CN106859762B - Electrophysiology catheter - Google Patents
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- CN106859762B CN106859762B CN201510927223.7A CN201510927223A CN106859762B CN 106859762 B CN106859762 B CN 106859762B CN 201510927223 A CN201510927223 A CN 201510927223A CN 106859762 B CN106859762 B CN 106859762B
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- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
- A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
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Abstract
The invention provides an electrophysiology catheter, which is characterized in that a support tube, at least one strain component and a temperature compensation component are arranged at the distal end of the catheter, the strain component is used for acquiring a first strain quantity generated under the joint action of the contact force of the distal end of the catheter and the ambient temperature, and the temperature compensation component is used for compensating the strain quantity generated by the ambient temperature in the first strain quantity, so that the actual strain quantity generated under the action of the contact force of the distal end of the catheter only is obtained. According to the invention, the temperature compensation part is arranged to perform temperature compensation on the strain magnitude measured by the strain part, so that the strain magnitude actually generated by the contact force is obtained, the change of the contact force at the far end can be accurately judged, and the measurement accuracy is improved.
Description
Technical Field
The invention relates to the technical field of medical catheters, in particular to an electrophysiology catheter.
Background
In recent years, interventional therapy has been available using catheter systems for conditions such as cardiac arrhythmias, refractory hypertension, etc. For example, in the treatment of atrial fibrillation in arrhythmia, an ablation or mapping catheter enters the heart through a vein or an artery, maps the heart to find the position or the path of an abnormal electric signal, and then applies energy to perform ablation to stop or change the useless electric signal so as to achieve the treatment effect. If the refractory hypertension is treated by renal artery ablation, the electrophysiology catheter enters the connecting artery between the abdominal aorta and the kidney from the artery, and the parasympathetic nerve pathway is ablated and blocked, so that the function of reducing the blood pressure is achieved.
During the ablation process, the contact force of the electrode at the distal end of the catheter with the vessel wall or tissue is important. When the contact force is small, the ablation focus is shallow, and abnormal electric signals or nerve conduction cannot be effectively isolated, and when the contact force is large, the safety risk is increased.
In response to the above problems, it has emerged that a pressure sensor is placed at the distal end of the catheter to effectively obtain a value of the contact force of the electrode with the vessel wall or tissue. For example, a position sensor using magnetic induction is added in a catheter to sense the contact force between the distal end of the catheter and an organ, but the sensor has certain limitations in application, such as being easily interfered by an external magnetic field to distort the result, and in addition, the realization of other functions of the catheter is limited based on the use of the magnetic field, such as a three-dimensional magnetic positioning system and the like. Pressure sensitive materials are also used as the base of the force sensor to sense the load at the distal end of the catheter, but this system can only accurately measure axial loads and lacks accuracy for non-axial loads. There are also force sensing catheters which mainly use optical fiber sensing systems to measure the contact force between the catheter and the vessel wall or the surface of an organ, but the packaging difficulty is high, the preparation process is complex, the price is high, and external electrical signal equipment is required.
Aiming at the problems of the pressure sensor arranged at the far end of the catheter, the electrophysiology catheter for realizing the pressure sensing function based on the strain gauge technology is developed subsequently, and the strain gauge mainly takes a metal grid wire embedded in a plastic substrate as an induction element to induce the external strain. When the strain gage is deformed, the wire is elongated and compressed to become thicker, thereby causing a change in the resistance of the wire. The weak resistance change is amplified through the bridge circuit, so that the magnitude of the strain is known. The electrophysiology catheter has the advantages of no influence of electromagnetic radiation environment, low cost, high sensitivity and the like.
