Multi-dimensional perceptual intervention guide wire and preparation method and application thereof

Abstract

The invention relates to the field of medical instruments, in particular to a multi-dimensional perceptual intervention guide wire and a preparation method and application thereof. The multi-dimensional sensing intervention guide wire comprises a guide wire body, a pressure sensing unit, a temperature sensing unit and a plurality of strain sensing units, the pressure sensing unit, the temperature sensing unit and the strain sensing units are distributed in the axial direction of the guide wire body, the pressure sensing unit determines the contact position and contact pressure of the guide wire body, and the temperature sensing unit monitors temperature changes of media around the guide wire body in real time. The strain sensing unit obtains the bending angle and spatial attitude information of the guide wire body in real time; wherein the electrode of the pressure sensing unit is located at the end of the guide wire body, the electrode of the temperature sensing unit is arranged behind the electrode of the pressure sensing unit in the axial direction, and the electrode of the strain sensing unit is arranged behind the temperature sensing electrode in the axial direction and located in the middle of the guide wire body. The multi-physical-quantity sensing device is compact in structure, high in flexibility and capable of achieving multi-physical-quantity sensing on an extremely-small curved surface.

Description

Technical Field

[0001] This invention relates to the field of medical devices, and in particular to a multidimensional sensing interventional guidewire, its preparation method, and its application. Background Technology

[0002] Cardiovascular and cerebrovascular diseases are major causes of death and disability worldwide, with stenosis or occlusion of the coronary arteries, cerebral arteries, and peripheral vessels being common and causing serious harm. To restore blood flow and improve lesion perfusion, interventional treatment techniques have developed rapidly. As one of the most critical instruments in interventional surgery, the guidewire plays a crucial role in vascular access, lesion passage, and instrument navigation; its mechanical and maneuverability directly affects the safety and success rate of the procedure.

[0003] Currently, guidewires used in clinical practice are mainly based on nickel-titanium alloy or stainless steel cores. Different levels of support, torsion control, and passability are achieved by altering the taper, compliant section structure, and surface coating. However, these traditional designs still rely heavily on the surgeon's experience and X-ray fluoroscopy for operation, providing only general information about the guidewire's position and outline, and failing to reflect the real-time state of the vascular environment. When the guidewire advances within a narrow, tortuous, or severely diseased vessel, it is difficult for the surgeon to determine the actual interaction between the guidewire tip and the vessel wall based on imaging, making it impossible to detect whether contact, puncture, jamming, or potential damage has occurred, thus posing surgical risks.

[0004] In addition, existing guidewires cannot provide key information such as force feedback, tactile feedback or temperature changes, and doctors lack real "tactile sensation" during the operation, especially in minimally invasive robotic systems or remote intervention platforms, where this deficiency is more obvious.

[0005] In recent years, interventional medical devices have been widely used in the treatment of cardiovascular, cerebrovascular, and peripheral vascular diseases. Among them, the interventional guidewire, as a key operating element, directly affects the surgical outcome due to its flexibility, controllability, and safety. To achieve precise and reliable vascular access and support delivery, scholars at home and abroad have been continuously exploring technical solutions that integrate multiple functions into the guidewire.

[0006] In terms of end-effector force sensing, researchers have explored structures such as piezoelectric films, MEMS pressure chips, and ion gel capacitive sensors to detect contact forces at the tip of guidewires or on the walls of catheters. These sensors offer high sensitivity but are typically large and rigid, making integration on thin-diameter guidewires difficult and potentially compromising the original flexibility and maneuverability of the guidewire. For temperature and strain sensing, common solutions include fiber Bragg grating (FBG) sensors and strain gauge sensing units. FBG sensors offer high sensitivity and resistance to electromagnetic interference, but their complex layout and high cost make mass integration on sub-millimeter flexible structures difficult. Strain gauge sensors have a simple structure, but traditional metal printing or vapor deposition processes struggle to create stable, continuous conductors on curved surfaces, resulting in insufficient reliability and consistency.

[0007] With the development of flexible electronics and spray coating manufacturing technologies, researchers have begun to use materials such as conductive polymers, silver nanoparticles, and carbon nanotubes to construct multifunctional sensing layers on flexible substrates through spraying, printing, or coating, enabling simultaneous sensing of bending, temperature, and stress. However, traditional sprayed or printed patterns have limited resolution and adhesion in curved areas, making it difficult to meet the application requirements of small-diameter guide wires in highly curved environments; at the same time, most solutions still focus on a single sensing mode, making it difficult to form a multifunctional integrated structure.

[0008] In summary, while existing technologies can achieve local sensing capabilities, they still suffer from insufficient force feedback, limited modality, and incomplete sensing, making it difficult to form a stable and continuous multimodal sensing structure on the surface of a small guidewire. There is an urgent need for an integrated solution that achieves multidimensional sensing on a thin-diameter flexible guidewire to meet the precise navigation and safety requirements in complex interventional environments.

[0009] Current technologies still have significant shortcomings in multidimensional sensing integration for interventional guidewires. First, traditional guidewire surface sensors mostly employ rigid electrodes or piezoelectric thin film structures, which are prone to delamination, breakage, and signal drift in highly curved, small-diameter guidewires, making it difficult to meet the requirements for long-term stable operation in complex vascular environments. Furthermore, the guidewire diameter is typically less than 1 mm, severely limiting the lead layout of the sensor array. Existing fiber optic or MEMS sensing solutions are bulky and complexly packaged, increasing the overall rigidity of the guidewire and reducing its flexibility and maneuverability.

[0010] At the same time, existing flexible electronic fabrication methods are limited in terms of pattern accuracy, uniformity, and adhesion on cylindrical micro-curved surfaces, making it difficult to maintain the stability of continuous wires under extremely small bending radii; multimodal sensing units are also difficult to achieve high-density integration, and problems such as wire crossing, poor interlayer adhesion, and signal crosstalk are prone to occur, thus affecting the overall sensing performance.

[0011] Therefore, existing technologies struggle to achieve high-precision integrated measurement of multiple physical quantities such as pressure, temperature, and strain while ensuring guidewire flexibility and dimensional compatibility. There is an urgent need for a multimodal sensing construction method suitable for the micro-curved surface of fine-diameter guidewires to achieve stable and reliable signal acquisition and transmission in complex vascular environments. Summary of the Invention

[0012] Therefore, the technical problem to be solved by the present invention is to overcome the problems in the prior art, thereby providing a multidimensional sensing interventional guidewire, its preparation method and application.

