Magnetic resonance imaging and radio frequency heating integrated guide wire and use method thereof

Abstract

The invention provides a magnetic resonance imaging and radio frequency heating integrated guide wire and a use method thereof, and can be applied to the technical field of medical instruments. The magnetic resonance imaging and radio frequency heating integrated guide wire comprises a signal processing circuit, the signal processing circuit comprises a first filtering sub-circuit and a second filtering sub-circuit, and a first filtering range of the first filtering sub-circuit and a second filtering range of the second filtering sub-circuit are different from each other, the first end of the first filtering sub-circuit is used for being connected with a magnetic resonance imaging system, the first end of the second filtering sub-circuit is used for being connected with a radio frequency generator, and the radio frequency generator is used for providing radio frequency heating signals for the second filtering sub-circuit; the first end of the guide wire main body is connected to the second end of the first filtering sub-circuit and the second end of the second filtering sub-circuit, and the second end of the guide wire main body is used for collecting a magnetic resonance imaging signal of an organ tissue; wherein the radio frequency heating signal and the magnetic resonance imaging signal are synchronously transmitted in the guide wire main body.

Description

Technical Field

[0001] The present disclosure relates to the technical field of medical devices, and in particular, to a guide wire integrating magnetic resonance imaging and radio frequency heating and a method for using the guide wire. Background Art

[0002] As a minimally invasive interventional surgical instrument, the guidewire mainly plays a guiding and supporting role during the operation and has been widely used in the diagnosis and treatment of organ cavity diseases such as cardiovascular, esophageal, bile duct, and rectum.

[0003] In the relevant technology, the guide wires used clinically are all passive devices with single functions. They only play a physical role of guidance and support during the operation and do not have other therapeutic functions. Therefore, other instruments are needed for imaging diagnosis and treatment during the operation.

[0004] For example, in related technologies, cardiovascular diseases are mainly diagnosed through X-CT (X-Ray Computed Tomography) and DSA (Digital Subtraction Angiography). However, these imaging technologies can only see the narrow blood vessel lumen, but not the plaques on the blood vessel wall, which is not convenient for disease diagnosis; and these imaging technologies have serious ionizing radiation, which will harm the doctors and patients.

[0005] Treatments for cardiovascular diseases mainly include medication, interventional therapy, and surgical treatment. Researchers are also exploring the possibility of using gene therapy for cardiovascular diseases. As a result, gene therapy is expected to become a cutting-edge technology for the treatment of cardiovascular diseases. Studies have shown that local heating can enhance the expression of vascular genes. However, how to achieve precise local heating remains a challenge.

[0006] In addition, in the related art, imaging diagnosis of luminal diseases such as the esophagus is mainly performed through endoscopes. However, endoscopes can only image the surface tissues in the lumen, and it is difficult to detect lesions in the deep tissues, which has certain limitations in diagnosis. Moreover, the commonly used treatment for luminal tumors such as the esophagus is invasive surgery. However, surgical treatment is highly traumatic to patients, has slow recovery, is often accompanied by a variety of postoperative complications, and has a high postoperative recurrence rate. In the related art, minimally invasive interventional ablation has developed into a hot spot in tumor treatment. On this basis, how to better integrate ablation therapy into the treatment of luminal tumors such as the esophagus needs to be solved urgently. Summary of the invention

[0007] In view of this, the present disclosure provides a magnetic resonance imaging and radio frequency heating integrated guide wire and a method of using the same.

[0008] One aspect of the present disclosure provides an integrated guidewire for magnetic resonance imaging and radio frequency heating, comprising: a signal processing circuit, the signal processing circuit comprising a first filtering subcircuit and a second filtering subcircuit, the first filtering range of the first filtering subcircuit and the second filtering range of the second filtering subcircuit are different from each other, the first end of the first filtering subcircuit is used to connect to a magnetic resonance imaging system, the first end of the second filtering subcircuit is used to connect to a radio frequency generator, and the radio frequency generator is used to provide a radio frequency heating signal to the second filtering subcircuit; and a guidewire body, the first end of the guidewire body is connected to the second end of the first filtering subcircuit and the second end of the second filtering subcircuit, and the second end of the guidewire body is used to collect magnetic resonance imaging signals of organ tissues; wherein the radio frequency heating signal and the magnetic resonance imaging signal are synchronously transmitted in the guidewire body; the frequency range of the magnetic resonance imaging signal corresponds to the first filtering range; and the frequency range of the radio frequency heating signal corresponds to the second filtering range.

