generating circuit, and the dorsal electrode array (second electrode array 202 shown in FIG. 8a) and the right-side electrode array (third electrode array 203 shown in FIG. 8a) are both set to receive a second electrical signal (low voltage signal) output from a second electrical signal generating circuit. In other words, the precordial electrode array receives the power supply voltage, and the dorsal electrode array and the right-side electrode array are both grounded.

[0131] From the results in Table 4, the electric field strength coverage amount E AUC The value of is the electric field strength coverage amount E when the single electrode array is grounded. AUC This is higher than the value of , which indicates that the electric field intensity coverage has improved. As can be seen from Table 3, for tumor T3, the electric field intensity coverage E AUC increases by 16.20% compared to the single-electrode array grounding. Also, for tumor T4, the electric field intensity coverage E AUC increases by 15.79% compared to when the single electrode array is grounded.

[0132] Schematic diagrams showing the electric field distribution in the horizontal plane of the human thoracic cavity for tumor T3 are shown in Figures 13a and 13b, with the tumor center selected as the location. As is clear from the figures, the electric field intensity located on the right side of the human body (the right part of the figure) in Figure 13b is stronger than the electric field intensity located on the right side in Figure 13a.

[0133] Schematic diagrams showing the electric field distribution in the horizontal plane of the human thoracic cavity for tumor T4 are shown in Figures 14a and 14b, with the tumor center selected as the location. As is clear from the figures, the electric field intensity located on the right side of the body in Figure 14b (the right part of the figure) is stronger than the electric field intensity located on the right side in Figure 14a.

[0134] JPEG0007783470000004.jpg36170

[0135] As can be seen from the above results, the method of grounding both the electrode array near the tumor and the electrode array on the back can improve the electric field strength in the tumor area compared to the method of grounding only the electrode array on the back, increasing the electric field strength coverage of the electric field generated between each electrode array and further enhancing the inhibitory effect on the division of target biological tissues such as diseased cells.

[0136] Also, as shown in Figure 8b, if two electrode arrays are attached to the left and right sides of the back in tumors T1, T2, T3, and T4, the two cases in Table 5 below will result.

[0137] 1. In the case of single electrode array grounding: The precordial electrode array (first electrode array 201 shown in FIG. 8a) is set to receive a first electrical signal (high voltage signal) output from a first electrical signal generating circuit, and the back electrode array (second electrode array 202 shown in FIG. 8a) is set to receive a second electrical signal (low voltage signal) output from a second electrical signal generating circuit. In other words, the precordial electrode array receives the power supply voltage, and the back electrode array is grounded.

[0138] 2. In the case of dual electrode array grounding: The electrode array on the precordial region (first electrode array 201 shown in FIG. 8a) is set to receive a first electrical signal (high-voltage signal) output from a first electrical signal generating circuit, and the electrode arrays on the back (two second electrode arrays 202 shown in FIG. 8b) are both set to receive a second electrical signal (low-voltage signal) output from a second electrical signal generating circuit. In other words, the electrode array on the precordial region receives the power supply voltage, and the electrode arrays on the back are grounded.

[0139] It is clear that the method of placing two second electrode arrays 202 with low-voltage signals on the back simultaneously can similarly improve the electric field strength at the tumor site compared to the method of placing only one second electrode array 202 with low-voltage signals on the back. As shown in Table 5, for the four types of tumor models mentioned above, the field coverage E AUC A comparison of the values ​​is shown.

[0140] As can be seen from Table 5, the electric field intensity coverage E for tumor T1 when the bipolar electrode array is grounded AUC is improved by 4.12% compared to the single-electrode array grounding. AUC is improved by 4.49% compared to the single-electrode array grounding. AUC is improved by 15.08% compared to the single-electrode array grounding. And the electric field intensity coverage E AUC is improved by 9.57% compared to the single electrode array grounding case.

[0141] Schematic diagrams showing the electric field distribution in the horizontal plane of the human thoracic cavity for tumor T1 are shown in Figures 11a and 11c, with the tumor center selected as the location. As is clear from the figures, the electric field intensity located on the back side of the human body (upper part in the figure) in Figure 11c is stronger than the electric field intensity located on the upper part in Figure 11a.

[0142] Schematic diagrams showing the electric field distribution in the horizontal plane of the human thoracic cavity for tumor T2 are shown in Figures 12a and 12c, with the tumor center selected as the location. As can be seen from the figures, the electric field intensity at the back side of the human body (upper part in the figure) in Figure 12c is stronger than the electric field intensity at the upper part in Figure 12a.

[0143] Schematic diagrams showing the electric field distribution in the horizontal plane of the human thoracic cavity for tumor T3 are shown in Figures 13a and 13c, with the tumor center selected as the location. As can be seen from the figures, the electric field intensity at the back side of the human body (upper part of the figure) in Figure 13c is stronger than the electric field intensity at the upper part of Figure 13a.