[0013] Firstly, a multi-dimensional sensing interventional guidewire is provided, comprising:

[0014] Guidewire body;

[0015] A pressure sensing unit is distributed along the axial direction of the guidewire body to determine the contact position and contact pressure of the guidewire body; the pressure sensing unit includes at least one piezoresistive effect-based unit, at least one triboelectric effect-based unit, a first conductive lead connected to the piezoresistive effect-based unit and the triboelectric effect-based unit respectively, and a first signal output terminal connected to the first conductive lead;

[0016] A temperature sensing unit is distributed along the axial direction of the guidewire body to monitor the temperature change of the medium surrounding the guidewire body in real time; the temperature sensing unit includes a temperature sensing electrode, a second conductive lead connected to the temperature sensing electrode, and a second signal output terminal connected to the second conductive lead;

[0017] Multiple strain sensing units are distributed along the axial direction of the guidewire body to acquire the bending angle and spatial attitude information of the guidewire body in real time; each strain sensing unit includes a strain sensing electrode, a third conductive lead connected to the strain sensing electrode, and a third signal output terminal connected to the third conductive lead.

[0018] The piezoresistive effect-based unit and the triboelectric effect-based unit are located at the end of the guidewire body. The temperature sensing electrode is arranged axially adjacent to the piezoresistive effect-based unit and the triboelectric effect-based unit, and the strain sensing electrode is arranged axially adjacent to the temperature sensing electrode and located in the middle of the guidewire body.

[0019] In one embodiment of the present invention, the piezoresistive effect-based unit is a multilayer composite structure, comprising a flexible protective layer, a first functional layer, and a first tactile sensing electrode from top to bottom; the first tactile sensing electrode is a nano-silver ink electrode, providing a stable conductive path; the first functional layer is a pressure-sensitive ink layer, whose resistance changes with compression or stretching under external force.

[0020] In one embodiment of the present invention, the triboelectric effect-based unit is a multilayer composite structure, comprising a second functional layer and a second tactile sensing electrode from top to bottom; the second tactile sensing electrode is a nano-silver ink electrode, providing a stable conductive path.

[0021] In one embodiment of the present invention, the second functional layer 2021 is a composite film of PDMS and PTFE, wherein the PTFE layer has strong negative charge, and when the PDMS layer and the PTFE layer come into contact or separate, interfacial charge transfer occurs, generating triboelectric signals.

[0022] In one embodiment of the present invention, the temperature sensing electrode is a periodic curved structure formed by thermosensitive ink printing, with alternating peaks and troughs and the direction of the wave vector parallel to the axis of the guide wire body.

[0023] In one embodiment of the present invention, the strain sensing electrode is a first periodic curve structure and a second periodic curve structure formed by strain-sensitive ink inkjet printing, and the adjacent ends of the first periodic curve structure and the second periodic curve structure are connected; the peaks and troughs of the first periodic curve structure and the second periodic curve structure alternate and the wave vector direction is parallel to the axis of the guide wire body.

[0024] In one embodiment of the present invention, the first conductive lead, the second conductive lead, and the third conductive lead are formed of nano-silver ink.

[0025] In one embodiment of the present invention, four strain sensing units are provided, and the four strain sensing units are symmetrically arranged along the circumference of the guide wire body at positions of 0°, 90°, 180° and 270°.

[0026] Secondly, a preparation method is provided, utilizing the multidimensional sensing interventional guidewire as described above, including the following steps:

[0027] S1. Pre-treat the guidewire body to form an active layer on the surface of the guidewire body;

[0028] S2. Spray nano-silver ink onto the first preset area on the outer wall of the guidewire body to form a first tactile sensing electrode based on the piezoresistive effect unit, a second tactile sensing electrode based on the triboelectric effect unit, and a first conductive lead; the first tactile sensing electrode and the second tactile sensing electrode are respectively connected to the first signal output terminal through the first conductive lead.

[0029] A first functional layer is formed on top of the first tactile sensing electrode, and then PDMS is spin-coated onto the first functional layer to form a protective layer.

[0030] A second functional layer is formed by spraying a PDMS and PTFE composite film onto the second tactile sensing electrode.

[0031] Simultaneously, temperature-sensing ink is sprayed onto the second preset area on the outer wall of the guide wire body to form a temperature-sensing electrode; nano-silver ink is sprayed onto the end of the temperature-sensing electrode to form a second conductive lead and connect it to the second signal output terminal.

[0032] Strain-sensitive ink is sprayed onto the third preset area on the outer wall of the guide wire body to form a strain-sensing electrode; the two ends of the strain-sensing electrode are connected to the third signal output terminal by spraying nano-silver ink to form a third conductive lead.

[0033] S3. Spin-coat PDMS onto the surface of the guidewire body to form a protective film and reinforce the connection points.

[0034] Thirdly, this paper provides an application of the multidimensional sensing interventional guidewire in vascular intervention as described above.

[0035] Compared with the prior art, the above-described technical solution of the present invention has the following advantages:

[0036] 1. The multidimensional sensing interventional guidewire of this invention improves flexibility and biocompatibility: It employs a PDMS / PTFE composite membrane and SENS series flexible functional materials (SENS-P300, SENS-T02A, SENS-S200) as the main structure, combined with nano-silver ink-printed electrodes, enabling the sensing unit to possess high flexibility, good adhesion, and excellent biocompatibility. This structure can adapt to the complex curvature of vascular cavities and the fluid erosion environment, significantly improving the safety and long-term stability of the guidewire during in vivo use.

[0037] 2. The multi-dimensional sensing interventional guidewire of this invention integrates multimodal sensing functions: By synergistically integrating four types of sensing units—triboelectric tactile, piezoresistive tactile, temperature, and strain sensing—on the guidewire wall, this invention achieves synchronous detection of multimodal physical signals. The guidewire can not only identify contact events and the magnitude of contact force, but also monitor local temperature changes and its own posture deformation, effectively solving the problem of single sensing dimensions in existing technologies.

[0038] 3. The multi-dimensional sensing interventional guidewire structure described in this invention is simplified and its manufacturability is improved: The sensing layer is directly constructed on the outer wall of the guidewire using electrofluid inkjet printing and dispensing processes, avoiding the complexity and high cost associated with traditional multi-layer bonding or micro-assembly methods. All sensing units share an integrated conductive lead structure, resulting in a simple process flow and enabling mass production and highly consistent output.

[0039] 4. The multidimensional sensing interventional guidewire described in this invention has high sensitivity and signal resolution: the pressure sensing unit uses SENS-P300 high-sensitivity material, which can generate a significant resistance response to minute pressure changes; the triboelectric unit utilizes the heterogeneous interface charge effect of PDMS and PTFE, and has a high signal-to-noise ratio output; the temperature sensing unit SENS-T02A and the strain sensing unit SENS-S200 both have linear response characteristics, enabling the guidewire to maintain high resolution and fast response performance in the detection of multiple physical quantities.

