Medical magnetic thermal ablation equipment and application method thereof for controlling microspheres to ablate tumors

Abstract

The invention discloses medical magnetic thermal ablation equipment and an application method for controlling microspheres to ablate tumors. The medical magnetic thermal ablation equipment is characterized in that an electromagnetic mechanism is arranged in a machine main body, and a cavity capable of allowing an object to pass through is formed in the machine main body; an inner cavity formed by the electromagnetic mechanism comprises the cavity, and a cooling device is arranged in the machine body at the same time to cool the electromagnetic mechanism. According to the medical magnetic thermal ablation equipment and the application method for controlling the microspheres to ablate tumors, by controlling injection of the microspheres and adjustment of the magnetic field, the tumors can be accurately treated, the surgical risk and recovery time are reduced in a non-invasive or minimally invasive mode, the magnetic field intensity and frequency are adjusted to adapt to different tumor characteristics, and the tumor ablation efficiency is improved. Meanwhile, the microsphere distribution and the heat effect are monitored in real time, the treatment accuracy is ensured, through the technology, the safety and comfort of a patient are improved, the treatment period is shortened, the medical efficiency is improved, more cases can be processed within a short time, and the use efficiency of medical resources is improved.

Description

Technical Field

[0001] The present invention relates to the technical field of medical magnetothermal ablation, and in particular to a medical magnetothermal ablation device and an application method thereof for controlling microspheres to ablate tumors. Background Art

[0002] Magnetothermal ablation is a treatment method that uses the heat generated by magnetic materials under the action of an external magnetic field to destroy or ablate abnormal tissue. This technology has broad application prospects in the medical field, especially in the treatment of cancer and other diseases.

[0003] Magnetic thermal ablation shows great potential in cancer treatment. By injecting magnetic nanoparticles or microspheres into tumor-bearing tissue and then applying a magnetic field externally, it can cause a local temperature rise in the tumor area, induce cancer cell death, and even achieve the purpose of ablating the tumor. This treatment method is expected to become an innovative means of tumor treatment, but most of this treatment method is ablation needle.

[0004] Although magnetothermal ablation has broad application prospects, there is still no corresponding medical magnetothermal ablation equipment on the market. Currently, magnetothermal equipment is mostly used for electromagnetic welding of industrial components. Summary of the invention

[0005] In view of the above-mentioned problems existing in the existing medical magnetic thermal ablation equipment, the present invention is proposed.

[0006] Therefore, the purpose of the present invention is to provide a medical magnetothermal ablation device, the purpose of which is to be able to use the device to directly heat the target to achieve magnetothermal ablation.

[0007] In order to solve the above technical problems, the present invention provides the following technical solution: an electromagnetic mechanism is arranged in a machine body, and a cavity capable of accommodating the passage of an object is arranged in the machine body; the inner cavity formed by the electromagnetic mechanism includes the cavity, and a cooling device is also arranged in the machine body to cool the electromagnetic mechanism.

[0008] As a preferred solution of the medical magnetic thermal ablation device described in the present invention, the machine body is a medical imaging machine, including a computer tomography device and a magnetic resonance imaging device.

[0009] As a preferred embodiment of the medical magnetic thermal ablation device described in the present invention, the machine body also includes a fan installed in the machine body; the machine body includes an annular cavity opened in the machine body, inner grooves evenly distributed in the annular cavity, an installation groove connected to the annular cavity through the inner groove, and a ventilation groove opened at one end of the annular cavity and connected to the fan.

[0010] As a preferred embodiment of the medical magnetic thermal ablation device described in the present invention, the electromagnetic mechanism includes an electromagnetic high-frequency heater arranged inside the circular cavity in the machine body, and an electromagnetic coil arranged at the output end of the electromagnetic high-frequency heater and located in the mounting groove.

[0011] In view of the above problems existing in the existing application methods of controlling microsphere ablation of tumors, the present invention is proposed.