[0009] According to an embodiment of the present disclosure, the first filtering range has a first degree of difference relative to the second filtering range; the center frequency of the magnetic resonance imaging system has a second degree of difference relative to the signal transmission frequency of the radio frequency generator; the first degree of difference corresponds to the second degree of difference.

[0010] According to an embodiment of the present disclosure, when the first filtering range is higher than the second filtering range, the center frequency of the magnetic resonance imaging system is higher than the signal transmission frequency of the radio frequency generator; and when the first filtering range is lower than the second filtering range, the center frequency of the magnetic resonance imaging system is lower than the signal transmission frequency of the radio frequency generator.

[0011] According to an embodiment of the present disclosure, the signal processing circuit further includes a tuning matching decoupling subcircuit; the first end of the first filtering subcircuit is connected to the first end of the tuning matching decoupling subcircuit, and the second end of the tuning matching decoupling subcircuit is used to connect to the magnetic resonance imaging system.

[0012] According to an embodiment of the present disclosure, the second end of the tuning, matching and decoupling subcircuit is connected to the signal transmission line of the magnetic resonance imaging system through a first non-magnetic SMA connector; the first end of the second filtering subcircuit is connected to the signal transmission line of the radio frequency generator through a second non-magnetic SMA connector.

[0013] According to an embodiment of the present disclosure, the frequency range of the RF heating signal is 300 KHz to 2.45 GHz; and

[0014] The magnetic field strength of the MRI system ranges from 0 to 7.0 T.

[0015] According to an embodiment of the present disclosure, the guide wire body includes a coaxially arranged metal wire, an insulating layer wrapping the metal wire, and a metal layer wrapping the insulating layer; the metal wire protrudes axially from the insulating layer and the metal layer, and the length of the metal wire protruding from the insulating layer and the metal layer is adjustable.

[0016] According to an embodiment of the present disclosure, the length of the metal wire protruding from the insulating layer and the metal layer is adjusted based on the magnetic resonance imaging range and the heating range, wherein the magnetic resonance imaging range represents the imaging requirement range for magnetic resonance imaging of organ tissue, and the heating range represents the requirement range for heating the organ tissue.

[0017] According to an embodiment of the present disclosure, the materials of the metal wire and the metal layer are non-magnetic metal materials; the material of the insulating layer is non-magnetic insulating material; and the material of the signal processing circuit includes at least one of non-magnetic material and weak magnetic material.

[0018] Another aspect of the present disclosure provides a method for using an integrated magnetic resonance imaging and radio frequency heating guide wire, comprising: extending the second end of the guide wire body to a target area, collecting magnetic resonance imaging signals of organ tissues located in the target area, and simultaneously heating the organ tissues located in the target area.

[0019] According to an embodiment of the present disclosure, by electrically connecting the guide wire body to the first filtering subcircuit and the second filtering subcircuit, the magnetic resonance imaging signal collected by the guide wire body can be transmitted to the magnetic resonance imaging system via the first filtering subcircuit, and the radio frequency heating signal from the radio frequency generator can be transmitted to the guide wire body via the second filtering subcircuit. Thus, the magnetic resonance imaging signal and the radio frequency heating signal are filtered respectively by the two subcircuits, thereby achieving isolation between the magnetic resonance imaging signal and the radio frequency heating signal. Based on this, the reception of the magnetic resonance imaging signal and the transmission of the radio frequency heating signal can be achieved simultaneously through the guide wire body, thereby achieving synchronization of imaging and radio frequency heating of organ tissues.

[0020] Based on this, the integrated guidewire provided by the present disclosure not only has the functions of guiding and supporting the guidewire, but also has the functions of magnetic resonance imaging and radiofrequency heating treatment. It is fully functional, greatly simplifies the surgical operation process of luminal diseases, reduces the burden on doctors and the pain of patients, and reduces the consumption of medical resources. In addition, since the integrated guidewire provided by the present disclosure can perform real-time magnetic resonance imaging while performing radiofrequency heating, it is convenient for doctors to monitor the treatment process in real time, improve surgical efficiency, and avoid overtreatment or undertreatment.