[0040] 5. The multidimensional sensing interventional guidewire described in this invention possesses reliability and long-term stability: Through a multi-layer flexible composite structure design, the PDMS protective layer provides mechanical buffering and insulation protection for the sensing layer, effectively preventing structural damage to the guidewire under insertion force and physiological fluid. The high stability of the nano-silver electrode and SENS material ensures the long-term reliability of the signal output, meeting the needs of long-term, dynamic monitoring in clinical operations. Attached Figure Description

[0041] To make the content of this invention easier to understand, the invention will be further described in detail below with reference to specific embodiments and accompanying drawings.

[0042] Figure 1 This is a schematic diagram of the structure of the multidimensional sensing interventional guidewire in this invention;

[0043] Figure 2 yes Figure 1 Enlarged view of point A in the middle;

[0044] Figure 3 This is a schematic diagram of the pressure sensing unit in this invention;

[0045] Figure 4 This is a schematic diagram of the piezoresistive effect unit in this invention;

[0046] Figure 5 This is a schematic diagram of the triboelectric effect-based unit in this invention;

[0047] Figure 6 This is a schematic diagram of the temperature sensing unit in this invention;

[0048] Figure 7 This is a schematic diagram of the strain sensing unit in this invention.

[0049] Explanation of reference numerals in the instruction manual:

[0050] 10. Guidewire body;

[0051] 20. Pressure sensing unit; 201. Piezoresistive effect-based unit; 2011. Flexible protective layer; 2012. First functional layer; 2013. First tactile sensing electrode; 202. Triboelectric effect-based unit; 2021. Second functional layer; 2022. Second tactile sensing electrode; 203. First conductive lead; 204. First signal output terminal;

[0052] 30. Temperature sensing unit; 301. Temperature sensing electrode; 302. Second conductive lead; 303. Second signal output terminal;

[0053] 40. Strain sensing unit; 401. Strain sensing electrode; 402. Third conductive lead; 403. Third signal output terminal. Detailed Implementation

[0054] The present invention will be further described below with reference to the accompanying drawings and specific embodiments, so that those skilled in the art can better understand and implement the present invention. However, the embodiments described are not intended to limit the present invention.

[0055] In interventional guidewire applications, existing sensor technologies face significant challenges due to the guidewire diameter typically being less than 1 mm and the need to operate in highly tortuous vascular environments. Specifically, rigid sensor structures are prone to delamination, breakage, and signal drift on micro-curved surfaces, making it difficult to maintain long-term stable operation. Simultaneously, limited lead wire layout makes the integration of multimodal sensing units difficult, easily leading to wire crossing and signal crosstalk. Furthermore, traditional spraying or printing processes lack sufficient pattern precision and adhesion on cylindrical micro-curved surfaces, failing to guarantee the stability of continuous leads. These problems directly reduce the reliability of the sensed signal, affecting the surgeon's judgment of the interaction between the guidewire and the vessel wall, thereby increasing surgical risks.

[0056] For example, in interventional procedures for chronic total occlusion of coronary arteries, the guidewire must traverse highly calcified and tortuous segments of the vessel. When the guidewire tip approaches the stenosis, the lack of real-time pressure feedback makes it impossible to accurately sense the contact state between the guidewire and the vessel wall; simultaneously, the absence of temperature change information makes it difficult to monitor the physiological state of the vessel wall. In this scenario, the instability and modal uniformity of sensor signals result in a lack of necessary tactile information during the procedure, easily leading to vascular perforation or dissection.

[0057] If the aforementioned issues are not addressed, the sensing capabilities of guidewires in complex vascular environments will be insufficient to meet the demands of precise intervention. Specifically, inaccurate or incomplete sensing signals can lead to misoperations, such as excessive pressure causing vascular damage, or failure to promptly identify dangerous conditions, resulting in delayed treatment. This not only reduces surgical success rates but may also trigger serious complications, endangering patient lives. Furthermore, the limitations of current technology restrict the application of interventional guidewires in minimally invasive robotic systems and remote platforms, hindering the further development of interventional treatment techniques.

[0058] In this regard, combined with Figures 1 to 3 , Figure 6 and Figure 7 This embodiment proposes a multidimensional sensing interventional guidewire, including:

[0059] Guide wire body 10;

[0060] The pressure sensing unit 20 is distributed along the axial direction of the guide wire body 10 to determine the contact position and contact pressure of the guide wire body 10. The pressure sensing unit 20 includes at least one piezoresistive effect-based unit 201, at least one triboelectric effect-based unit 202, a first conductive lead 203 connected to the piezoresistive effect-based unit 201 and the triboelectric effect-based unit 202 respectively, and a first signal output terminal 204 connected to the first conductive lead 203.

[0061] Temperature sensing unit 30 is distributed along the axial direction of the guide wire body 10 to monitor the temperature change of the medium around the guide wire body 10 in real time; temperature sensing unit 30 includes temperature sensing electrode 301, second conductive lead 302 connected to temperature sensing electrode 301, and second signal output terminal 303 connected to second conductive lead 302.

[0062] Multiple strain sensing units 40 are distributed along the axial direction of the guidewire body 10 to acquire the bending angle and spatial attitude information of the guidewire body 10 in real time. The strain sensing unit 40 includes a strain sensing electrode 401, a third conductive lead 402 connected to the strain sensing electrode 401, and a third signal output terminal 403 connected to the third conductive lead 402.

[0063] The piezoresistive effect-based unit 201 and the triboelectric effect-based unit 202 are located at the end of the guidewire body 10. The temperature sensing electrode 301 is arranged axially adjacent to the piezoresistive effect-based unit 201 and the triboelectric effect-based unit 202. The strain sensing electrode 401 is arranged axially adjacent to the temperature sensing electrode 301 and located in the middle of the guidewire body 10.

[0064] For ease of understanding, the following explains some key terms in this embodiment:

[0065] Multidimensional sensing interventional guidewire: refers to an interventional guidewire that integrates multiple sensing functions (such as pressure, temperature, strain) to acquire information about the internal vascular environment in real time, assisting doctors in precise navigation and operation.

[0066] Guidewire body 10: As the core support structure of the interventional guidewire, it is usually a slender, flexible rod-shaped object used for advancement and guidance within the blood vessel.

[0067] Pressure sensing unit 20: used to detect the pressure magnitude and contact position when the guidewire body 10 contacts the blood vessel wall or other tissues, so as to provide tactile feedback.