Referring to fig. 1 and fig. 2, the electrophysiology catheter implementing the pressure sensing function based on the strain gauge technology mainly includes three strain gauges 121 'and a supporting tube 120' disposed at the distal end of the electrophysiology catheter, the three strain gauges 121 'are uniformly disposed on the supporting tube 120', and the supporting tube 120 'is an elastic tube that deforms under pressure, so that the strain gauges 121' can sensitively provide the change of the contact force at the distal end of the electrophysiology catheter, but the strain gauges are greatly affected by temperature in the actual use process, as shown in the following formula:
εCombined＝εtem+εstrain；
εCombinedfor the magnitude of the measured strain,. epsilontemIs strained by strain force, epsilonstrainIs the strain due to temperature, and the magnitude of the measured strain is equal to the sum of the strain due to strain force and the strain due to temperature. Fig. 2 is a graph of the output measurement result of the pressure sensor of fig. 1 as a function of temperature, as shown in fig. 2, the base line (without stress) of the strain gauge in practical application fluctuates greatly at different temperatures enough to cover the signal generated by the strain force (e.g., the signal in the region D in fig. 2, which is particularly drawn to represent the stress and the temperature is not changed for easy understanding and comparison, and cannot be shown if the temperature changes continuously during the practical measurement), so that the accuracy of the measurement is reduced, and therefore, the temperature compensation needs to be performed on the strain gauge. Therefore, there is a need to design an electrophysiology catheter with temperature compensation to improve the accuracy of the measurement.
Disclosure of Invention
The invention aims to provide an electrophysiology catheter, which aims to solve the problem that when the contact force at the distal end of the catheter is measured based on a strain gauge in the prior art, the strain gauge is influenced by temperature to cause the reduction of the measurement accuracy.
In order to solve the technical problem, the invention provides an electrophysiology catheter, which is provided with a catheter distal end and comprises an ablation electrode, a supporting tube, at least one strain component and a temperature compensation component, wherein the ablation electrode, the supporting tube, the at least one strain component and the temperature compensation component are arranged at the catheter distal end; the supporting tube is connected with the ablation electrode, the strain component and the temperature compensation component are arranged on the supporting tube, and the supporting tube has an elastic deformation section; the strain component is arranged on the elastic deformation section and used for generating a first strain quantity under the combined action of the contact force of the far end of the catheter and the environment temperature, and the temperature compensation component is used for compensating the strain quantity generated by the environment temperature in the first strain quantity so as to obtain the actual strain quantity generated under the action of the contact force.
Optionally, in the electrophysiology catheter, the strain component is a first strain gauge; the temperature compensation component is a temperature sensor and is used for sensing the environment temperature, and further provides a second strain quantity generated by the first strain gauge under the action of the environment temperature through a temperature compensation curve of the first strain gauge, and the second strain quantity is used for compensating the strain quantity generated by the environment temperature in the first strain quantity.
Optionally, in the electrophysiology catheter, the strain component is a first strain gauge; the temperature compensation component is a second strain gauge and is used for generating a second strain quantity under the action of the ambient temperature, the second strain quantity is used for compensating the strain quantity generated by the ambient temperature in the first strain quantity, and the first strain gauge and the second strain gauge have the same resistance temperature coefficient, linear expansion coefficient, strain sensitivity coefficient and initial resistance value.
Optionally, in the electrophysiology catheter, the supporting tube further includes an inelastic deformation section, the first strain gauge is disposed on the elastic deformation section of the supporting tube, and the second strain gauge is disposed on the inelastic deformation section of the supporting tube.
Optionally, in the electrophysiology catheter, the first strain gauge includes a comb-teeth wire, a polymer sheet, and a wire, the comb-teeth wire is fixed in the polymer sheet, each of the comb-teeth wire is parallel to the axial direction of the support tube, and the wire is connected to the comb-teeth wire and extends out of the polymer sheet, and is used for connecting to an electronic component in the handle of the electrophysiology catheter.
Optionally, in the electrophysiology catheter, the second strain gauge includes a comb-teeth wire, a polymer sheet, and a wire, the comb-teeth wire is fixed in the polymer sheet, each of the comb-teeth wire is parallel to the axial direction of the support tube, and the wire is connected to the comb-teeth wire and extends out of the polymer sheet, and is used for connecting to an electronic component in the handle of the electrophysiology catheter.
