CN219962889U - Single-pole composite microelectrode - Google Patents
Single-pole composite microelectrode Download PDFInfo
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- CN219962889U CN219962889U CN202320646023.4U CN202320646023U CN219962889U CN 219962889 U CN219962889 U CN 219962889U CN 202320646023 U CN202320646023 U CN 202320646023U CN 219962889 U CN219962889 U CN 219962889U
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Abstract
The utility model discloses a monopole composite microelectrode, which belongs to the technical field of microelectrodes, and particularly comprises an electrode body, wherein an outer shielding layer is arranged outside the electrode body, and the front end and the rear end of the electrode body penetrate through the outer shielding layer; the electrode body comprises a detection electrode inner core and an electrode tail end, wherein the detection electrode inner core comprises a composite metal control electrode formed by a tungsten wire inner core and a gold-plating layer, and a coverThe glass tube is arranged outside the composite metal control electrode, the front end and the rear end of the composite metal control electrode penetrate through the glass tube, the tail end of the electrode is a copper wire outer-cladding inner insulating layer, and the rear end of the tungsten wire inner core is fixedly connected with the front end of the copper wire. The utility model can be used for heart activity mapping, and the sensitivity of detection signals meets the highest resolution of 50um 2 The minimum identifiable signal voltage amplitude is 50uV, the electromagnetic interference resistance is high, the electrode structure can be used in a conventional shielding network environment, the operability of the electrode structure is high, and repeated mapping can be realized.
Description
Technical Field
The utility model relates to the technical field of microelectrodes, in particular to a monopolar composite microelectrode.
Background
Bioelectric signals are one of the important components for maintaining biological activity and information exchange between cells. Bioelectric activity of cardiac tissue also participates in maintaining an important function of the electrical conduction and mechanical coupling of the heart, and abnormal changes thereof may lead to heart rhythm disorders or development of arrhythmia. Identification of changes in electrical activity between heart tissue is one of the important means of understanding the mechanisms by which the heart maintains physiological states and pathologies. The study of cardiac electrical signals has been a century history, ranging from the earliest electrocardiography to the recording of electrical activity of the heart as a whole, to the diaphragm technology to the recording of cellular action potentials, and to the recent application of high density three-dimensional electrical mapping of the whole heart. The accuracy and flux of bioelectric signal detection are greatly improved. By deepening analysis and understanding of bioelectric activities, research and development of related medicaments and improvement of success rate of clinical arrhythmia surgery are further promoted.
Currently applied bioelectric mapping techniques are largely classified into intracellular mapping and extracellular mapping according to the study objectives. The intracellular mapping is mainly realized by applying patch clamp technology, and can record the change of cell action potential, the electric activity performance of a single ion channel and the like. The method has higher precision, but has low flux, and can only record the activity performance in one cell, so that the effect of the electric signal on the tissue level is difficult to analyze. The method is mainly applied to intracellular signal transduction analysis, toxicity of the medicine to cell ion channels and the like. The extracellular mapping is mainly used for mapping research on tissue layers or whole organs, and can record the changes of extracellular field potentials in different ranges according to the size of the electrode section, so that high-flux recording can be realized. However, the current precision is lower, and the mixed potential signal of the group cells (the three-dimensional signal is generally mixed with more than hundred cells) is mainly applied to the intra-operative mapping of the clinical electrophysiological operation, and can integrate information of tens of thousands of points to study the whole electric activity performance of tissues or organs. The application of the technology has realized the success rate of surgical intervention to clinical laboratory early, room up speed, typical room speed and the like approaching 90 percent. However, in recognizing the progress of complex arrhythmia such as scar atrial rate, atrial fibrillation, ventricular rate and the like, mainly because the spatial resolution of extracellular mapping is generally greater than 1mm, the time synchronous activation of cellular electric activities can cause superposition of recorded electric signals, and the activation directions can not be distinguished in local space, so that the analysis of conduction mechanisms is limited.