[0021] Moreover, compared with imaging methods such as X-CT, DSA and endoscope, the magnetic resonance imaging method supported by the integrated guidewire provided by the present disclosure has high image resolution, high soft tissue contrast, and can be multi-directionally imaged, which is convenient for doctors to diagnose and treat. Moreover, the integrated guidewire provided by the present disclosure has no ionizing radiation and does not cause radiation damage to doctors and patients. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] The above and other objects, features and advantages of the present disclosure will become more apparent through the following description of the embodiments of the present disclosure with reference to the accompanying drawings, in which:

[0023] Figure 1 A schematic diagram of a guidewire integrating magnetic resonance imaging and radio frequency heating according to a first embodiment of the present disclosure is schematically shown.

[0024] Figure 2 The figure schematically shows a schematic diagram of a signal processing circuit according to an embodiment of the present disclosure.

[0025] Figure 3 A schematic diagram of a guidewire integrating magnetic resonance imaging and radio frequency heating according to a second embodiment of the present disclosure is schematically shown.

[0026] Figure 4 A schematic diagram of a guidewire body according to an embodiment of the present disclosure is schematically shown.

[0027] Figure 5 A detailed schematic diagram of a guidewire body according to an embodiment of the present disclosure is schematically shown.

[0028] Figure 6 The flowchart of the guidewire integrating magnetic resonance imaging and radio frequency heating according to an embodiment of the present disclosure is schematically shown. DETAILED DESCRIPTION

[0029] Hereinafter, embodiments of the present disclosure will be described with reference to the accompanying drawings. However, it should be understood that these descriptions are exemplary only and are not intended to limit the scope of the present disclosure. In the following detailed description, for ease of explanation, many specific details are set forth to provide a comprehensive understanding of the embodiments of the present disclosure. However, it is apparent that one or more embodiments may also be implemented without these specific details. In addition, in the following description, descriptions of known structures and technologies are omitted to avoid unnecessary confusion of the concepts of the present disclosure.

[0030] The terms used herein are only for describing specific embodiments and are not intended to limit the present disclosure. The terms "comprise", "include", etc. used herein indicate the existence of the features, steps, operations and / or components, but do not exclude the existence or addition of one or more other features, steps, operations or components.

[0031] All terms (including technical and scientific terms) used herein have the meanings commonly understood by those skilled in the art unless otherwise defined. It should be noted that the terms used herein should be interpreted as having a meaning consistent with the context of this specification and should not be interpreted in an idealized or overly rigid manner.

[0032] When using expressions such as "at least one of A, B, and C, etc.", they should generally be interpreted according to the meaning of the expression commonly understood by those skilled in the art (for example, "a system having at least one of A, B, and C" should include but is not limited to a system having A alone, B alone, C alone, A and B, A and C, B and C, and / or A, B, C, etc.).

[0033] The present disclosure provides an integrated guidewire for magnetic resonance imaging and radio frequency heating, which is used for minimally invasive interventional treatment of luminal diseases under magnetic resonance guidance. Based on the guidance and support functions of a passive guidewire, magnetic resonance imaging and radio frequency heating treatment can be performed on various lumens, and real-time imaging and monitoring of the treatment progress can be performed while radio frequency heating is performed.

[0034] Specifically, the embodiment of the present disclosure provides an integrated guidewire for magnetic resonance imaging and radio frequency heating, comprising: a signal processing circuit, the signal processing circuit comprising a first filtering subcircuit and a second filtering subcircuit, the first filtering range of the first filtering subcircuit and the second filtering range of the second filtering subcircuit are different from each other, the first end of the first filtering subcircuit is used to connect to the magnetic resonance imaging system, the first end of the second filtering subcircuit is used to connect to the radio frequency generator, and the radio frequency generator is used to provide a radio frequency heating signal to the second filtering subcircuit. And a guidewire body, the first end of the guidewire body is connected to the second end of the first filtering subcircuit and the second end of the second filtering subcircuit, and the second end of the guidewire body is used to collect magnetic resonance imaging signals of organ tissues. Wherein, the radio frequency heating signal and the magnetic resonance imaging signal are transmitted synchronously in the guidewire body. The frequency range of the magnetic resonance imaging signal corresponds to the first filtering range. The frequency range of the radio frequency heating signal corresponds to the second filtering range.