[0012] Therefore, the purpose of the present invention is to provide an application method for controlling microsphere ablation of tumors, the purpose of which is to be able to adjust the magnetic thermal ablation parameters for individualized treatment according to the specific conditions of the patient.

[0013] To solve the above technical problems, the present invention provides the following technical solution: including injecting magnetic material or microspheres into the patient's affected area, moving the patient into the cavity using a moving bed, and heating the microspheres by activating an electromagnetic mechanism so that the microspheres thermally ablate the affected area.

[0014] As a preferred embodiment of the application method of the present invention for controlling microsphere ablation of tumors, the method of injecting microspheres into the patient's diseased area is interventional embolization, specifically:

[0015] Under the guidance of digital subtraction angiography, the femoral artery was percutaneously punctured and the microcatheter was super-selectively inserted into the tumor-feeding artery.

[0016] The magnetic material, namely the magnetothermal microspheres, is embolized into the tumor tissue. After the embolization is complete, the catheter guide wire is withdrawn and the puncture point is bandaged and fixed.

[0017] As a preferred embodiment of the application method of controlling microsphere ablation of tumors described in the present invention, the interventional embolization process is performed by selecting epidural anesthesia or general anesthesia, turning on an electrocardiogram monitor to detect blood pressure and heart rate during the ablation process, and opening an intravenous catheter for fluid infusion.

[0018] As a preferred embodiment of the application method of the present invention for controlling microsphere ablation of tumors, the microsphere positioning method after interventional embolization is specifically as follows:

[0019] The surface location of the tumor is scanned and located by B-ultrasound or computer tomography. After the affected artery is embolized, the patient lies on a mobile bed and is moved to the medical magnetic thermal ablation device.

[0020] Adjust the position according to the body surface positioning so that the tumor is within the range of the magnetic thermal ablation coil;

[0021] Adjust the alternating magnetic field strength button on the control panel and set the magnetic thermal ablation power, time, and magnetic thermal ablation insulation time according to the size of the tumor.

[0022] As a preferred embodiment of the application method of the present invention for controlling microsphere ablation of tumors, wherein: during the ablation process or after the ablation is completed, a B-ultrasound or computer tomography device is used to scan and observe the ablation range;

[0023] When the ablation range completely covers the tumor lesion, the ablation is terminated;

[0024] If the ablation range does not completely cover the tumor lesion, the ablation power can be increased or the ablation time can be extended to continue ablation;

[0025] Until the ablation range completely covers the tumor lesion.

[0026] As a preferred embodiment of the application method of the present invention for controlling microsphere ablation of tumors, the diameter of the magnetothermal microspheres is between 48 and 52 um.

[0027] The beneficial effects of the present invention are as follows: by controlling the injection of microspheres and the adjustment of the magnetic field, tumors can be accurately treated, and surgical risks and recovery time can be reduced through non-invasive or minimally invasive methods, and personalized treatment can be allowed. By adjusting the magnetic field strength and frequency to adapt to different tumor characteristics, the distribution of microspheres and thermal effects can be monitored in real time to ensure the accuracy of treatment. In addition, this technology improves the safety and comfort of patients, shortens the treatment cycle, and improves medical efficiency, so that more cases can be treated in a shorter time, effectively improving the efficiency of the use of medical resources. BRIEF DESCRIPTION OF THE DRAWINGS

[0028] In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the following briefly introduces the drawings required for describing the embodiments. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work. Among them:

[0029] Figure 1 It is a schematic diagram of the overall structure of the medical magnetic thermal ablation device of the present invention and its application method of controlling microspheres to ablate tumors.

[0030] Figure 2 It is a schematic diagram of the overall front section structure of the medical magnetic thermal ablation device of the present invention and the application method of controlling microspheres to ablate tumors.

[0031] Figure 3 It is a schematic diagram of the partial cross-sectional structure of the medical magnetothermal ablation device of the present invention and the application method of controlling microspheres to ablate tumors.

[0032] Figure 4 Schematic diagram of the heating temperature of PAM@Fe3O4 MSs with 30% Fe3O4 content within 5 minutes in the medical magnetothermal ablation device and the application method of the present invention for controlling microsphere ablation of tumors.