[0144] Schematic diagrams showing the electric field distribution in the horizontal plane of the human thoracic cavity for tumor T4 are shown in Figures 14a and 14c, with the tumor center selected as the location. As is clear from the figures, the electric field intensity at the back side of the human body (upper part in the figure) in Figure 14c is stronger than the electric field intensity at the upper part in Figure 14a.

[0145] JPEG0007783470000005.jpg36170

[0146] From the above, it can be seen that when the number of electrodes with high voltage signals remains the same, the greater the number of electrodes with low voltage signals, the greater the coverage of the electric field strength generated between each electrode, thereby further enhancing the inhibitory effect on the division of target biological tissues such as diseased cells.

[0147] In this embodiment, when the number of electrodes having the first electrical signal (high-voltage signal) remains the same, the more electrodes having the second electrical signal (low-voltage signal), the stronger the electric field generated between the electrodes having the first electrical signal and the electrodes having the second electrical signal, and the wider the coverage area of ​​the electric field in the target biological tissue region, which increases the strength of the electric field covering the target biological tissue region and further improves the inhibitory effect on the division of target biological tissue, such as diseased cells.

[0148] Based on the same inventive concept, an embodiment of the present application provides a computer-readable storage medium having a computer program stored thereon, the computer program realizing the method for controlling an electric field generating device in any one of the above selectable embodiments when executed by a processor.

[0149] The computer-readable storage medium provided in the examples of the present application is applicable to various selectable embodiments of the control method for the electric field generating device described above, and the computer-readable storage medium may be a non-volatile readable storage medium or a volatile readable storage medium, which will not be described again here.

[0150] By applying the embodiments of the present application, at least the following effects (1) to (4) can be achieved.

[0151] (1) According to the electric field generating device provided by the embodiments of the present application, n electrodes are arranged in a designed manner around the target biological tissue region, and the electrical signal generator is controlled to output a first electrical signal to m electrodes out of the n electrodes, and the electrical signal generator is controlled to output a second electrical signal to at least two electrodes out of the n - m electrodes, where n is an integer greater than or equal to 3, 1 ≤ m < n, and m is an integer. In the embodiments of the present application, based on the position of the target biological tissue within the target biological tissue region, the number of electrodes around the target biological tissue region can be flexibly selected, and by controlling which electrodes have the second electrical signal, the coverage area of the electric field generated between the electrodes having the first electrical signal and the electrodes having the second electrical signal can be made to best match the position of the target biological tissue. Therefore, this embodiment can improve the degree of fit between the coverage area of the electric field and the position of the target biological tissue, the coverage rate of the target biological tissue by the electric field, flexibility or adaptability. As a result, the intensity of the electric field covering the target biological tissue can be increased, and the inhibitory effect on the division of the target biological tissue such as diseased cells can be further enhanced.

[0152] And between the electrodes having the first electrical signal and at least two electrodes having the second electrical signal, a plurality of electric fields can be generated, and the superposition of these electric fields strengthens the electric field intensity in the superposition region of the electric fields. By reasonably selecting at least two electrodes having the second electrical signal, the coverage rate of the target biological tissue by the superposition region of the electric fields can be improved, which contributes to further improving the inhibitory effect on the division of the target biological tissue such as diseased cells.

[0153] (2) In this embodiment, one electrode of the n electrodes continuously receives a first electric signal, while the remaining electrodes sequentially receive a second electric signal according to a designed sequence, and the voltage of the second electric signal of the remaining electrodes is controlled to be lower than the voltage of the first electric signal. Compared to alternately loading the first electric signal to all of the voltages, this embodiment loads the first electric signal to one electrode, loads the second electric signal to the remaining electrodes, and alternates the second electric signal between the remaining electrodes, thereby reducing power consumption and thereby reducing the power consumption of the electric field generator.

[0154] (3) In this embodiment, the n electrodes are controlled to have a first electrical signal (high voltage signal) and a second electrical signal (low voltage signal) in sequence according to the design sequence, thereby further reducing the power consumption of the electric field generator and preventing the electric field generator from overheating.

[0155] (4) In this embodiment, when the number of electrodes having the first electrical signal (high-voltage signal) remains constant, the more electrodes having the second electrical signal (low-voltage signal), the stronger the electric field generated between the electrodes having the first electrical signal and the electrodes having the second electrical signal, and the wider the coverage area of ​​the electric field in the target biological tissue region, which increases the strength of the electric field covering the target biological tissue region and further improves the inhibitory effect on the division of target biological tissue, such as diseased cells.