Optionally, in the electrophysiology catheter, the second strain gauge includes a comb-tooth wire, a polymer sheet, and a wire, the comb-tooth wire is fixed in the polymer sheet, each of the comb-tooth wires is perpendicular to the axial direction of the support tube, and the wire is connected to the comb-tooth wire, extends out of the polymer sheet, and is used for connecting to an electronic component in the handle of the electrophysiology catheter.
Optionally, in the electrophysiology catheter, the first strain gauge and the second strain gauge are integrated or separated.
Optionally, in the electrophysiology catheter, the first strain gauge and the second strain gauge are all multiple and are uniformly arranged along the circumference of the electrophysiology catheter, and each second strain gauge is arranged at the front end or the rear end of the first strain gauge along the axial direction of the electrophysiology catheter.
Optionally, in the electrophysiology catheter, the elastic deformation section of the supporting tube is provided with a plurality of notches for deforming the deformation section.
Optionally, in the electrophysiology catheter, the elastically deformable section of the support tube has a helical indentation.
Optionally, in the electrophysiology catheter, the support tube is a metal tube or a plastic tube.
Optionally, in the electrophysiology catheter, the electrophysiology catheter further includes a deflectable section, a catheter main body, and a control handle, the catheter distal end, the deflectable section, the catheter main body, and the control handle are connected in sequence, and the control handle is connected with the deflectable section through a pull wire and controls deflection of the deflectable section.
In the electrophysiology catheter provided by the invention, the sensor is arranged at the distal end of the catheter and comprises a supporting tube, at least one strain component and a temperature compensation component, wherein the strain component is used for generating a first strain quantity under the joint action of the contact force of the distal end of the catheter and the ambient temperature, and the temperature compensation component is used for compensating the first strain quantity so as to obtain an actual strain quantity generated only by the contact force of the distal end of the catheter. According to the invention, the temperature compensation part is arranged to perform temperature compensation on the strain magnitude measured by the strain part, so that the strain magnitude actually generated by the contact force is obtained, the change of the contact force at the far end can be accurately judged, and the measurement accuracy is improved.
Drawings
FIG. 1 is a schematic diagram of a prior art pressure sensor of an electrophysiology catheter;
FIG. 2 is a graph of results of output measurements as a function of temperature using the pressure sensor of FIG. 1;
FIG. 3 is a schematic illustration of the electrophysiology catheter of the present invention performing cardiac ablation;
FIG. 4 is a schematic perspective view of a sensor at the distal end of an electrophysiology catheter in accordance with a second embodiment of the present invention;
FIG. 5 is a cross-sectional view of a pressure sensor of the electrophysiology catheter, in accordance with a second embodiment of the present invention;
FIG. 6 is a graph of the variation of voltage with time before temperature compensation of the electrophysiology catheter in the second embodiment of the present invention;
FIG. 7 is a graph of the variation of voltage with time after temperature compensation of the electrophysiology catheter in the second embodiment of the invention;
FIG. 8 is a schematic perspective view of a sensor at the distal end of an electrophysiology catheter in accordance with a third embodiment of the present invention;
FIGS. 9a and 9b are schematic structural views of a strain member according to a second or third embodiment of the present invention;
fig. 9c is a schematic perspective view of a sensor at the distal end of an electrophysiology catheter in accordance with a fourth embodiment of the present invention.
In fig. 1 to 2, a pressure sensor 12'; a support tube 120'; a strain gauge 121';
in fig. 3 to 9c, the electrophysiology catheter 1; a catheter distal end 11; a sensor 12; a support tube 120; a deformation section 120 a; a non-deformation section 120 b; a strain member 121; a first strain gauge 121 a; a second strain gauge 121 b; polymeric sheets 122, 122a, 122 b; comb wires 123a, 123 b; a deflectable segment 13; a catheter body 14; a control handle 15; a tail 16; a control panel 17; a puncture sheath 18; the left atrium 19.