[0033] Figure 5 Schematic diagram of heating temperature curves of PAM@Fe3O4 MSs with 10%, 20%, and 30% Fe3O4 content within 5 minutes in the medical magnetothermal ablation device and its application method for controlling microsphere ablation of tumors of the present invention.

[0034] Figure 6 Schematic diagram of the repeatable heating curve of PAM@Fe3O4 with 30% Fe3O4 content in five AMF switching cycles of the medical magnetothermal ablation device and the application method thereof for controlling microsphere ablation of tumors of the present invention.

[0035] Figure 7 Schematic diagram of MTA treatment of rabbit liver tumors in a rabbit liver cancer model using magnetic thermal ablation to treat rabbit liver cancer using the medical magnetic thermal ablation device of the present invention and its application method for controlling microsphere ablation of tumors.

[0036] Figure 8 The medical magnetic thermal ablation device of the present invention and its application method for controlling microsphere ablation of tumors are used to embolize PAM@Fe3O4 MSs to VX2 liver tumors under DSA guidance. The green dotted line is a schematic diagram of the real-time development of PAM@Fe3O4 MSs in liver tumors.

[0037] Fig. 9 The medical magnetic thermal ablation device and the application method of the present invention for controlling microsphere ablation of tumors before and after different treatments 18 Schematic diagram of F-FDG PET image.

[0038] Fig.10 The figure is a schematic diagram of immunohistochemical images of the medical magnetic thermal ablation device and the application method thereof for controlling microsphere ablation of tumors according to the present invention. Fig.10 E is a schematic diagram of H&E staining and CD3 immunohistochemistry images of tumors in each group. Fig.10 F is a schematic diagram of the immunohistochemical image of T lymphocyte infiltration.

[0039] Fig.11 This is a data schematic diagram of the medical magnetic thermal ablation device of the present invention and its application method for controlling microspheres to ablate tumors. Fig.11 D is a schematic diagram of the changes in the standard uptake value (SUV) of the tumor in the treatment group. Fig.11 G is the changes of alanine aminotransferase and aspartate aminotransferase after treatment in group G. Fig.11 H is the changes of alanine aminotransferase and aspartate aminotransferase in group H after treatment. DETAILED DESCRIPTION

[0040] In order to make the above-mentioned objects, features and advantages of the present invention more obvious and easy to understand, the specific implementation methods of the present invention are described in detail below in conjunction with the accompanying drawings.

[0041] In the following description, many specific details are set forth to facilitate a full understanding of the present invention, but the present invention may also be implemented in other ways different from those described herein, and those skilled in the art may make similar generalizations without violating the connotation of the present invention. Therefore, the present invention is not limited to the specific embodiments disclosed below.

[0042] Secondly, the term "one embodiment" or "embodiment" as used herein refers to a specific feature, structure, or characteristic that may be included in at least one implementation of the present invention. The term "in one embodiment" that appears in different places in this specification does not necessarily refer to the same embodiment, nor does it refer to a separate or selective embodiment that is mutually exclusive with other embodiments.

[0043] Secondly, the present invention is described in detail with reference to the schematic diagram. When describing the embodiments of the present invention in detail, for the sake of convenience, the cross-sectional diagrams showing the device structure will not be partially enlarged according to the general scale, and the schematic diagrams are only examples, which should not limit the scope of protection of the present invention. In addition, in actual production, the three-dimensional dimensions of length, width and depth should be included.

[0044] Example 1

[0045] Reference Figure 1 , which is the first embodiment of the present invention, provides a magnetic microsphere 200 for use with a medical magnetothermal ablation device, specifically, polyacrylamide-ferroferric oxide magnetothermal microspheres (PAM@Fe3O4 MSs) with different ferroferric oxide contents are prepared by SPG membrane emulsification method.