[0035] Figure 1 A schematic diagram of a guidewire integrating magnetic resonance imaging and radio frequency heating according to an embodiment of the present disclosure is schematically shown.

[0036] like Figure 1 As shown, the magnetic resonance imaging and radio frequency heating integrated guidewire of this embodiment includes: a signal processing circuit 110 and a guidewire body 120.

[0037] The signal processing circuit 110 includes a first filtering subcircuit 111_1 and a second filtering subcircuit 111_2. The first filtering range of the first filtering subcircuit 111_1 and the second filtering range of the second filtering subcircuit 111_2 are different from each other. The first end of the first filtering subcircuit 111_1 is used to connect to a magnetic resonance imaging (MRI) system 130, and the first end of the second filtering subcircuit 111_2 is used to connect to a radio frequency (RF) generator 140, and the RF generator 140 is used to provide a radio frequency heating signal to the second filtering subcircuit 111_2. The frequency range of the radio frequency heating signal corresponds to the second filtering range.

[0038] The first end of the guide wire body 120 is connected to the second end of the first filter subcircuit 111_1 and the second end of the second filter subcircuit 111_2, and the second end of the guide wire body 120 is used to collect magnetic resonance imaging signals of organ tissues. For example, organ tissues may include but are not limited to lumens. The guide wire body 120 can extend into the lumen to collect magnetic resonance imaging signals inside the lumen. The radio frequency heating signal and the magnetic resonance imaging signal are synchronously transmitted in the guide wire body 120.

[0039] In the embodiment of the present disclosure, the frequency range of the magnetic resonance imaging signal corresponds to the first filtering range. The frequency range of the radio frequency heating signal corresponds to the second filtering range. For example, the function of one of the first filtering subcircuit 111_1 and the second filtering subcircuit 111_2 may be high-pass filtering, and the function of the other filtering subcircuit may be low-pass filtering. It should be understood that the "high-pass filtering" and "low-pass filtering" herein are relative. For example, in the case where the function of the first filtering subcircuit 111_1 is high-pass filtering and the function of the second filtering subcircuit 111_2 is low-pass filtering, the frequency range of the magnetic resonance imaging signal may correspond to the range of the high-pass filtering, and the frequency range of the radio frequency heating signal may correspond to the range of the low-pass filtering. For another example, in the case where the function of the first filtering subcircuit 111_1 is low-pass filtering and the function of the second filtering subcircuit 111_2 is high-pass filtering, the frequency range of the magnetic resonance imaging signal may correspond to the range of the low-pass filtering, and the frequency range of the radio frequency heating signal may correspond to the range of the high-pass filtering.

[0040] Specifically, in the embodiment of the present disclosure, the first filter range has a first difference degree relative to the second filter range. The first difference degree can represent the difference between the first filter range and the second filter range. Specifically, the first difference degree can represent that the first filter range is higher than the second filter range, or the first filter range is lower than the second filter range.

[0041] The center frequency of the magnetic resonance imaging system 130 has a second difference degree relative to the signal transmission frequency of the radio frequency generator 140. The second difference degree can represent the difference between the signal transmission frequency of the radio frequency generator 140 and the signal transmission frequency of the radio frequency generator 140. Specifically, the second difference degree can be used to represent that the center frequency of the magnetic resonance imaging system 130 is higher than the signal transmission frequency of the radio frequency generator 140, or that the center frequency of the magnetic resonance imaging system 130 is lower than the signal transmission frequency of the radio frequency generator 140.