Extracellular mapping is classified into monopolar signal mapping and bipolar signal mapping according to the content of the acquired signals. The monopole mapping is made of 2-4mm high-conductivity metal to be a detection head end, and the single-strand conducting wire is connected with the tail end of the insulating anti-interference plastic connection to the signal amplifier, so that the full-time electric activity in a cell cycle can be recorded, and the depth of a signal source can be indirectly judged by identifying the positive and negative of a recorded waveform in the two-dimensional mapping process. However, unipolar signals tend to merge into more electrode-surrounding signals, and the analysis accuracy of local signals is lower. The bipolar mapping needs to apply the detection head end of the double channels, the recorded electric signals are related to the distance between 2 detection head ends, only the electric signals between the electrodes are recorded, signals except the two detection head ends can be shielded, and the bipolar mapping has advantages in local signal analysis, but part of information can be lost due to signal algorithm in the content of the signals.
Therefore, the further improvement of the accuracy of the extracellular mapping electrode is of great significance for understanding the overall performance of the electrical signal in a physiological state and diagnosing and treating clinical complex arrhythmia. By further reducing the probe tip of the monopolar electrode, the influence of the surrounding field potential on the target potential can be reduced without affecting the signal integrity, but the signal anti-interference performance needs to be improved at the same time, because the target signal source obtained by reducing the probe electrode is more accurate, the amplitude of the target signal source is obviously reduced, and the influence of the surrounding electromagnetic field is probably relatively larger. At the same time, the role between microelectrodes and mapping tissue requires availability, and the more tiny probe tips are more prone to damage due to low operating fault tolerance. In general, microelectrode recording is accomplished by utilizing high conductivity wires and glass electrodes filled with electrolyte. The microelectrode with the metal electrode as the main body is currently used for mapping the tissue field potential, and the mapping precision range is more than 200um. The metal electrode has better toughness and hardness, strong operability, suitability for high-flux and large-range repeated mapping, relatively low sensitivity and difficult identification of single cell or small cell group signals. Meanwhile, the metal electrode is larger in volume in contact environment, more susceptible to electromagnetic interference of external environment and larger in mapping background noise. The glass electrode can be manufactured through hot drawing, so that the detection head end of the minimum um level is realized, but the brittleness of the glass electrode is higher, and the operability is low. The method is generally only used for single mapping, cannot be repeatedly applied, and is generally poor in universality because the method is generally connected through a special patch clamp amplifier.
Disclosure of Invention
In view of the above problems, the present utility model aims to provide a monopolar composite microelectrode which can be used for cardiac activity mapping and which has a detected signal sensitivity satisfying a maximum resolution of 50um 2 The minimum identifiable signal voltage amplitude is 50uV, the electromagnetic interference resistance is high, the electrode structure can be used in a conventional shielding network environment, the operability of the electrode structure is high, and repeated mapping can be realized.
In order to achieve the above purpose, the technical scheme adopted by the utility model is as follows:
the utility model provides a monopole composite microelectrode, includes the electrode body, its characterized in that: an outer shielding layer is arranged outside the electrode body, and the front end and the rear end of the electrode body penetrate through the outer shielding layer;
the electrode body comprises a detection electrode inner core and an electrode tail end, the detection electrode inner core comprises a composite metal control electrode and a glass tube covered outside the composite metal control electrode, the front end and the rear end of the composite metal control electrode penetrate through the glass tube, and the rear end of the composite metal control electrode is fixedly connected with the electrode tail end.
Further, the composite metal control electrode comprises a tungsten wire inner core and a gold-plating layer, wherein the gold-plating layer is arranged outside the front end of the tungsten wire inner core.
Furthermore, the front end and the rear end of the glass tube are both of an opening structure, the rear end of the glass tube is fixedly connected with the tungsten filament inner core through a sealing block, and the rear end of the tungsten filament inner core penetrates through the sealing block and then is fixedly connected with the tail end of the electrode.