[0046] The specific preparation method of the magnetic microsphere 200 is as follows:

[0047] S1, pre-prepared solid nano-iron tetroxide powder (powdered dry product), weighing 20g;

[0048] S2, mix the solid nano-iron tetroxide powder with 10 ml SDS aqueous solution (0.5%), and ultrasonicate for 10 minutes. The ultrasonic oscillation of a YM-040PLUS ultrasonic cleaning machine can be used to assist the dissolution;

[0049] S3, add PEG 400 2g, and continue ultrasonication for 15 minutes;

[0050] S4. After the ultrasonic treatment, the mixture was filtered through a 50 μm mesh to obtain the target product (solution A). The filtrate would settle rapidly if placed normally. When used, it should be shaken evenly and the corresponding volume should be taken out.

[0051] S5, weigh 10 g of target block polymer (polyacrylamide) powder, perform ultrasound, and disperse it in a pre-prepared SDS aqueous solution (90 degrees) in the laboratory by stirring with a vortex oscillator;

[0052] S6, adding and mixing A magnetic fluid solution (target solid content), and configuring 10%, 20%, and 30% ferrosoferric oxide content;

[0053] S7, after adding them respectively, ultrasonically apply them for 5 minutes to obtain solutions B1 (containing 10% ferrosoferric oxide), B2 (containing 20% ​​ferrosoferric oxide), and B3 (containing 30% ferrosoferric oxide);

[0054] S8, solutions B1, B2, and B3 were added to the SPG membrane emulsification device (emulsification pore size 20 microns) through water bath temperature control (solution B123 was placed in a glass container, the glass container was placed in a water bath, the water temperature was set to 45°C, and the solution B123 was controlled at a temperature of 45°C), pressurized to 0.5 mBar, and repeatedly passed through the membrane three times to obtain dispersions C1, C2, and C3 respectively;

[0055] S9, dispersions C1, C2, and C3 were rapidly cooled in an ice-water bath, filtered, washed three times with ethanol, redispersed in water, magnetically separated, and dried to obtain the target product PAM@Fe3O4 microspheres (containing 10%, 20%, and 30% Fe3O4, respectively).

[0056] Among them, step S8 is to connect the high-pressure nitrogen cylinder to the SPG device, turn on the nitrogen pressurization switch of the SPG membrane emulsifier, set the pressure to 20 bar, and use the nitrogen pressurization method to make the solution pass through the membrane pore size. The membrane used for repeated membrane passing is a hydrophilic SPG membrane with a pore size of 20 μm;

[0057] Furthermore, the rapid cooling in the water bath in step S9 is to place the dispersion into a glass container, and directly place the glass container in an ice-water mixture to cool it to 0°C; the filtering method is to filter with a 0.22 μm needle filter for later use; after separation by magnet, the dispersion is placed in a German Christ freeze dryer and freeze-dried at -10°C for 24 hours.

[0058] Example 2

[0059] Reference Figures 1 to 3 , which is the second embodiment of the present invention. This embodiment is different from the first embodiment in that: a medical magnetic thermal ablation device includes an electromagnetic mechanism 106 arranged in a machine body 101, and a cavity 102 capable of accommodating an object to pass through is arranged in the machine body 101; the inner cavity formed by the electromagnetic mechanism 106 includes the cavity 102, and a cooling device is also arranged in the machine body 101 to cool the electromagnetic mechanism 106.

[0060] Compared with Example 1, further, the machine body 101 can be a medical imaging machine, including a computer tomography device and a magnetic resonance imaging device, that is, the electromagnetic mechanism 106 can be arranged in a medical imaging machine-type device to facilitate observation. In this embodiment, the machine body 101 is a medical imaging machine, and the medical imaging machines are all existing technologies. Their internal structures are existing technologies and are not shown in the figure. The machine body 101 can also not adopt a medical imaging machine, but only needs a shell body with a detailed electromagnetic mechanism 106 arranged inside.

[0061] The electromagnetic mechanism 106 includes an electromagnetic high-frequency heater 106a disposed inside the circular cavity 101a in the machine body 101, and an electromagnetic coil 106b disposed at the output end of the electromagnetic high-frequency heater 106a and located in the mounting groove 101d.