[0068] Piezoresistive effect unit 201: One type of pressure sensing unit 20, which senses pressure by means of the principle that the resistance of a material changes when it is under pressure.

[0069] Triboelectric effect unit 202: Another type of pressure sensing unit 20, which senses pressure by means of charge transfer generated when two different materials come into contact or separate.

[0070] Temperature sensing unit 30: Used to monitor the temperature changes of the medium surrounding the guidewire body 10 in real time, and can be used to assess local blood flow, inflammation or tissue damage.

[0071] Strain sensing unit 40: used to acquire the angle and overall spatial posture information of the guidewire body 10 when it bends in the blood vessel in real time, so as to reflect the deformation state of the guidewire.

[0072] The first conductive lead 203, the second conductive lead 302, and the third conductive lead 402 are used to transmit the electrical signals generated by the pressure sensing unit 20, the temperature sensing unit 30, and the strain sensing unit 40 to the external processing system, respectively.

[0073] The first signal output terminal 204, the second signal output terminal 303, and the third signal output terminal 403 serve as signal output interfaces for the pressure sensing unit 20, the temperature sensing unit 30, and the strain sensing unit 40, respectively, and are connected to an external processing system.

[0074] This embodiment provides a multidimensional sensing interventional guidewire, whose structural design aims to achieve comprehensive sensing of the intravascular environment. The guidewire includes a guidewire body 10, a pressure sensing unit 20, a temperature sensing unit 30, and multiple strain sensing units 40.

[0075] The guidewire body 10 forms the framework of the entire interventional guidewire and is typically made of materials with good flexibility and biocompatibility, such as nickel-titanium alloys or polymers. The guidewire body 10 usually has a small diameter to accommodate the fine structure of blood vessels. In practical applications, the guidewire body 10 can be designed with different stiffnesses and tapers to meet the needs of various interventional procedures.

[0076] The pressure sensing unit 20 is distributed along the axial direction of the guide wire body 10, and its main function is to determine the contact position and contact pressure of the guide wire body 10. This pressure sensing unit 20 can be implemented in various ways. For example, a piezoresistive sensor can be used, which senses pressure by coating a layer of piezoresistive material on the surface of the guide wire body 10. When this material is subjected to external pressure, its resistance changes, and the pressure information can be derived by measuring the resistance change. Another implementation is a sensor based on the triboelectric effect, which uses two layers of materials with different triboelectric polarities on the surface of the guide wire body 10. When these two layers of materials move relative to each other due to contact or friction, charge separation occurs, generating a measurable electrical signal that is related to the contact pressure. These pressure sensing elements are connected to the first signal output terminal 204 via a first conductive lead 203 to transmit the sensed pressure signal to an external processing device.

[0077] Temperature sensing units 30 are also distributed along the axial direction of the guidewire body 10, used to monitor the temperature changes of the medium surrounding the guidewire body 10 in real time. Temperature sensing units 30 can be composed of temperature sensing electrodes 301. For example, temperature sensing electrodes 301 can be made of a thermistor material, whose resistance changes with temperature; temperature information can be obtained by measuring the resistance. The temperature sensing electrode 301 is connected to a second signal output terminal 303 via a second conductive lead 302 to output a temperature signal.

[0078] Multiple strain sensing units 40 are also distributed along the axial direction of the guidewire body 10, and their function is to acquire the bending angle and spatial attitude information of the guidewire body 10 in real time. Each strain sensing unit 40 can be composed of strain sensing electrodes 401. When the guidewire body 10 bends, the strain gauge deforms accordingly, and its resistance value changes, thus reflecting the strain state of the guidewire. These strain sensing electrodes 401 are connected to a third signal output terminal 403 via a third conductive lead 402 for outputting strain signals.

[0079] In terms of structural layout, the piezoresistive effect unit 201 and the triboelectric effect unit 202 are strategically positioned at the end of the guidewire body 10. This is because the end of the guidewire is the area where it first contacts and primarily interacts with the blood vessel wall, and placing the pressure sensing function here can provide the most direct tactile feedback. The temperature sensing electrode 301 is positioned axially immediately following the piezoresistive effect unit 201 and the triboelectric effect unit 202 to monitor the local temperature immediately after pressure sensing, which helps to assess the physiological state of the contact area. The strain sensing electrode 401 is positioned axially immediately following the temperature sensing electrode 301 and located in the middle of the guidewire body 10. This position allows for better capture of the overall bending and deformation of the guidewire in complex vascular pathways, thus providing comprehensive spatial attitude information. This axially layered layout enables different types of sensors to work collaboratively, providing multi-dimensional environmental perception capabilities.

[0080] Combination Figure 3 and Figure 4 This embodiment further proposes a multi-layer composite structure based on the piezoresistive effect unit 201, which includes a flexible protective layer 2011, a first functional layer 2012, and a first tactile sensing electrode 2013 from top to bottom. Among them, the first tactile sensing electrode 2013 is a nano-silver ink electrode, providing a stable conductive path; the first functional layer 2012 is a pressure-sensitive ink layer, whose resistance changes with compression or stretching under external force.

[0081] Specifically, a "multilayer composite structure" refers to a structure formed by stacking different materials or functional layers in a specific order, aiming to achieve comprehensive performance that is difficult to achieve with a single material through the synergistic effect of each layer. This structure can be realized in various ways; for example, layer-by-layer deposition technology can be used to sequentially spray or print each layer of material onto the surface of the guidewire body 10. The flexible protective layer 2011 is located on the outermost side of the piezoresistive effect unit 201. Its main function is to provide physical and chemical protection for the internal sensitive structure, resisting erosion and damage from the external environment (such as body fluids and mechanical friction), while maintaining overall flexibility to accommodate the bending and movement of the guidewire body 10 within the blood vessel. The first functional layer 2012 is the core sensing part based on the piezoresistive effect unit 201. Its material properties undergo measurable electrical changes under external force, thereby achieving pressure sensing. The first tactile sensing electrode 2013 is responsible for collecting the electrical signals generated by the first functional layer 2012 and reliably transmitting them to the subsequent signal processing circuit.

[0082] The flexible protective layer 2011 can be prepared from PDMS, which refers to a thin film made of polydimethylsiloxane. PDMS is an elastomer with excellent flexibility, biocompatibility, chemical stability, and optical transparency. PDMS can be prepared by spin coating, blade coating, or spray coating, where the PDMS prepolymer is coated onto the first functional layer 2012 and then cured.