Detailed Description
The electrophysiology catheter proposed by the present invention is further explained in detail with reference to the figures and the specific embodiments. Advantages and features of the present invention will become apparent from the following description and from the claims. It is to be noted that the drawings are in a very simplified form and are not to precise scale, which is merely for the purpose of facilitating and distinctly claiming the embodiments of the present invention.
Fig. 3 is a schematic view of the electrophysiology catheter of the present invention performing cardiac ablation. As shown in fig. 3, the electrophysiology catheter 1 performs ablation through the puncture sheath 18, via the inferior vena cava, into the left atrium 19. The embodiment of the present invention provides an electrophysiology catheter 1 comprising a distal catheter end 11, a deflectable segment 13, a catheter body 14 and a control handle 15 connected in series. The distal end 11 of the catheter is provided with an ablation electrode, energy can be applied to perform ablation, and the material of the ablation electrode is a metal material, and can be stainless steel, gold or platinum-iridium alloy. The distal end 11 of the catheter is further provided with a first strain gauge for generating a first strain under the combined contact force of the distal end 11 of the catheter and the ambient temperature. The control handle 15 can control the deflectable segment 13 to achieve deflection. The catheter body 14 is generally made of a polymer material, which may be PU (Polyurethane), PEBAX (nylon elastomer), nylon or PU with a metal woven mesh, and the diameter of the tubing is not more than 9F.
The electrophysiology catheter 1 is connected with a control system at the rear end through a tail wire 16, ablation energy and ablation time can be set on a control panel 17 of the control system, and changes of output power, impedance, electrode temperature and distal contact force in the ablation process can be displayed in real time. In the invention, a temperature compensation component is arranged to compensate the strain quantity generated by the environment temperature in the first strain quantity of the first strain gauge, so as to obtain the actual strain quantity of the first strain gauge under the action of the far-end contact force and accurately judge the change of the far-end contact force.
Example one
In order to reduce the influence of temperature-induced strain on the measurement accuracy, the electrophysiology catheter 1 of the present embodiment further includes a temperature sensor as a temperature compensation component disposed at the distal end 11 of the catheter and near the first strain gauge, wherein a temperature compensation curve of the first strain gauge in a certain working state can be provided by a supplier of the strain gauge or can be measured by a user, and the temperature compensation curve can be stored in the control system. Therefore, after the temperature sensor senses the ambient temperature near the strain gauge and outputs the sensed temperature value, the control system can calculate the second strain quantity generated by the first strain gauge at a specific temperature through the temperature compensation curve. After the first strain quantity is obtained through the far-end first strain gauge, the actual strain quantity generated by the far-end contact force can be obtained through mathematical operation. The temperature sensor is preferably a type K thermocouple, but may be another type thermocouple.
Example two
Although the purpose of temperature compensation can be achieved by the first embodiment, since the temperature is obtained by the temperature sensor, and the amount of strain caused by the temperature is obtained by the temperature compensation curve, the accuracy of the amount of strain is affected by the accuracy of the temperature sensor and the accuracy of the temperature compensation curve, which leads to inaccuracy of the measurement result. The placing position of the second strain gauge meets the requirement that 1) deformation does not occur; 2) the working environment of the first strain gage is the same or similar enough. The characteristics of the second strain gauge should satisfy: the second strain gauge has the same temperature coefficient of resistance, linear expansion coefficient, strain sensitivity coefficient and initial resistance value as the first strain gauge.