[0062] The machine body 101 also includes a fan 105 installed in the machine body 101; the machine body 101 includes an annular cavity 101a opened in the machine body 101, inner grooves 101b evenly distributed in the annular cavity 101a, an installation groove 101d connected to the annular cavity 101a through the inner groove 101b, and a ventilation groove 101c opened at one end of the annular cavity 101a and connected to the fan 105.

[0063] During use, the electromagnetic high-frequency heater 106a is started by the control panel 104 and observed through the display screen 103. In this process, the fan 105 is started, and the fan 105 ventilates toward the annular cavity 101a through the ventilation groove 101c to directly dissipate the heat of the electromagnetic high-frequency heater 106a, while dissipating the heat of the electromagnetic coil 106b in the installation groove 101d through the inner groove 101b.

[0064] Alternatively, a water cooling device can be added for water cooling, and the control panel 104 and the display screen 103 are conventional technical means of the same products as CT or MRI, and the working principle is not described in detail here.

[0065] The remaining structures are the same as those of Example 1.

[0066] Example 3

[0067] Reference Figures 1 to 11 , which is the third embodiment of the present invention. This embodiment is different from the second embodiment in that: a method for controlling the application of microsphere ablation of tumors, injecting magnetic material or microspheres 200 into the patient's affected area, moving the patient into the cavity 102 using a moving bed, and heating the microspheres 200 by starting the electromagnetic mechanism 106, so that the microspheres 200 thermally ablate the affected area.

[0068] Compared with Example 2, further, magnetothermal ablation uses an alternating magnetic field to generate eddy current heat in the magnetic material in the tumor tissue, causing the tissue protein to coagulate and denature, thereby achieving the purpose of treatment. The general steps are interventional embolization, monitoring, positioning, and magnetothermal ablation surgery.

[0069] 1. Interventional embolization: Under the guidance of DSA, the femoral artery is percutaneously punctured, and the microcatheter is super-selectively inserted into the liver tumor supplying artery. Magnetic materials such as magnetothermal microspheres 200 are embolized into the liver tumor tissue. After the embolization is complete, the catheter guide wire is withdrawn and the puncture point is bandaged and fixed.

[0070] 2. Anesthesia and ECG monitoring: Choose epidural anesthesia or general anesthesia to relieve pain, turn on the ECG monitor to monitor blood pressure and heart rate during the ablation process, and open an intravenous catheter for fluid infusion.

[0071] 3. Positioning: Use B-ultrasound or CT scanning to locate the surface position of the tumor. After hepatic artery embolization, the patient lies on a mobile bed and is moved to the device. The position is adjusted according to the surface positioning so that the liver tumor is within the range of the magnetic thermal ablation coil. The alternating magnetic field strength button on the control panel is adjusted to set the magnetic thermal ablation power, time, and magnetic thermal ablation insulation time according to the size of the tumor.

[0072] 4. Magnetic thermal ablation: After turning on the water cooling device or the fan 105, click the start button to start magnetic thermal ablation, and continue to maintain it after reaching the rated temperature. Generally, the ablation power is set differently according to the size of the tumor. The specific parameters are shown in Table 1. During or after the ablation, the ablation range is observed by B-ultrasound or CT scanning. When the ablation range completely covers the tumor lesion, the ablation is terminated. If the ablation range does not completely cover the tumor lesion, the ablation power can be increased or the ablation time can be extended to continue ablation. Good ablation should be when the ablation range completely covers the tumor lesion.

[0073] Power supply KVA 50 70 90 110 130 150 Time min 5 5 5 5 5 5 Lesion size cm 2 3 5 6 8 10

[0074] Table 1 Lesion range parameters of different ablation powers at the same time

[0075] 5. Notes: Since the liver is located deep in the right upper costal arch of the human body and adjacent to the diaphragm, relevant examinations should be completed before undergoing liver magnetic thermal ablation to rule out serious cardiopulmonary diseases and underlying diseases such as hypertension and diabetes. In addition, blood pressure changes should be closely monitored for those with severe anemia and coagulation disorders. In addition, patients who have undergone liver magnetic thermal ablation should pay attention to rest and avoid excessive fatigue to avoid affecting physical recovery.