[0156] As will be understood by those skilled in the art, the various operations, methods, process steps, acts, and schemes previously discussed herein may be interchanged, modified, combined, or deleted, and other steps, acts, and schemes within the various operations, methods, and processes previously discussed herein may also be interchanged, modified, rearranged, broken down, combined, or deleted. Furthermore, the various operations, methods, process steps, acts, and schemes disclosed herein that are similar to those in the prior art may also be interchanged, modified, rearranged, broken down, combined, or deleted.

[0157] The terms "first" and "second" are used for descriptive purposes only and should not be understood as indicating or suggesting the relative importance or quantity of the indicated technical features. Thus, a feature qualified as "first" or "second" can expressly or implicitly indicate the inclusion of one or more of that feature. In the description of this application, unless expressly stated otherwise, "plurality" means two or more.

[0158] Note that although the steps in the flowcharts of the drawings are shown in the order indicated by the arrows, these steps are not necessarily executed in the order indicated by the arrows. Unless otherwise clearly stated in the text, there is no strict order to the execution of these steps, and they may be executed in other orders. Furthermore, at least some of the steps in the flowcharts of the drawings include multiple substeps or stages, which are not necessarily executed simultaneously but may be executed at different times. The order of execution is also not necessarily sequential, and they may be executed alternately or with other steps or at least some of the substeps or stages of other steps.

[0159] The above are only some embodiments of the present application, and those skilled in the art can make further improvements and refinements without departing from the principles of the present application, and these improvements and refinements should also be considered as part of the protection scope of the present application. [Explanation of symbols]

[0160] 10 n electrodes 25 Electrical Signal Generator 20 First electrical signal generating circuit 30 Second electrical signal generating circuit 40 Control Signal Generator 50 First switch part 501 First switch unit 60 Second switch part 601 Second switch unit 70 Multiplex Analog Switch Unit 80 Target Biological Tissue Regions 81 Target Biological Tissues 82 Normal biological tissue 91 First layer 92 Second layer 201 First electrode array 202 Second electrode array 203 Third Electrode Array

Claims

1. An electric field generator comprising: n electrodes arranged in a designed manner around a target biological tissue region; an electrical signal generator electrically connected to the n electrodes; a control signal generator electrically connected to the electrical signal generator, the control signal generator being used to control the electrical signal generator to output a first electrical signal to m electrodes among the n electrodes and to control the electrical signal generator to output a second electrical signal to at least two electrodes among the n-m electrodes, thereby generating an electric field between the electrode having the first electrical signal and the electrode having the second electrical signal; an electric field generating device, wherein n is an integer greater than or equal to 3, the voltage of the second electric signal is lower than the voltage of the first electric signal, the first electric signal is a high-voltage signal, and the second electric signal is a low-voltage signal, and 1≦m<n, m is an integer.

2. The electrical signal generator a first electrical signal generating circuit electrically connected to the n electrodes for outputting the first electrical signal; a second electrical signal generating circuit electrically connected to the n electrodes for outputting the second electrical signal.

3. The electric field generator is further comprising a first switch component and a second switch component; the first electrical signal generating circuit is electrically connected to the n electrodes via the first switch element, and the control signal generator is electrically connected to the first switch element; the second electrical signal generating circuit is electrically connected to the n electrodes via the second switch element, and the control signal generator is electrically connected to the second switch element; 3. The electric field generating device of claim 2, wherein the control signal generator is adapted to control the first switch component to transmit the first electrical signal to m electrodes of the n electrodes and to control the second switch component to transmit the second electrical signal to at least two electrodes of the nm electrodes, thereby generating an electric field between an electrode having the first electrical signal and an electrode having the second electrical signal.

4. the first switch component includes n first switch units, and the second switch component includes n second switch units; the n first switch units are electrically connected to the n electrodes in a one-to-one relationship, and are electrically connected to both the first electrical signal generating circuit and the control signal generator; 4. The electric field generating device of claim 3, wherein the n second switch units are electrically connected to the n electrodes in a one-to-one relationship and are electrically connected to both the second electric signal generating circuit and the control signal generator.

5. The electric field generator is the first electrical signal comprises an AC voltage signal, a pulse voltage signal, or a square wave voltage signal; the second electrical signal comprises a constant voltage signal or a varying voltage signal; the absolute value of the voltage width of the first electrical signal is 0 volts or more and 500 volts or less; the absolute value of the voltage width of the second electrical signal is 0 volts or more and 10 volts or less; The strength of the electric field is greater than or equal to 0.1 volts / centimeter and less than or equal to 10 volts / centimeter; and the frequency of the electric field is between 50 kilohertz and 500 kilohertz, 2. The electric field generator of claim 1, wherein m is 1.

6. 6. The electric field generator of claim 5, wherein the absolute value of the voltage amplitude of the second electric signal is 0 volts, 1 volt, or 5 volts.