[0042] In the embodiment of the present disclosure, the first degree of difference corresponds to the second degree of difference. For example, when the first filtering range is higher than the second filtering range, the center frequency of the magnetic resonance imaging system 130 is higher than the signal transmission frequency of the radio frequency generator 140. When the first filtering range is lower than the second filtering range, the center frequency of the magnetic resonance imaging system 130 is lower than the signal transmission frequency of the radio frequency generator 140. For example, the frequency range of the radio frequency heating signal is 300 KHz~2.45 GHz; and the magnetic field strength range of the magnetic resonance imaging system 130 is 0~7.0 T. Based on this, different radio frequency frequencies can be selected according to the required heating effect, and the magnetic field strength can be selected according to the required imaging accuracy. On this basis, the integrated guide wire provided by the present disclosure can select different radio frequency frequencies according to the purpose of the required heating treatment, and has high flexibility. For example, the radio frequency frequency can be controlled to a frequency that can be used to enhance gene expression or a frequency that can be used to ablate tumors according to the treatment purpose. Specifically, if gene expression is enhanced, a lower frequency heating can be designed; if a tumor is ablated, a higher frequency heating can be designed.

[0043] In one embodiment of the present disclosure, the center frequency of the magnetic resonance imaging system 130 and the signal transmission frequency of the radio frequency generator 140 may be adjusted according to the first difference degree, so that the center frequency of the magnetic resonance imaging system 130 has a second difference degree corresponding to the first difference degree relative to the signal transmission frequency of the radio frequency generator 140. In another embodiment of the present disclosure, the first filter subcircuit 111_1 and the second filter subcircuit 111_2 may be adjusted according to the second difference degree, so that the first filter range of the first filter subcircuit 111_1 has a first difference degree corresponding to the second difference degree relative to the second filter range of the second filter subcircuit 111_2.

[0044] According to an embodiment of the present disclosure, by electrically connecting the guide wire body 120 to the first filtering subcircuit 111_1 and the second filtering subcircuit 111_2, the magnetic resonance imaging signal collected by the guide wire body 120 can be transmitted to the magnetic resonance imaging system 130 via the first filtering subcircuit 111_1, and the radio frequency heating signal from the radio frequency generator 140 can be transmitted to the guide wire body 120 via the second filtering subcircuit 111_2. Thus, the magnetic resonance imaging signal and the radio frequency heating signal are filtered respectively by the two subcircuits, thereby achieving isolation between the magnetic resonance imaging signal and the radio frequency heating signal. Based on this, the guide wire body 120 can simultaneously realize the reception of the magnetic resonance imaging signal and the transmission of the radio frequency heating signal, thereby realizing the synchronization of imaging and radio frequency heating of organ tissues.

[0045] Based on this, the integrated guidewire provided by the present disclosure not only has the functions of guiding and supporting the guidewire, but also has the functions of magnetic resonance imaging and radiofrequency heating treatment. It is fully functional, greatly simplifies the surgical operation process of luminal diseases, reduces the burden on doctors and the pain of patients, and reduces the consumption of medical resources. In addition, since the integrated guidewire provided by the present disclosure can perform real-time magnetic resonance imaging while performing radiofrequency heating, it is convenient for doctors to monitor the treatment process in real time, improve surgical efficiency, and avoid overtreatment or undertreatment.

[0046] Moreover, compared with imaging methods such as X-CT, DSA and endoscope, the magnetic resonance imaging method supported by the integrated guidewire provided by the present disclosure has high image resolution, high soft tissue contrast, and can be multi-directionally imaged, which is convenient for doctors to diagnose and treat. Moreover, the integrated guidewire provided by the present disclosure has no ionizing radiation and does not cause radiation damage to doctors and patients.

[0047] Figure 2 The figure schematically shows a schematic diagram of a signal processing circuit according to an embodiment of the present disclosure.

[0048] Figure 3 A schematic diagram of a guidewire integrating magnetic resonance imaging and radio frequency heating according to a second embodiment of the present disclosure is schematically shown.

[0049] like Figure 2 and Figure 3 As shown, the signal processing circuit 110 further includes a tuning, matching and decoupling subcircuit 111_3 . A first end of the first filtering subcircuit 111_1 is connected to a first end of the tuning, matching and decoupling subcircuit 111_3 , and a second end of the tuning, matching and decoupling subcircuit 111_3 is used to connect to the magnetic resonance imaging system 130 .