[0076] The remaining structure is the same as that of Example 2.

[0077] Example 4

[0078] Reference Figures 1 to 11 , which is the fourth embodiment of the present invention. This embodiment is different from the third embodiment in that: a study on the in vitro warming effect and stability of a magnetothermal ablation device.

[0079] Compared with Example 3, further, the diameter of human capillaries is 4-10um, while the diameter of embolic microspheres currently used in clinical practice is mostly 50um, which can effectively prevent the microspheres from entering the venous circulation through the capillaries and better embolize the terminal branches of the tumor supplying arteries.

[0080] refer to Figures 4 to 6 Therefore, firstly, the SPG membrane emulsification method was used to prepare polyacrylamide-iron tetroxide microspheres 200 (PAM@Fe3O4 MSs) with a diameter of about 50 μm. The main advantage of this SPG membrane emulsification method is that it can prepare monodisperse microdroplets with controllable size and different synthetic monomer ratios on a large scale. By selecting the pore size of the oleophilic membrane and setting the nitrogen pressurization pressure of the aqueous phase, magnetocaloric microspheres with uniform size distribution and regular morphology with different Fe3O4 ratios (10%, 20%, 30%) were prepared. Figure 5 When the Fe3O4 ratio is higher than 30%, it is difficult to form a ball or begins to deform, which is not conducive to the implementation of arterial embolization.

[0081] These magnetocaloric microspheres 200 with different Fe3O4 ratios were exposed to a magnetocaloric ablation device with parameters set at fappl = 500kHz, Happl = 5.0kA·m-1 to study their heating performance. It is worth noting that under a certain AMF intensity, the temperature change of the magnetocaloric microspheres obviously depends on their Fe3O4 ratio. This phenomenon originates from the formation of eddy currents inside the magnetocaloric microspheres. Following Faraday's law, the microspheres with a Fe3O4 ratio of 30% can reach a maximum temperature of 87 degrees Celsius when continued for 5 minutes. Figure 4 and Figure 5 , and can maintain a stable magnetothermal efficiency, refer to Figure 6 .

[0082] The remaining structure is the same as that of Example 3.

[0083] Example 5

[0084] Reference Figures 1 to 11 , which is the fifth embodiment of the present invention. This embodiment is different from the fourth embodiment in that the magnetic thermal ablation device performs magnetic thermal ablation of rabbit VXII in situ liver tumor.

[0085] Magnetic thermal ablation (MTA) is not limited by the penetration depth. It can achieve uniform distribution of magnetic thermal microspheres in tumor tissue through transarterial embolization technology, thus overcoming the limitations of image-guided percutaneous thermal ablation. To further verify the reliability of magnetic thermal ablation equipment, a comparative study between magnetic thermal ablation and microwave ablation (WMA) was conducted. Figure 7 .

[0086] refer to Figure 8 Transarterial embolization is the key to MTA. PAM@Fe3O4MSs can be accurately embolized into the rabbit VX2 tumor blood supply artery, thereby accumulating in the tumor. The microcatheter is inserted into the rabbit's right femoral artery through puncture. After DSA angiography shows the hepatic artery and tumor blood supply artery, the microcatheter enters the tumor blood supply artery and slowly perfuses PAM@Fe3O4 MSs until the artery is completely embolized.