As shown in fig. 4, the electrophysiology catheter 1 further comprises a support tube 120, a strain component 121 and a temperature compensation component, said support tube 120 comprising an elastically deformable section 120a and an inelastically deformable section 120 b. In this embodiment, the strain component 121 includes three first strain gauges 121a, the temperature compensation component includes one second strain gauge 121b, and the first strain gauge 121a and the second strain gauge 121b are the same strain gauge, but have different functions due to different positions. The first strain gauge 121a is disposed in the elastic deformation section 120a of the support tube 120 to generate a first strain amount under the combined action of the contact force of the distal end 11 of the catheter and the ambient temperature, and the second strain gauge 121b is disposed in the non-deformation section 120b of the support tube 120 to generate a second strain amount under the action of the ambient temperature, so as to obtain the first strain amount and the second strain amount through a circuit, and compensate the strain amount generated by the ambient temperature in the first strain amount by using the second strain amount, i.e., obtain the actual strain amount generated by the contact force of the distal end.
The support tube 120 is a metal tube or a plastic tube, the elastically deformable section 120a of the support tube 120 is formed by a cutting process, and the inelastically deformable section 120b of the support tube 120 does not need to be formed by a cutting process. Preferably, the elastically deformable section 120a of the support tube 120 has a plurality of notches for deforming the elastically deformable section 120 a. In this embodiment, the elastically deformable section 120a of the support tube 120 has a spiral notch to deform differently under various contact forces in different directions. As shown in fig. 5, the strain part 121 is preferably embedded inside the support tube 120, so as to better sense the magnitude of the contact force.
In order to better illustrate the feasibility of the technical solution in this embodiment, a map of the strain component 121 is explained by taking an example where the strain component 121 includes three first strain gauges 121a and one second strain gauge 121b, specifically referring to fig. 6 and 7, where fig. 6 is a graph of voltage changes with time before temperature compensation in the first embodiment of the present invention; FIG. 7 is a graph of voltage versus time after temperature compensation according to an embodiment of the present invention. Before temperature compensation, that is, the first strain gauges 121a (three in this embodiment) and the second strain gauge 121b (one in this embodiment) both sense the strain of the distal end 11 of the catheter, as shown in fig. 6, the trends of the four strain gauges (the first strain gauge 121a and the second strain gauge 121b) with temperature change are approximately the same in the time-dependent voltage spectrum, and the strain caused by the contact force is masked. After temperature compensation, that is, the difference between the strain result sensed by the second strain gauge 121b and the values of the three first strain gauges 121a is obtained, so that temperature compensation is obtained, and the drift of the baseline after temperature compensation is significantly improved, as shown in fig. 7 and table 1.
TABLE 1
Of course, in other embodiments, the elastically deformable section 120a and the non-elastically deformable section 120b of the support tube may also be a split structure, that is, two different tubes, and the support tube may further include a liner tube and a metal tube, the liner tube has a structure corresponding to the metal tube, the liner tube is a plastic or rubber tube made of TPU, PVC, PEBAX, or nylon, and is connected to the metal tube by epoxy resin glue or other adhesive, the metal tube is fixed inside the liner tube, and the first strain gauge 121a and the second strain gauge 121b are both circumferentially disposed on the liner tube. The first strain gauge 121a is fixed to the lining pipe corresponding to the cut metal pipe, and the second strain gauge 121b is fixed to the lining pipe corresponding to the uncut metal pipe. Preferably, the strain element 121 is embedded in the wall of the liner. The diameter range of the liner tube is 1-3 mm, and preferably 2 mm. Because the thickness of the strain gauge is very thin, the use of the liner tube can enable the very thin strain gauge to reduce the crease and maintain the sensing capability. The support tube may have various other structural forms as long as a part of the support tube is deformable and another part of the support tube is not deformable.
EXAMPLE III
The difference between the third embodiment and the second embodiment is that each first strain gauge 121a is correspondingly provided with one second strain gauge 121b for temperature compensation, so that the accuracy of the strain measurement result is further improved. As shown in fig. 8, each first strain gauge 121a is followed by a second strain gauge 121b along the axial extension direction of the liner, so as to simulate the working environment of the first strain gauge 121a, thereby improving the accuracy of the temperature-generated strain result and the accuracy of the contact force-generated strain result.