[0050] In the embodiment of the present disclosure, since the magnetic resonance imaging signal is received by the second end of the guide wire body 120 and is synchronously transmitted with the radio frequency heating signal in the guide wire body 120, in order to ensure the imaging effect of the magnetic resonance imaging system 130, the magnetic resonance imaging signal needs to be input into the tuning matching decoupling subcircuit 111_3 that can achieve signal tuning, impedance matching and signal decoupling for processing, and then the processed magnetic resonance imaging signal is input into the magnetic resonance imaging system 130. Based on this, by connecting the tuning matching decoupling subcircuit 111_3 between the first filtering subcircuit 111_1 and the magnetic resonance imaging system 130, the quality of the magnetic resonance imaging signal transmitted to the magnetic resonance imaging system 130 is improved, thereby improving the imaging effect of magnetic resonance imaging of organ tissues.

[0051] According to an embodiment of the present disclosure, the second end of the tuning, matching and decoupling subcircuit 111_3 is connected to the signal transmission line of the magnetic resonance imaging system 130 through a first non-magnetic SMA (SubMiniature version A) connector 112_1. The first end of the second filtering subcircuit 111_2 is connected to the signal transmission line of the RF generator 140 through a second non-magnetic SMA connector 112_2.

[0052] In the disclosed embodiment, the signal processing circuit 110 may be encapsulated in a housing. Three non-magnetic SMA connectors may be provided on the outside of the housing. The three non-magnetic SMA connectors may be non-magnetic SMA male connectors. The first non-magnetic SMA connector 112_1 of the three non-magnetic SMA connectors may be connected to the magnetic resonance imaging system 130 through a signal transmission line; the second non-magnetic SMA connector 112_2 of the three non-magnetic SMA connectors is connected to the signal transmission line of the radio frequency generator 140; and the third non-magnetic SMA connector 112_3 of the three non-magnetic SMA connectors is connected to the guide wire body 120. For example, the third non-magnetic SMA connector 112_3 may be electrically connected to the second end of the first filtering subcircuit 111_1 and the second end of the second filtering subcircuit 111_2, and the first end of the guide wire body 120 may be provided with a fourth non-magnetic SMA connector 121_1, and the fourth non-magnetic SMA connector 121_1 may be a non-magnetic SMA female connector. Thus, the third non-magnetic SMA connector 112_3 and the fourth non-magnetic SMA connector 121_1 may be connected to each other, so that the first end of the guidewire body 120 is connected to the second end of the first filter subcircuit 111_1 and the second end of the second filter subcircuit 111_2.

[0053] Through this connection method, the signal processing circuit 110 encapsulated in the shell is composed of a two-way structure, one way transmits the magnetic resonance imaging signal received by the guide wire body 120 to the magnetic resonance imaging system 130 through the first filtering sub-circuit 111_1 and the tuning matching decoupling sub-circuit 111_3; the other way transmits the radio frequency heating signal generated by the radio frequency generator 140 to the guide wire body 120 through the second filtering sub-circuit 111_2.

[0054] According to an embodiment of the present disclosure, by using a non-magnetic SMA connector to connect the signal processing circuit 110 to the magnetic resonance imaging system 130, it is convenient to disassemble and separate the signal processing circuit 110 from the magnetic resonance imaging system 130, and the connection relationship between the signal processing circuit 110 and the magnetic resonance imaging system 130 can be flexibly adjusted. Similarly, by using a non-magnetic SMA connector to connect the signal processing circuit 110 to the radio frequency generator 140, it is convenient to disassemble and separate the signal processing circuit 110 from the radio frequency generator 140, and the connection relationship between the signal processing circuit 110 and the radio frequency generator 140 can be flexibly adjusted. Thus, the flexibility of adjusting the connection relationship between the signal processing circuit 110 and other systems is improved. In addition, by using a non-magnetic SMA connector to connect the guide wire body 120 and the signal processing circuit 110, it is convenient to disassemble and separate the guide wire body 120 and the signal processing circuit 110. Based on this, the present disclosure improves the convenience of replacing the guide wire body 120 and the signal processing circuit 110 by using a non-magnetic SMA connector, and the signal processing circuit 110 can be reused.

[0055] Figure 4 A schematic diagram of a guidewire body according to an embodiment of the present disclosure is schematically shown.

[0056] Figure 5 A detailed schematic diagram of a guidewire body according to an embodiment of the present disclosure is schematically shown.