[0083] "Nano-silver ink electrode" refers to an electrode formed on a flexible substrate using conductive ink containing nano-sized silver particles through printing techniques (such as inkjet printing, screen printing, etc.). Due to its excellent conductivity, good flexibility, and biocompatibility, nano-silver ink is particularly suitable for constructing fine and stable conductive paths in flexible medical devices. The main function of this electrode is to provide a low-resistance, highly stable electrical signal transmission channel, ensuring that the weak resistance change signals generated by the first functional layer 2012 can be accurately and effectively acquired.

[0084] The “pressure-sensitive ink layer” refers to the SENS-P300 piezoresistive functional material deposited by a dispensing machine. When the guide wire comes into contact with the cavity wall, the SENS-P300 layer is compressed, its resistance decreases, and it outputs an electrical signal proportional to the pressure intensity, which is used to determine the magnitude of the contact force.

[0085] Combination Figure 3 and Figure 5 This embodiment further proposes that the triboelectric effect unit 202 is a multilayer composite structure, which includes a second functional layer 2021 and a second tactile sensing electrode 2022 from top to bottom; the second tactile sensing electrode 2022 is a nano-silver ink electrode, providing a stable conductive path.

[0086] A multilayer composite structure refers to a structure composed of two or more different materials stacked together, aiming to combine the advantages of each layer to achieve comprehensive performance that is difficult to achieve with a single material. This structure can be formed by sequentially depositing, coating, or laminating different functional layer materials onto a substrate. Employing a multilayer composite structure provides structural stability, mechanical strength, and functional layered optimization for the triboelectric effect-based unit 202. The stacking order from top to bottom, including the second functional layer 2021 and the second tactile sensing electrode 2022, clarifies the spatial arrangement of the components within the triboelectric effect-based unit 202. The second functional layer 2021 can serve as the main generation layer for the triboelectric effect, directly contacting the external medium or indirectly through a protective layer, while the second tactile sensing electrode 2022 is located below it, used to collect the charge signal generated by the triboelectric effect. This specific layer sequence design helps optimize the generation and collection efficiency of triboelectric signals and the structural integration.

[0087] This embodiment further proposes that the second functional layer 2021 is a composite film of PDMS and PTFE, wherein the PTFE layer has strong negative charge, and when PDMS comes into contact with or separates from it, interfacial charge transfer occurs, generating triboelectric signals.

[0088] Specifically, PDMS (polydimethylsiloxane) is an organosilicon polymer with good biocompatibility, flexibility, and chemical stability, and typically exhibits strong positive charge in the triboelectric field. PTFE (polytetrafluoroethylene), on the other hand, is a high-performance fluoropolymer with an extremely low coefficient of friction and excellent chemical inertness, making it a typical strongly negatively charged material in the triboelectric sequence. Combining PDMS and PTFE to form a composite film can fully utilize the significant electrical differences between the two in the triboelectric sequence. The strong negative charge of the PTFE layer means that it tends to gain electrons and become negatively charged when in contact with most other materials, which is the basis for the triboelectric effect. When the PDMS / PTFE composite film comes into contact with or separates from an object, charge transfer occurs, thereby generating a triboelectric signal.

[0089] like Figure 6 As shown, this embodiment further proposes that the temperature sensing electrode 301 is a periodic curve structure formed by thermosensitive ink printing, with alternating peaks and troughs and the direction of the wave vector parallel to the axis of the guide wire body 10.

[0090] Specifically, "thermal ink printing formation" refers to the manufacturing materials and processes of the temperature sensing electrode 301. Thermal ink is a material whose electrical properties (e.g., resistance) change significantly and predictably with temperature. For example, conductive ink containing metal nanoparticles (such as platinum or nickel) can be used, whose resistivity increases linearly with increasing temperature; or ink containing semiconductor materials can be used, whose resistivity decreases exponentially with increasing temperature. In this embodiment, SENS-T02A thermal ink can be used. Printing formation is a precise material deposition technique that allows thermal ink to be directly printed onto the surface of the guide wire body 10 in a preset pattern, thereby ensuring the miniaturization of the electrode and its good bonding with the guide wire body 10. "Periodic curve structure" refers to a pattern that repeats in space and has specific waveform characteristics, such as a serpentine, sawtooth, or spiral shape. The purpose of this structure is to maximize the effective length of the temperature-sensing material within a limited axial space, thereby improving the sensitivity of temperature sensing. The phrase "its alternating crests and troughs, with the wave vector direction parallel to the axis of the guidewire body 10" further defines the specific morphology and spatial orientation of the periodic curved structure. "Alternating crests and troughs" means the structure exhibits a continuous, undulating wave-like or curved shape, which helps to disperse stress when the guidewire body 10 bends, maintaining the integrity of the electrode and electrical continuity. "The wave vector direction is parallel to the axis of the guidewire body 10" indicates that the main extension direction of the periodic curved structure is consistent with the axial direction of the guidewire body 10. For example, for a serpentine structure, its overall "S"-shaped arrangement extends along the axis of the guidewire. This design allows the temperature sensing electrode 301 to better adapt to the axial flexibility of the guidewire body 10 and provide continuous temperature sensing capability along its entire axial length.

[0091] like Figure 7As shown, this embodiment further proposes a structure for the strain-sensing electrode 401, which includes a first periodic curve structure and a second periodic curve structure formed by inkjet printing of strain-sensitive ink. The strain-sensitive ink is a special conductive material whose resistance changes measurably with deformation (stretching or compression). In this embodiment, SENS-S200 strain-sensitive ink can be used. Through inkjet printing technology, this ink can be precisely deposited on the surface of the guide wire body 10 to form an electrode with a specific pattern. This formation method not only enables the miniaturization and flexibility of the electrode, ensuring a good match with the flexibility of the guide wire body 10, but also guarantees good adhesion between the electrode and the guide wire body 10, thereby ensuring that the electrode can deform synchronously and generate an accurate resistance signal when the guide wire body 10 is bent. The first periodic curve structure and the second periodic curve structure refer to the electrode's geometry exhibiting repeating, wavy, or serpentine curve patterns. Compared to simple linear electrodes, this periodic curve structure provides a longer effective conductive path for the same axial length. This allows it to effectively convert the macroscopic bending deformation of the guidewire body 10 into tensile or compressive deformation of the electrode itself when the guidewire body 10 bends, resulting in a more significant resistance change and improved strain sensing sensitivity. For example, this structure can be designed as a series of interconnected "S" or "C" shaped units, or a spiral pattern. The adjacent ends of the first and second periodic curve structures are connected, meaning that these two periodic curve structures are spatially interconnected, forming a continuous electrical path. This connection allows the two structures to work collaboratively to sense the strain of the guidewire body 10, thereby expanding the effective sensing range, or enhancing signal strength and improving measurement reliability through series or parallel connections. The peaks and troughs of the first and second periodic curve structures alternate, and the wave vector direction is parallel to the axis of the guidewire body 10. This alternating peak and trough design allows the electrode to better adapt to bending deformation when the guidewire body 10 bends. When the guidewire body 10 bends, a portion of the periodic curved structure is in a stretched state (e.g., located on the outside of the bend), while another portion is in a compressed state (e.g., located on the inside of the bend). This differential deformation produces a more pronounced change in resistance. The wave vector direction is parallel to the axis of the guidewire body 10, meaning that the main extension direction of the periodic curved structure is consistent with the axial direction of the guidewire body 10. This orientation design ensures that the electrodes can primarily sense the bending deformation of the guidewire body 10 along its axial direction, thereby accurately capturing the bending angle and spatial orientation information of the guidewire body 10 and avoiding sensing errors caused by orientation mismatch.