7. A method for controlling an electric field generator, which is applied to the electric field generator according to any one of claims 1 to 6 and is controlled by a control signal generator, comprising: the control signal generator controls the electrical signal generator to output a first electrical signal to m electrodes among the n electrodes, and controls the electrical signal generator to output a second electrical signal to at least two electrodes among the n-m electrodes; n is an integer of 3 or more, 1≦m<n, m is an integer, The method for controlling an electric field generating device, wherein the electric field generating device includes the electric signal generator and the n electrodes electrically connected to each other, the voltage of the second electric signal is lower than the voltage of the first electric signal, the first electric signal is a high-voltage signal, and the second electric signal is a low-voltage signal.

8. A method for controlling an electric field generating device as described in claim 7, wherein the electric signal generator includes a first electric signal generating circuit and a second electric signal generating circuit, the electric field generating device further includes a first switch component and a second switch component, the first switch component is electrically connected to the first electric signal generating circuit, the control signal generator, and all of the n electrodes, and the second switch component is electrically connected to the second electric signal generating circuit, the control signal generator, and all of the n electrodes, Controlling the electrical signal generator to output a first electrical signal to m electrodes among the n electrodes, and controlling the electrical signal generator to output a second electrical signal to at least two electrodes among the n-m electrodes, controlling the first switch component to transmit the first electrical signal to m electrodes of the n electrodes, and controlling the second switch component to transmit the second electrical signal to at least two electrodes of the n-m electrodes. A method for controlling the electric field generator according to claim 7.

9. controlling the first switch component to transmit the first electrical signal to m electrodes of the n electrodes and controlling the second switch component to transmit the second electrical signal to at least two electrodes of the n-m electrodes includes: controlling a first switch unit numbered 1 to transmit the first electrical signal to the electrode numbered 1 of the n electrodes, controlling all of the first switch units numbered 2 to n to turn them off, and simultaneously turning off the second switch unit numbered 1 electrically connected to the electrode numbered 1, and controlling at least two second switch units numbered 2 to n to transmit the second electrical signal to at least two of the n electrodes excluding the electrode numbered 1; 9. The method for controlling an electric field generating device according to claim 8, wherein the first switch component includes n first switch units, the second switch component includes n second switch units, the n first switch units include first switch unit numbered 1 to first switch unit numbered n, the n second switch units include second switch unit numbered 1 to second switch unit numbered n, and the n electrodes include electrode numbered 1 to electrode numbered n.

10. controlling the first switch component to transmit the first electrical signal to m electrodes of the n electrodes and controlling the second switch component to transmit the second electrical signal to at least two electrodes of the n-m electrodes 9. The method for controlling an electric field generator according to claim 8, comprising controlling a first switch unit numbered 1 to transmit the first electrical signal to the electrode numbered 1 of the n electrodes, controlling all of the first switch units numbered 2 to n to turn them off, and simultaneously controlling the second switch unit numbered 1 electrically connected to the electrode numbered 1 to turn it off, and sequentially turning on at least two second switch units numbered 2 to n according to a designed sequence, so as to sequentially transmit the second electrical signal to at least two of the n electrodes excluding the electrode numbered 1 according to the designed sequence.

11. controlling the first switch component to transmit the first electrical signal to m electrodes of the n electrodes and controlling the second switch component to transmit the second electrical signal to at least two electrodes of the n-m electrodes when m is 1, controlling n first switch units to be sequentially turned on in accordance with a design sequence, so that n electrodes receive a first electrical signal in accordance with the design sequence, controlling n second switch units to be sequentially turned off in accordance with the design sequence, and further controlling each combination of second switch units to be sequentially turned on in accordance with the design sequence, so that a combination of electrodes corresponding to each combination of second switch units receives the second electrical signal in accordance with the design sequence; the combination of second switch units includes at least two second switch units among the n-1 second switch units that are not turned off, and the combination of electrodes includes at least two electrodes that are not receiving the first electrical signal; 9. The method for controlling an electric field generating device according to claim 8, wherein the first switch component includes n first switch units, and the second switch component includes n second switch units.

12. 11. The method for controlling an electric field generating device according to claim 10, wherein the time interval during which each second switch unit is sequentially turned on or off according to a designed sequence is not less than 20 milliseconds and not more than 500 milliseconds.

13. 8. The method for controlling an electric field generator according to claim 7, wherein the electric signal generator is controlled so that a first electric signal output to m electrodes out of the n electrodes is a high-voltage signal, and a second electric signal output to at least two electrodes out of the n-m electrodes is a low-voltage signal.

14. A computer-readable storage medium on which a computer program is stored, When the computer program is executed by a processor, the method for controlling an electric field generating device according to claim 7 is realized. A computer-readable storage medium.

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