Further, the front end of the composite metal control electrode penetrates through the glass tube to be less than 30um in length.
Further, the electrode tail end comprises a copper wire, an inner insulating layer is coated outside the copper wire, and the front end and the rear end of the copper wire penetrate through the inner insulating layer.
Further, the rear end of the tungsten wire inner core in the detection electrode inner core is fixedly connected with the front end of the copper wire in the electrode tail end through welding of the tin transition section.
Further, the outer shielding layer sequentially comprises a red copper net layer, an aluminum foil layer and an outer insulating layer from inside to outside, and the front end of the inner core of the detection electrode and the rear end of the tail end of the electrode penetrate through the outer shielding layer.
The beneficial effects of the utility model are as follows: compared with the prior art, the utility model has the advantages that,
1. the utility model discloses a monopole composite microelectrode, wherein a detection electrode inner core in the monopole composite microelectrode uses a tungsten wire inner core and a gold plating layer to form a composite metal control electrode, a silicate drawn glass tube is arranged outside the composite metal control electrode, so that the effect of reducing noise can be achieved, the front end of the composite metal control electrode penetrates through the length of the glass tube to be less than 30 mu m, the diameter of the tungsten wire inner core is 10 mu m, the thickness of the gold plating layer is 0.3 mu m, and on the premise of reducing and mapping a tissue contact section, a high-conductivity material is utilized, signal loss is not increased, the minimum amplitude of signal voltage is identifiable to be 50 mu V, and the single myocardial fine-level extracellular potential mapping can be realized.
2. Compared with the existing metal Shan Jiwei mapping electrode, the monopole composite microelectrode has higher signal sensitivity, and the highest resolution can reach 50um 2 About only 10 conventional cell-range levels. The influence of the surrounding tissue field potential on the target potential can be better reduced.
3. According to the utility model, the rear end of the tungsten wire inner core in the detection electrode inner core is fixedly connected with the front end of the copper wire in the electrode tail end through the tin transition section in a welding way, so that stable connection between the tungsten wire with the diameter of 10um and the copper wire with the diameter of 0.5mm can be realized; the outer shielding layer is arranged outside the electrode body, so that the electrode body can be loaded, the operability of continuous mapping and good electromagnetic interference resistance can be realized, and the background noise of a recorded signal can be less than 50uV; the electrode body is small in size, has higher electrode operability, and can be repeatedly applied and realize high-flux mapping.
4. The monopole composite microelectrode can be used for detecting high-resolution heart tissue electric signal information, and realizes stable monopole recording and recording under program stimulation. The high-resolution characteristics of the electrode can be used for further exploring the characteristics of physiological myocardial conduction, in particular to an anatomical characteristic region with multiple tissue intersections in the atrioventricular junction area, and high-resolution signals are needed. In complex arrhythmia, the method can be used for distinguishing myocardial cell conduction differences in various states of scar related atrial flutter and ventricular tachycardia, and has important value for revealing the mechanism of arrhythmia and improving the electrophysiological operation treatment scheme.
Drawings
FIG. 1 is a schematic diagram of a monopolar composite microelectrode according to the present utility model.
Fig. 2 is an enlarged view of a portion a of fig. 1 according to the present utility model.
Fig. 3 is a schematic view of the structure of an electrode body according to the present utility model.
Fig. 4 is a schematic diagram of the structure of the inner core of the detection electrode in the present utility model.
Fig. 5 is an enlarged view of part B of the structure of fig. 4 in part according to the present utility model.
FIG. 6 is a schematic diagram of the application of the monopolar composite microelectrode according to the present utility model.
FIG. 7 is a graph showing the size comparison between a monopolar composite microelectrode and a pathological section according to an embodiment of the present utility model.
Fig. 8 is a schematic diagram of a cardiac electrical signal obtained by mapping an atrioventricular junction using a monopolar composite microelectrode according to a first embodiment of the present utility model.