[0087] refer to Fig. 9 , Fig.10 E and Fig.10 F, in order to intuitively evaluate the treatment effect, use 18 F-fluorodeoxyglucose (FDG) for PET imaging, 18 F-FDG PET imaging showed that the liver cancer tissues of the tumor-bearing rabbits in each group showed strong 18 F-FDG signal and high biological activity, after 7 days of treatment, the control group showed tumor growth. 18 The F-FDG signal was enlarged, while the active area in the group using only microsphere embolization was relatively reduced. The microwave ablation group showed better treatment effect. It is worth noting that the liver tumor of rabbits in the magnetic thermal ablation group showed only weak 18 F-FDG signal, indicating that magnetic thermal ablation has an excellent inhibitory effect on liver tumors. The green dashed line is PAM@Fe3O4 MSs, scale bar = 100μm.

[0088] refer to Fig.11 D. Fig.11 G and Fig.11 H, (n = 5), To further confirm the therapeutic effect of MTA and its effect on immunity, histopathological analysis of tumor tissue sections was performed, including H&E staining and immunohistochemistry. It is worth noting that compared with other groups, the tumor cell apoptosis in the MTA group (MSs+AMF) was the highest, further proving the therapeutic effect of MTA ( Fig.11 D) In ​​terms of safety, it showed no toxicity to organs.

[0089] The percentage of CD3+T cells in both the magnetic thermal ablation and microwave ablation treatment groups increased significantly, indicating that MTA, like MWA, can induce a strong immune response and further inhibit liver cancer lesions. At the same time, the safety of MTA was verified, and it was found that the liver function of the MSs group, WMA group, and MSs+AMF group was affected to a certain extent. Alanine aminotransferase and aspartate aminotransferase reached a peak on the fourth day after surgery, but returned to normal around the twelfth day after surgery ( Fig.11 G and Fig.11H), no intolerable complications or deaths occurred in the tumor-bearing rabbits in each group after surgery, which shows that MTA, like MWA, has good feasibility and safety.

[0090] Compared with Example 4, further, under the guidance of DSA, rabbit ear artery embolization and renal artery embolization were used to prove that PAM@Fe3O4 MSs can be effectively retained in blood vessels to achieve magnetic thermal therapy. An alternating magnetic field was applied under the magnetic thermal ablation device, and the efficient magnetic thermal heating effect of PAM@Fe3O4 microspheres 200 was utilized to achieve efficient magnetic thermal ablation treatment of the rabbit VX2 in situ liver tumor model. The construction of this device promotes the transformation of liver cancer treatment from "minimally invasive ablation" of percutaneous puncture under image guidance to "non-invasive ablation" under alternating magnetic fields, which is of great significance and potential clinical application value.

[0091] The remaining structures are the same as those of Example 4.

[0092] Importantly, it should be noted that the construction and arrangement of the present application shown in a plurality of different exemplary embodiments are only exemplary. Although only a few embodiments are described in detail in this disclosure, it should be readily understood by those who refer to this disclosure that many modifications are possible (e.g., the size, scale, structure, shape and proportion of various elements, and parameter values ​​(e.g., temperature, pressure, etc.), installation arrangement, use of materials, color, directional changes, etc.) without substantially departing from the novel teachings and advantages of the subject matter described in the application. For example, the element shown as integrally formed can be composed of multiple parts or elements, the position of the element can be inverted or otherwise changed, and the nature or number or position of the discrete element can be changed or changed. Therefore, all such modifications are intended to be included in the scope of the present invention. The order or sequence of any process or method steps can be changed or reordered according to alternative embodiments. In the claims, any "device plus function" clause is intended to cover the structure of performing the function described herein, and is not only structurally equivalent but also equivalent structure. Without departing from the scope of the present invention, other replacements, modifications, changes and omissions can be made in the design, operating conditions and arrangement of the exemplary embodiments. Therefore, the invention is not limited to a specific embodiment, but extends to numerous modifications still falling within the scope of the appended claims.

[0093] Additionally, in order to provide a concise description of exemplary embodiments, all features of an actual embodiment (ie, those features that are not relevant to the best mode presently contemplated for carrying out the invention or those that are not relevant to implementing the invention) may not be described.