Please refer to fig. 9a and 9b to understand the structural schematic diagram of the strain element in the second or third embodiment of the present invention. The first strain gauge 121a and the second strain gauge 121b in the strain component 121 may be an integral structure or a split structure, and if the first strain gauge 121a and the second strain gauge 121b are an integral structure, the structure may specifically include the following structures:
the structure I is as follows: as shown in fig. 9a, the first strain gauge 121a and the second strain gauge 121b are integrated, the first strain gauge 121a includes a comb-shaped wire 123a, a polymer sheet 122a and a conductive wire, the comb-shaped wire 123a refers to a plurality of connected wires arranged in a comb-tooth shape, the connected wires are fixed in the polymer sheet 122a and are parallel to the axial direction of the support tube 120, and the conductive wire is connected to the end of the comb-shaped wire 123a and extends out of the polymer sheet 122 a; the second strain gauge 121b also includes comb-teeth wires 123b, a polymer sheet 122b, and a lead, wherein the comb-teeth wires 123b are fixed in the polymer sheet 122b and are parallel to the axial direction of the metal tube, and the lead is connected to the ends of the comb-teeth wires 123b and extends out of the polymer sheet 122 b.
At this time, the first strain gauge 121a and the second strain gauge 121b share one polymer sheet 122, the arrangement direction of the comb-teeth wires 123a of the first strain gauge 121a and the arrangement direction of the comb-teeth wires 123b of the second strain gauge 121b are consistent and do not interfere with each other, and the comb-teeth wires 123a of the first strain gauge 121a correspond to the deformation sections 120a of the support tube 120 to simultaneously sense the contact force and the temperature change of the distal end 11 of the catheter; the comb-teeth wire 123b of the second strain gauge 121b corresponds to the non-deformed section 120b of the support tube 120 to sense only the change in temperature at and around the distal end 11 of the catheter. In practical application, the comb-teeth wires 123a, 123b of the first strain gage 121a and the second strain gage 121b are parallel to the axial direction of the support tube. The wires of the first strain gage 121a and the second strain gage 121b are not related to each other.
The structure II is as follows: as shown in fig. 9b, the first strain gage 121a and the second strain gage 121b are also integrated, except that the arrangement direction of the comb-teeth wires 123a of the first strain gage 121a and the arrangement direction of the comb-teeth wires 123b of the second strain gage 121b are perpendicular to each other. In practical application, the comb-teeth wire 123a of the first strain gage 121a is parallel to the axial direction of the support tube, and the comb-teeth wire 123b of the second strain gage 121b is perpendicular to the axial direction of the support tube. Based on the strain component 121 with this structure, since the comb-teeth wires 123b of the second strain gauge 121b are perpendicular to the axial direction of the support tube, when the distal end 11 of the catheter is axially stressed, the second strain gauge 121b is less affected by the contact force of the distal end and is only sensitive to temperature; because the comb-teeth wire 123a of the first strain gauge 121a is parallel to the axial direction of the liner tube, when the distal end 11 of the catheter is axially stressed, the first strain gauge 121a will change and be sensitive to the stress and temperature. The second strain gauge 121b adopting this arrangement method can sense the second strain amount under the temperature action more accurately. At this time, the conductive line of the first strain gage 121a may also be connected with the conductive line of the second strain gage 121 b. In practical applications, the second strain gauge 121b may be selectively disposed above or below the first strain gauge 121a as long as the second strain gauge 121b is disposed in the inelastic deformation section.
Example four
As shown in fig. 9c, in the present embodiment, the second strain gauge 121b may be disposed above the first strain gauge 121a and located at the inelastic deformation section. In order to reduce the production cost and the manufacturing difficulty of the strain gauge, the first strain gauge 121a and the second strain gauge 121b may be designed to be split, that is, the comb-teeth wires 123a of the first strain gauge 121a and the comb-teeth wires 123b of the second strain gauge 121b are distributed and fixed on different polymer sheets, at this time, the first strain gauge 121a may have the same structure as the second strain gauge 121b, only in the actual application, the arrangement direction of the comb-teeth wires 123a of the first strain gauge 121a needs to be parallel to the axial direction of the support tube, and the arrangement of the comb-teeth wires 123b of the second strain gauge 121b is not limited, and may be arranged along the circumferential direction of the support tube, or may be arranged along the axial direction of the support tube.