[0057] like Figure 4 and Figure 5 As shown, the guide wire body 120 includes a coaxially arranged metal wire 120_1, an insulating layer 120_2 wrapping the metal wire 120_1, and a metal layer 120_3 wrapping the insulating layer 120_2. The metal wire 120_1 protrudes from the insulating layer 120_2 and the metal layer 120_3 in the axial direction, and the length of the metal wire 120_1 protruding from the insulating layer 120_2 and the metal layer 120_3 is adjustable.

[0058] In the disclosed embodiment, the diameter and length of the guidewire body 120 are adjustable, so that the guidewire body 120 can be flexibly designed to have different sizes according to the actual lumen structure used, and the characteristic impedance of the guidewire body 120 is designed to be 50 ohms.

[0059] In the embodiment of the present disclosure, the length of the metal wire 120_1 protruding from the insulating layer 120_2 and the metal layer 120_3 is adjustable, so that the length of the metal wire 120_1 protruding from the insulating layer 120_2 and the metal layer 120_3 can be flexibly adjusted according to actual needs, thereby improving the flexibility of adjusting the guide wire body 120.

[0060] Specifically, the length of the metal wire 120_1 protruding from the insulating layer 120_2 and the metal layer 120_3 is adjusted based on the magnetic resonance imaging range and the heating range, wherein the magnetic resonance imaging range represents the imaging requirement range of magnetic resonance imaging of organ tissues, and the heating range represents the requirement range for heating organ tissues.

[0061] In the embodiment of the present disclosure, since the magnetic resonance imaging signal and the radio frequency heating signal are transmitted via the metal wire 120_1, the metal wire 120_1 protruding from the insulating layer 120_2 and the metal layer 120_3 can be used as the receiving end of the magnetic resonance imaging signal and the transmitting end of the radio frequency heating signal. On this basis, since the length of the metal wire 120_1 protruding from the insulating layer 120_2 and the metal layer 120_3 is adjustable, the metal wire 120_1 can be designed to different sizes according to the actual required imaging and heating range. For example, if the imaging range and heating range need to be increased, the protruding length of the metal wire 120_1 is extended; if the imaging range and heating range need to be reduced, the protruding length of the metal wire 120_1 is shortened. As a result, the flexibility of adjusting the imaging range and the heating range is improved, so that accurate treatment of the lesion can be achieved.

[0062] According to an embodiment of the present disclosure, the materials of the metal wire 120_1 and the metal layer 120_3 are non-magnetic metal materials. The material of the insulating layer 120_2 is a non-magnetic insulating material. And the material of the signal processing circuit 110 includes at least one of a non-magnetic material and a weak magnetic material. Specifically, the materials of the first filtering sub-circuit 111_1, the second filtering sub-circuit 111_2, and the tuning matching decoupling sub-circuit 111_3 include at least one of a non-magnetic material and a weak magnetic material.

[0063] In the embodiment of the present disclosure, the non-magnetic metal material includes, but is not limited to, gold, silver, and copper. Since the materials of the metal wire 120_1 and the metal layer 120_3 are non-magnetic metal materials, and the material of the insulating layer 120_2 is non-magnetic insulating material, the guide wire body 120 of the present disclosure can be used in a magnetic resonance environment without image metal artifacts. The guide wire body 120 of the present disclosure has low resistivity and good conductivity, and can effectively transmit signals. In addition, the guide wire body 120 of the present disclosure has good elasticity and flexibility, and is easy to enter the lumen structure.

[0064] In the disclosed embodiment, each structure of the signal processing circuit 110 encapsulated in the housing is made of non-magnetic or weakly magnetic materials such as gold, silver and copper, and can be safely used in a magnetic resonance environment.

[0065] Figure 6 A flow chart schematically illustrates a method for using a guidewire integrating magnetic resonance imaging and radio frequency heating according to an embodiment of the present disclosure.

[0066] like Figure 6 As shown, the method for using the magnetic resonance imaging and radio frequency heating integrated guidewire of this embodiment includes: operation S610.

[0067] In operation S610, the second end of the guide wire body is extended to the target area to collect magnetic resonance imaging signals of the organ tissue in the target area, and the organ tissue in the target area is heated simultaneously.