[0094] It should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention rather than to limit it. Although the present invention has been described in detail with reference to the preferred embodiments, those skilled in the art should understand that the technical solutions of the present invention may be modified or replaced by equivalents without departing from the spirit and scope of the technical solutions of the present invention, which should all be included in the scope of the claims of the present invention.

Claims

1. A medical magnetic thermal ablation device, characterized in that: include, An electromagnetic mechanism (106) is arranged in the machine body (101), and a cavity (102) capable of accommodating the passage of an object is arranged in the machine body (101); The inner cavity formed by the electromagnetic mechanism (106) includes the cavity (102), and a cooling device is also provided in the machine body (101) to cool the electromagnetic mechanism (106).

2. The medical magnetic thermal ablation device according to claim 1, characterized in that: The machine body (101) is a medical imaging machine, including a computer tomography device and a magnetic resonance imaging device.

3. The medical magnetic thermal ablation device according to claim 1 or 2, characterized in that: The machine body (101) further includes a fan (105) installed in the machine body (101); The machine body (101) comprises an annular cavity (101a) provided in the machine body (101), inner grooves (101b) evenly distributed in the annular cavity (101a), a mounting groove (101d) connected to the annular cavity (101a) via the inner groove (101b), and a ventilation groove (101c) provided at one end of the annular cavity (101a) and connected to the fan (105).

4. The medical magnetic thermal ablation device according to claim 3, characterized in that: The electromagnetic mechanism (106) comprises an electromagnetic high-frequency heater (106a) arranged inside the annular cavity (101a) in the machine body (101), and an electromagnetic coil (106b) arranged at the output end of the electromagnetic high-frequency heater (106a) and located in the installation groove (101d).

5. An application method for controlling microsphere ablation of tumors, characterized in that: The medical magnetic thermal ablation device comprising any one of claims 1 to 4, further comprising: A magnetic material or microspheres (200) is injected into the patient's affected area, the patient is moved into the cavity (102) using a moving bed, and the microspheres (200) are heated by activating an electromagnetic mechanism (106), so that the microspheres (200) thermally ablate the affected area.

6. The application method of controlling microsphere ablation of tumors according to claim 5, characterized in that: The method of injecting the microspheres (200) into the patient's affected area is interventional embolization, specifically: Under the guidance of digital subtraction angiography, the femoral artery was percutaneously punctured and the microcatheter was super-selectively inserted into the tumor-feeding artery. The magnetic material, namely the magnetothermal microspheres (200), is embolized into the tumor tissue. After the embolization is complete, the catheter guide wire is withdrawn and the puncture point is bandaged and fixed.

7. The application method of controlling microsphere ablation of tumors according to claim 6, characterized in that: The interventional embolization process is performed by selecting epidural anesthesia or general anesthesia, turning on an electrocardiogram monitor to monitor blood pressure and heart rate during the ablation process, and opening a venous indwelling needle for fluid infusion.

8. The application method of controlling microsphere ablation of tumors according to claim 6 or 7, characterized in that: The positioning method of the microspheres (200) after the interventional embolization is specifically as follows: The surface location of the tumor is scanned and located by B-ultrasound or computer tomography. After the affected artery is embolized, the patient lies on a mobile bed and is moved to the medical magnetic thermal ablation device. Adjust the position according to the body surface positioning so that the tumor is within the range of the magnetic thermal ablation coil; Adjust the alternating magnetic field strength button on the control panel and set the magnetic thermal ablation power, time, and magnetic thermal ablation insulation time according to the size of the tumor.

9. The application method of controlling microsphere ablation of tumors according to claim 8, characterized in that: During the ablation process or after the ablation is completed, a B-ultrasound or computer tomography device is used to scan and observe the ablation range; When the ablation range completely covers the tumor lesion, the ablation is terminated; If the ablation range does not completely cover the tumor lesion, the ablation power can be increased or the ablation time can be extended to continue ablation; Until the ablation range completely covers the tumor lesion.

10. The application method of controlling microsphere ablation of tumors according to claim 9, characterized in that: The diameter of the magnetocaloric microsphere (200) is between 48 and 52 um.

Images