The embodiments in the present description are described in a progressive manner, each embodiment focuses on differences from other embodiments, and the same and similar parts among the embodiments are referred to each other.
In summary, in the electrophysiology catheter provided by the invention, the support tube, the at least one strain component and the temperature compensation component are arranged at the distal end of the catheter, the strain component is used for generating a first strain amount under the combined action of the contact force of the distal end of the catheter and the ambient temperature, and the temperature compensation component is used for acquiring the ambient temperature or generating a second strain amount under the action of the ambient temperature so as to compensate the strain amount generated by the ambient temperature in the first strain amount, thereby acquiring the actual strain amount generated only under the action of the contact force of the distal end of the catheter. According to the invention, the temperature compensation part is arranged, so that the magnitude of the strain actually generated by the contact force can be obtained, the change of the contact force at the far end can be accurately judged, and the measurement accuracy is improved.
The above description is only for the purpose of describing the preferred embodiments of the present invention, and is not intended to limit the scope of the present invention, and any variations and modifications made by those skilled in the art based on the above disclosure are within the scope of the appended claims.
Claims (7)
1. An electrophysiology catheter having a catheter distal end, comprising an ablation electrode disposed at the catheter distal end, a support tube, at least one strain component, and a temperature compensation component; the supporting tube is connected with the ablation electrode, the strain component and the temperature compensation component are arranged on the supporting tube, the supporting tube comprises an elastic deformation section and an inelastic deformation section, and the elastic deformation section of the supporting tube is provided with a plurality of notches for enabling the elastic deformation section to deform;
the strain component is arranged in the elastic deformation section and used for generating a first strain quantity under the combined action of a contact force at the far end of the catheter and the ambient temperature, the strain component is a first strain sheet, the first strain sheet is arranged in the elastic deformation section of the support tube, the first strain sheet comprises comb-tooth metal wires, a polymer sheet and a lead, the comb-tooth metal wires are fixed in the polymer sheet, all the metal wires in the comb-tooth metal wires are parallel to the axial direction of the support tube, and the lead is connected with the comb-tooth metal wires, extends out of the polymer sheet and is used for being connected to electronic components in the handle of the electrophysiology catheter;
the temperature compensation component is used for compensating the strain quantity generated by the environment temperature in the first strain quantity so as to obtain the actual strain quantity generated only under the action of the contact force, the temperature compensation component is a second strain gauge which is used for generating a second strain quantity under the action of the environment temperature, the second strain quantity is used for compensating the strain quantity generated by the environment temperature in the first strain quantity, the second strain gauge is arranged in the inelastic deformation section of the support tube and comprises comb-tooth metal wires, a high-molecular sheet and a lead, the comb-tooth metal wires are fixed in the high-molecular sheet, all the metal wires in the comb-tooth metal wires are parallel or vertical to the axial direction of the support tube, and the lead is connected with the comb-tooth metal wires and extends out of the high-molecular sheet, an electronic component for connection into the electrophysiology catheter handle;
the first strain gauge and the second strain gauge are integrated, and the first strain gauge and the second strain gauge share one polymer sheet.
2. The electrophysiology catheter of claim 1, wherein the first strain gage and the second strain gage have the same temperature coefficient of resistance, linear expansion coefficient, strain sensitivity coefficient, and initial resistance value.
3. The electrophysiology catheter of claim 1, wherein the first strain gauge and the second strain gauge are uniformly arranged along the circumference of the electrophysiology catheter, and each second strain gauge is disposed at the front end or the rear end of the first strain gauge along the axial direction of the electrophysiology catheter.