[0092] This embodiment further proposes that the first conductive lead 203, the second conductive lead 302, and the third conductive lead 402 are formed from nano-silver ink.

[0093] In this embodiment, nano-silver ink is used to form conductive leads, whose main function is to provide a stable, low-resistance electrical signal transmission path, effectively transmitting the electrical signals generated by each sensing unit to an external processing unit. The first conductive lead 203, the second conductive lead 302, and the third conductive lead 402 are key components connecting each sensing unit (including the piezoresistive effect-based unit 201, the triboelectric effect-based unit 202, the temperature sensing electrode 301, and the strain sensing electrode 401) to their corresponding signal terminals (first signal output terminal 204, second signal output terminal 303, and third signal output terminal 403), responsible for transmitting the sensed electrical signals from the sensor end to the external circuit for processing. The geometry, width, and thickness of these conductive leads can be designed according to signal transmission requirements, the diameter of the guide wire body 10, and integration requirements with other components. For example, they can be designed as long, thin strips or spirals to accommodate the flexibility of the guide wire body 10.

[0094] This embodiment further proposes that there are four strain sensing units 40, which are symmetrically arranged around the circumference of the guide wire body 10 at positions of 0°, 90°, 180° and 270°.

[0095] To obtain more comprehensive information on the bending angle and spatial attitude of the guidewire body 10, this embodiment increases the number of strain sensing units 40 to four. The arrangement of multiple strain sensing units 40 allows for more complete capture of the deformation of the guidewire body 10 in different directions, thus providing richer and more reliable raw data for subsequent data processing. For example, four independent strain sensors can be used, or a strain sensor array can be divided into four independent sensing regions. The symmetrical arrangement of the strain sensing units 40 is crucial for accurately resolving the spatial attitude of the guidewire body 10. By symmetrically arranging the four strain sensing units 40 at 90-degree intervals along the circumference of the guidewire body 10 at positions of 0°, 90°, 180°, and 270°, it can be ensured that at least two strain sensing units 40 can effectively respond to deformation and provide complementary strain data in any bending direction. This symmetrical layout can effectively eliminate directional bias in measurement and simplify the attitude calculation algorithm. For example, a microelectromechanical system (MEMS) strain sensor or a fiber Bragg grating (FBG) sensor can be used and precisely integrated into a preset position on the guide wire body 10.

[0096] This embodiment achieves precise sensing of the bending and torsional posture of the guidewire body 10 in three-dimensional space by symmetrically arranging four strain sensing units 40 along the circumferential direction in the middle of the guidewire body 10. When the guidewire body 10 bends, the strain sensing unit 40 located on the outer side of the bend will be subjected to tensile strain, while the strain sensing unit 40 located on the inner side of the bend will be subjected to compressive strain. Since these four strain sensing units 40 are symmetrically distributed at 90° intervals, they can capture the bending deformation of the guidewire body 10 in any plane. For example, when the guidewire body 10 bends in the 0°-180° plane, the strain sensing units 40 at the 0° and 180° positions will respond primarily, while the strain sensing units 40 at the 90° and 270° positions will provide auxiliary information. By comparing and analyzing the output signals of these four strain sensing units 40, the bending direction and bending angle of the guidewire body 10 can be accurately calculated. In addition, this symmetrical layout also helps to identify the torsional deformation of the guidewire body 10, because torsion will cause the strain sensing units 40 at different positions to produce specific differential responses. This multi-point, symmetrical strain sensing mechanism significantly improves the accuracy and comprehensiveness of acquiring spatial posture information of the guidewire body 10, thereby providing reliable data support for precise operations in interventional surgery and effectively solving the problem of inaccurate posture sensing by single or asymmetrical sensors in complex environments.

[0097] The working principle of this embodiment is as follows:

[0098] The multimodal sensing system on the outer wall of the guidewire body 10 achieves collaborative detection through sensing units with different mechanisms. The pressure sensing unit 20 generates a transient triboelectric signal when the guidewire contacts the blood vessel wall to determine "contact status," while the piezoresistive effect unit 201 outputs an electrical signal related to pressure intensity to assess the degree of contact. After signal fusion, the system can determine the guidewire contact status in real time and output a warning signal when the contact risk is too high, providing operational reference for doctors or the control system.

[0099] The temperature sensing unit 30 utilizes the temperature-dependent resistance characteristics of SENS-T02A ink to continuously monitor the local ambient temperature of the guidewire. Its high sensitivity and flexibility ensure stable signal output in the complex fluid environment within blood vessels.

[0100] The strain sensing unit 40 detects the bending state of the guidewire by the resistance change of the SENS-S200 functional layer. Combined with tactile and temperature information, it can realize the comprehensive status recognition of the guidewire in the blood vessel.

[0101] Through the above design, the present invention realizes the coordinated sensing of four types of signals: triboelectric tactile, piezoresistive tactile, temperature and strain. The guidewire has multimodal sensing capabilities without changing the overall structural dimensions, providing a real-time feedback basis for safe and accurate interventional operations.

[0102] The materials used in this embodiment are as follows: nano silver conductive ink (AgNPInk), SENS-P300 piezoresistive functional ink, SENS-T02A thermosensitive ink, SENS-S200 strain-sensitive ink (all purchased from Shanghai Mifang Electronics Co., Ltd.), PDMS (Sylgard 184, prepolymer liquid to curing agent volume ratio 10:1), PTFE powder, isopropyl alcohol (IPA), and 502 glue.

[0103] The aforementioned functional inks are all commercially available materials and can be replaced by alternative materials with the same conductivity, piezoresistive properties, temperature sensitivity, and strain sensitivity without affecting the implementation effect of this invention.