[0068] The embodiments of the present disclosure are described above. However, these embodiments are only for illustrative purposes and are not intended to limit the scope of the present disclosure. Although the embodiments are described above, this does not mean that the measures in the various embodiments cannot be used in combination to advantage. Without departing from the scope of the present disclosure, those skilled in the art may make a variety of substitutions and modifications, which should all fall within the scope of the present disclosure.

Claims

1. A magnetic resonance imaging and radio frequency heating integrated guide wire, comprising: a signal processing circuit, the signal processing circuit comprising a first filtering subcircuit and a second filtering subcircuit, the first filtering range of the first filtering subcircuit and the second filtering range of the second filtering subcircuit are different from each other, the first end of the first filtering subcircuit is used to connect to a magnetic resonance imaging system, the first end of the second filtering subcircuit is used to connect to a radio frequency generator, and the radio frequency generator is used to provide a radio frequency heating signal to the second filtering subcircuit; as well as A guide wire body, a first end of which is connected to a second end of the first filter subcircuit and a second end of the second filter subcircuit, and the second end of the guide wire body is used to collect magnetic resonance imaging signals of organ tissues; Wherein, the radio frequency heating signal and the magnetic resonance imaging signal are synchronously transmitted in the guide wire body; the frequency range of the magnetic resonance imaging signal corresponds to the first filtering range; and the frequency range of the radio frequency heating signal corresponds to the second filtering range.

2. The method according to claim 1, wherein: The first filtering range has a first degree of difference with respect to the second filtering range; The center frequency of the magnetic resonance imaging system has a second degree of difference with respect to the signal transmission frequency of the radio frequency generator; The first degree of difference corresponds to the second degree of difference.

3. The method according to claim 2, wherein: In the case where the first filtering range is higher than the second filtering range, the center frequency of the magnetic resonance imaging system is higher than the signal transmission frequency of the radio frequency generator; as well as When the first filtering range is lower than the second filtering range, the center frequency of the magnetic resonance imaging system is lower than the signal transmission frequency of the radio frequency generator.

4. The method according to any one of claims 1 to 3, wherein The signal processing circuit further comprises a tuning matching decoupling subcircuit; a first end of the first filtering subcircuit is connected to a first end of the tuning matching decoupling subcircuit, and a second end of the tuning matching decoupling subcircuit is used to connect to the magnetic resonance imaging system.

5. The method according to claim 4, wherein: The second end of the tuning, matching and decoupling subcircuit is connected to the signal transmission line of the magnetic resonance imaging system through a first non-magnetic SMA connector; The first end of the second filtering subcircuit is connected to the signal transmission line of the radio frequency generator through a second non-magnetic SMA connector.

6. The method according to any one of claims 1 to 3, wherein The frequency range of the radio frequency heating signal is 300 KHz to 2.45 GHz; and The magnetic field strength of the magnetic resonance imaging system ranges from 0 to 7.0 T.

7. The method according to any one of claims 1 to 3, wherein The guide wire body includes a coaxially arranged metal wire, an insulating layer wrapping the metal wire, and a metal layer wrapping the insulating layer; the metal wire protrudes axially from the insulating layer and the metal layer, and the length of the metal wire protruding from the insulating layer and the metal layer is adjustable.

8. The method according to claim 7, wherein: The length of the metal wire protruding from the insulating layer and the metal layer is adjusted based on a magnetic resonance imaging range and a heating range, wherein the magnetic resonance imaging range represents the imaging requirement range for magnetic resonance imaging of the organ tissue, and the heating range represents the heating requirement range for the organ tissue.

9. The method according to claim 7, wherein: The metal wire and the metal layer are made of non-magnetic metal materials; The material of the insulating layer is a non-magnetic insulating material; and The material of the signal processing circuit includes at least one of a non-magnetic material and a weakly magnetic material.

10. A method for using the magnetic resonance imaging and radio frequency heating integrated guide wire according to any one of claims 1 to 9, comprising: By extending the second end of the guide wire body to the target area, the magnetic resonance imaging signal of the organ tissue located in the target area is collected, and the organ tissue located in the target area is heated synchronously.

Images