4. The electrophysiology catheter of claim 1, wherein the elastically-deformed section of the support tube has a helical indentation.
5. The electrophysiology catheter of claim 1, wherein the support tube is a metal tube or a plastic tube.
6. The electrophysiology catheter of any one of claims 1-5, wherein the strain component is disposed in a wall of the support tube.
7. The electrophysiology catheter of any one of claims 1-5, further comprising a deflectable segment, a catheter body, and a control handle, the catheter distal end, deflectable segment, catheter body, and control handle being connected in series, and the control handle being connected to the deflectable segment by a pull wire and providing deflection control over the deflectable segment.
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| Application Number | Priority Date | Filing Date | Title |
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| CN201510927223.7A CN106859762B (en) | 2015-12-11 | 2015-12-11 | Electrophysiology catheter |
| PCT/CN2016/108875 WO2017097200A1 (en) | 2015-12-11 | 2016-12-07 | Electrophysiology catheter |
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| CN201510927223.7A CN106859762B (en) | 2015-12-11 | 2015-12-11 | Electrophysiology catheter |
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| CN101132730A (en) * | 2005-03-04 | 2008-02-27 | 恩杜森斯公司 | System for mapping and intervention of an organ within the human or animal body |
| CN102160909A (en) * | 2009-12-28 | 2011-08-24 | 韦伯斯特生物官能(以色列)有限公司 | Catheter with strain gauge sensor |
| CN203915066U (en) * | 2014-06-06 | 2014-11-05 | 乐普（北京）医疗器械股份有限公司 | A kind of medical catheter head end that can measuring pressure |
| CN204072317U (en) * | 2014-09-02 | 2015-01-07 | 上海微创电生理医疗科技有限公司 | A kind of ablation catheter |
| CN204318750U (en) * | 2014-11-27 | 2015-05-13 | 上海微创电生理医疗科技有限公司 | A kind of electrophysiologicalcatheter catheter |
| CN204744408U (en) * | 2015-06-30 | 2015-11-11 | 四川锦江电子科技有限公司 | Melt device with pressure detection |
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| US8628520B2 (en) * | 2006-05-02 | 2014-01-14 | Biosense Webster, Inc. | Catheter with omni-directional optical lesion evaluation |
| US8157789B2 (en) * | 2007-05-24 | 2012-04-17 | Endosense Sa | Touch sensing catheter |
| CN102269567A (en) * | 2010-06-03 | 2011-12-07 | 陈彦平 | Self-compensating integrated strain gauge of concrete |
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2015
- 2015-12-11 CN CN201510927223.7A patent/CN106859762B/en active Active
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2016
- 2016-12-07 WO PCT/CN2016/108875 patent/WO2017097200A1/en active Application Filing
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| CN101132730A (en) * | 2005-03-04 | 2008-02-27 | 恩杜森斯公司 | System for mapping and intervention of an organ within the human or animal body |
| CN102160909A (en) * | 2009-12-28 | 2011-08-24 | 韦伯斯特生物官能(以色列)有限公司 | Catheter with strain gauge sensor |
| CN203915066U (en) * | 2014-06-06 | 2014-11-05 | 乐普（北京）医疗器械股份有限公司 | A kind of medical catheter head end that can measuring pressure |
| CN204072317U (en) * | 2014-09-02 | 2015-01-07 | 上海微创电生理医疗科技有限公司 | A kind of ablation catheter |
| CN204318750U (en) * | 2014-11-27 | 2015-05-13 | 上海微创电生理医疗科技有限公司 | A kind of electrophysiologicalcatheter catheter |
| CN204744408U (en) * | 2015-06-30 | 2015-11-11 | 四川锦江电子科技有限公司 | Melt device with pressure detection |
Also Published As
| Publication number | Publication date |
|---|---|
| CN106859762A (en) | 2017-06-20 |
| WO2017097200A1 (en) | 2017-06-15 |
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