[0104] This embodiment also proposes a method for preparing a multidimensional sensing interventional guidewire, including the following steps:

[0105] S1. Pre-treat the surface of the guide wire body 10 to form an active layer. Specifically, ultrasonically clean the guide wire body 10 with isopropanol for 10 minutes to remove surface impurities, dry it, and then place it in an oxygen plasma cleaner at 100W power for 5 minutes to form an active layer on the surface, improving ink adhesion. The wettability of the treated guide wire body 10 surface is enhanced, which is beneficial to the uniformity and accuracy of subsequent inkjet printing patterns.

[0106] S2. Electrohydraulic inkjet printing (EHD) technology is used to print nano-silver ink on the first preset area of ​​the outer wall of the guide wire body 10 to form a first tactile sensing electrode 2013 based on the piezoresistive effect unit 201, a second tactile sensing electrode 2022 based on the triboelectric effect unit 202, and a first conductive lead 203; the first tactile sensing electrode 2013 and the second tactile sensing electrode 2022 are respectively connected to the first signal output terminal 204 through the first conductive lead 203;

[0107] A first functional layer 2012 is formed above the first tactile sensing electrode 2013, followed by spin-coating PDMS to form a protective layer 2011. Specifically, SENS-P300 ink is deposited above the first tactile sensing electrode 2013 using a dispensing machine to form a first functional layer 2012 approximately 25 μm thick, which is then cured at 80°C for 10 minutes. Subsequently, PDMS is spin-coated as the protective layer 2011, with the thickness of the protective layer 2011 controlled to within 50 μm to ensure sufficient flexibility and biocompatibility of the guidewire when bent.

[0108] A second functional layer 2021 is formed by spraying a PDMS and PTFE composite film onto the second tactile sensing electrode 2022. Specifically, the PDMS and PTFE composite film is sprayed onto the second tactile sensing electrode 2022, with PTFE powder uniformly dispersed in a PDMS prepolymer solution at a mass ratio of 1:10, and cured at 80°C for 30 minutes to form the second functional layer 2021. This structure is used to generate detectable triboelectric signals when the guidewire contacts or separates from the cavity wall, enabling contact event recognition.

[0109] Simultaneously, temperature-sensing ink is sprayed onto the second preset area on the outer wall of the guide wire body 10 to form a temperature-sensing electrode 301; nano-silver ink is sprayed onto the end of the temperature-sensing electrode 301 to form a second conductive lead 302 and connect it to the second signal output terminal 303. Specifically, EHD sprayed SENS-T02A ink is used to form the temperature-sensing electrode 301 to improve the temperature sensing length and sensitivity.

[0110] Strain-sensitive ink is sprayed onto a third preset area on the outer wall of the guidewire body 10 to form a strain-sensing electrode 401. The two ends of the strain-sensing electrode 401 are connected to a third signal output terminal 403 via nano-silver ink spraying to form third conductive leads 402. Specifically, SENS-S200 strain-sensitive ink is sprayed using EHD, employing a wavy pattern to accommodate the bending deformation of the guidewire. The two ends of the strain-sensing electrode 401 are connected to the third signal output terminal 403 via the third conductive leads 402, and annealed and cured at 120°C for 20 minutes for monitoring the guidewire's posture and bending angle.

[0111] S3. Spin-coat PDMS onto the surface of the guidewire body 10 to form a protective film and reinforce the connection points. Specifically, after the overall printing is completed, spin-coat a thin PDMS protective layer, approximately 30μm–40μm thick, onto the surface of the guidewire body 10 to prevent mechanical damage to the sensing layer and erosion by physiological fluids. After curing, expose the signal leads at the ports of each sensing area and reinforce each wire connection point with 502 glue.

[0112] It should be noted that the parameters for electrohydraulic inkjet printing are set as follows: voltage 2.8kV–3.2kV, inkjet distance 3mm, and inkjet speed 0.5mm / s. After printing, the inkjet layer is annealed at 120℃ for 30 minutes to form a continuous conductive network with a thickness of approximately 2μm–3μm, exhibiting good conductivity and adhesion.

[0113] Through the above-described process, a flexible interventional guidewire integrating triboelectric tactile, piezoresistive, temperature, and strain multimodal sensing functions on its outer wall can be obtained. This guidewire has a compact structure, good flexibility, and a smooth, uniform surface, making it suitable for multi-physical signal detection in complex physiological environments such as vascular cavities.

[0114] This embodiment further illustrates the application of the aforementioned multidimensional sensing interventional guidewire in vascular intervention.

[0115] Interventional vascular surgery refers to minimally invasive procedures that involve inserting catheters, guidewires, and other instruments into blood vessels through puncture to diagnose or treat vascular lesions. These procedures demand extremely high precision in instrument positioning, operational feedback, and safety. The multi-dimensional sensing interventional guidewire proposed in this embodiment, by integrating pressure, temperature, and strain sensing capabilities, can provide physicians with real-time and comprehensive guidewire status information, thereby significantly improving the accuracy and safety of interventional vascular surgery. Its applications can include, but are not limited to, coronary artery intervention, peripheral vascular intervention, and neurovascular intervention. For example, in coronary artery intervention, the guidewire needs precise navigation in narrowed or tortuous blood vessels; in peripheral vascular intervention, it may be necessary to assess the stiffness of thrombi or stenotic segments; and in neurovascular intervention, even higher requirements are placed on guidewire flexibility and precise manipulation.

[0116] In interventional vascular surgery, the aforementioned multidimensional sensing guidewire is introduced into the patient's blood vessel. As the guidewire body 10 travels within the vessel, its end pressure sensing unit 20, including a piezoresistive effect-based unit 201 and a triboelectric effect-based unit 202, can monitor the contact position and pressure between the guidewire and the vessel wall in real time. This allows the physician to perceive the force exerted on the guidewire within the vessel, preventing excessive pressure that could damage the vessel. Simultaneously, the temperature sensing electrode 301 of the temperature sensing unit 30 can monitor the temperature changes of the surrounding medium (such as blood or contrast agent) in real time, which is crucial for assessing local blood flow or monitoring drug release. Furthermore, multiple strain sensing units 40, distributed axially along the middle of the guidewire body 10, acquire real-time information on the bending angle and spatial orientation of the guidewire body 10 through the strain sensing electrode 401, providing the physician with precise position and shape feedback of the guidewire in three-dimensional space within the vessel. This multi-dimensional information is transmitted to an external processing device through the first signal output terminal 204, the second signal output terminal 303, and the third signal output terminal 403. After analysis, it is presented to the doctor in an intuitive way. In this way, the doctor can monitor the precise state of the guidewire in the blood vessel in real time, thereby making more accurate judgments and operations, effectively reducing surgical risks and improving the success rate of the operation.

[0117] By applying the aforementioned multidimensional sensing interventional guidewire to the field of vascular intervention, the limitations of traditional interventional guidewires in providing only single information feedback and restricting operational precision during surgery are resolved. This application allows physicians to obtain multidimensional information in real time, including the contact pressure of the guidewire within the blood vessel, the temperature of the surrounding medium, and the bending posture of the guidewire itself, greatly enhancing the visualization and controllability of the surgery. This not only helps physicians accurately determine the position and state of the guidewire within the blood vessel, effectively avoiding risks such as vascular injury and perforation, but also significantly improves the success rate and safety of interventional procedures, bringing better treatment outcomes to patients.

[0118] Obviously, the above embodiments are merely illustrative examples for clear explanation and are not intended to limit the implementation. Those skilled in the art will recognize that other variations or modifications can be made based on the above description. It is neither necessary nor possible to exhaustively list all possible implementations here. However, obvious variations or modifications derived therefrom are still within the scope of protection of this invention.

Claims

1. A multidimensional sensing interventional guidewire, characterized in that, include: Guide wire body (10); The pressure sensing unit (20) is distributed along the axial direction of the guide wire body (10) to determine the contact position and contact pressure of the guide wire body (10); the pressure sensing unit (20) includes at least one piezoresistive effect-based unit (201), at least one triboelectric effect-based unit (202), a first conductive lead (203) connected to the piezoresistive effect-based unit (201) and the triboelectric effect-based unit (202) respectively, and a first signal output terminal (204) connected to the first conductive lead (203). A temperature sensing unit (30) is distributed along the axial direction of the guide wire body (10) to monitor the temperature change of the medium around the guide wire body (10) in real time. The temperature sensing unit (30) includes a temperature sensing electrode (301), a second conductive lead (302) connected to the temperature sensing electrode (301), and a second signal output terminal (303) connected to the second conductive lead (302). Multiple strain sensing units (40) are distributed along the axial direction of the guide wire body (10) to acquire the bending angle and spatial attitude information of the guide wire body (10) in real time; the strain sensing unit (40) includes a strain sensing electrode (401), a third conductive lead (402) connected to the strain sensing electrode (401), and a third signal output terminal (403) connected to the third conductive lead (402). The piezoresistive effect-based unit (201) and the triboelectric effect-based unit (202) are located at the ends of the guidewire body (10). The temperature sensing electrode (301) is arranged axially adjacent to the piezoresistive effect-based unit (201) and the triboelectric effect-based unit (202). The strain sensing electrode (401) is arranged axially adjacent to the temperature sensing electrode (301) and located in the middle of the guidewire body (10).

2. The multidimensional sensing interventional guidewire according to claim 1, characterized in that, The piezoresistive effect-based unit (201) is a multi-layer composite structure, comprising a flexible protective layer (2011), a first functional layer (2012), and a first tactile sensing electrode (2013) from top to bottom; the first tactile sensing electrode (2013) is a nano-silver ink electrode, providing a stable conductive path; the first functional layer (2012) is a pressure-sensitive ink layer, whose resistance changes with compression or stretching under external force.

3. The multidimensional sensing interventional guidewire according to claim 1, characterized in that, The triboelectric effect-based unit (202) is a multilayer composite structure, including a second functional layer (2021) and a second tactile sensing electrode (2022) from top to bottom; the second tactile sensing electrode (2022) is a nano-silver ink electrode, providing a stable conductive path.

4. The multidimensional sensing interventional guidewire according to claim 3, characterized in that, The second functional layer (2021) is a composite membrane of PDMS and PTFE.

5. The multidimensional sensing interventional guidewire according to claim 1, characterized in that, The temperature sensing electrode (301) is a periodic curve structure formed by thermosensitive ink printing, with alternating peaks and troughs and the direction of the wave vector parallel to the axis of the guide wire body (10).

6. The multidimensional sensing interventional guidewire according to claim 1, characterized in that, The strain sensing electrode (401) is a first periodic curve structure and a second periodic curve structure formed by strain-sensitive ink spraying, with adjacent ends of the first periodic curve structure and the second periodic curve structure connected; the peaks and troughs of the first periodic curve structure and the second periodic curve structure alternate and the wave vector direction is parallel to the axis of the guide wire body (10).

7. The multidimensional sensing interventional guidewire according to claim 1, characterized in that, The first conductive lead (203), the second conductive lead (302) and the third conductive lead (402) are formed of nano silver ink.

8. The multidimensional sensing interventional guidewire according to claim 1, characterized in that, The strain sensing unit (40) is provided in four positions, which are symmetrically arranged around the circumference of the guide wire body (10) at 0°, 90°, 180° and 270°.

9. A preparation method, characterized in that, Using the multidimensional sensing interventional guidewire as described in any one of claims 1-8, the procedure includes the following steps: S1. Pre-treat the guidewire body (10) to form an active layer on the surface of the guidewire body (10); S2. Nano-silver ink is sprayed onto the first preset area on the outer wall of the guide wire body (10) to form a first tactile sensing electrode (2013) based on the piezoresistive effect unit (201), a second tactile sensing electrode (2022) based on the triboelectric effect unit (202), and a first conductive lead (203); the first tactile sensing electrode (2013) and the second tactile sensing electrode (2022) are respectively connected to the first signal output terminal (204) through the first conductive lead (203); A first functional layer (2012) is formed on top of the first tactile sensing electrode (2013), and then a protective layer (2011) is formed by spin coating PDMS on the first functional layer (2012). A second functional layer (2021) is formed by printing a PDMS and PTFE composite film onto the second tactile sensing electrode (2022). Meanwhile, temperature sensing ink is sprayed on the second preset area on the outer wall of the guide wire body (10) to form a temperature sensing electrode (301); nano silver ink is sprayed on the end of the temperature sensing electrode (301) to form a second conductive lead (302) and connected to the second signal output end (303). Strain-sensitive ink is sprayed onto the third preset area on the outer wall of the guide wire body (10) to form a strain sensing electrode (401); the two ends of the strain sensing electrode (401) are formed into a third conductive lead (402) by spraying nano silver ink and connected to the third signal output end (403). S3. Spin-coat PDMS onto the surface of the guidewire body (10) to form a protective film and reinforce the connection area.

10. The application of the multidimensional sensing interventional guidewire as described in any one of claims 1-8 in vascular intervention.

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