Fig. 9 is an intracardiac electrical signal recorded by a monopolar composite microelectrode under electrophysiological programming in a second embodiment of the present utility model.
Wherein: the high-strength copper-clad steel wire comprises a 1-tungsten wire inner core, a 2-gold-plated layer, a 3-glass tube, a 4-sealing block, a 5-copper wire, a 6-inner insulating layer, a 7-tin transition section, an 8-red copper net layer, a 9-aluminum foil layer and a 10-outer insulating layer.
Detailed Description
In order to enable those skilled in the art to better understand the technical solution of the present utility model, the technical solution of the present utility model is further described below with reference to the accompanying drawings and examples.
As shown in fig. 1-5, a monopole composite microelectrode comprises an electrode body and an outer shielding layer arranged outside the electrode body, wherein the electrode body comprises a detection electrode inner core and an electrode tail end, the detection electrode inner core comprises a tungsten wire inner core 1, a gold plating layer 2 is arranged outside the front end of the tungsten wire inner core 1, a composite metal control electrode is formed by the tungsten wire inner core 1 and the gold plating layer 2, a glass tube 3 is arranged outside the composite metal control electrode, the rear end of the glass tube 3 is fixedly connected with the tungsten wire inner core 1 through a sealing block 4, the rear end of the tungsten wire inner core 1 penetrates through the sealing block 4, and the front end of the composite metal control electrode penetrates through the glass tube 3.
Preferably, the diameter of the tungsten filament inner core 1 is 10um, the thickness of the gold plating layer 2 is 0.3um, the glass tube 3 is made of silicate drawn glass tube, the effect of reducing noise can be achieved, the outer diameter of the front end of the glass tube is 15um, the inner diameter of the glass tube is larger than the outer diameter of the gold plating layer 2, the outer diameter of the rear end of the glass tube 3 is larger than the outer diameter of the front end, a cylindrical sealing block 4 made of ethyl cyanoacrylate material is arranged at the rear end of the glass tube 3, and the rear end of the gold plating layer 2 penetrates through the sealing block 4 and is fixedly connected with the sealing block 4.
The front end of the composite metal control electrode formed by the tungsten wire inner core 1 and the gold-plating layer 2 penetrates through the length of the glass tube 3 to be less than 30um, namely the exposed height of the end of the marking head of the composite metal control electrode is less than 30um.
The electrode tail end comprises a copper wire 5, an inner insulating layer 6 is coated outside the copper wire 5, the front end and the rear end of the copper wire 5 penetrate through the inner insulating layer 6, and the copper wire 5 is a low-resistance plastic copper wire with the diameter of 0.5mm.
The rear end of the tungsten wire inner core 1 in the detection electrode inner core is fixedly connected with the front end of the copper wire 5 in the electrode tail end through the tin transition section 7 in a welding mode, and stable connection between the tungsten wire with the diameter of 10um and the copper wire with the diameter of 0.5mm can be achieved. The detection electrode inner core, the electrode tail end and the tin transition section 7 are fixedly connected to form an electrode body structure.
The outer shielding layer sequentially comprises a red copper net layer 8, an aluminum foil layer 9 and an outer insulating layer 10 from inside to outside, and the front end of the detection electrode inner core and the rear end of the electrode tail end penetrate through the outer shielding layer.
Embodiment one:
example one application of the monopolar composite microelectrode of the present utility model was used to record atrioventricular junction electrical activity. When the monopole composite microelectrode is applied, the monopole composite microelectrode needs to be connected with an electrode coupler, a signal amplifier and a digital-to-analog converter in sequence for use, and a specific application mode diagram is shown in figure 6.
The specific application implementation process is as follows:
1. material
1.1 animals
Adult New Zealand white rabbits
1.2 reagents
Anticoagulant for intraperitoneal injection, heparin (3125U/kg)
10% chloral hydrate for anesthesia of experimental animals
Saturated gas for continuous infusion (95% O) 2 +5％CO 2 )
Improved bench perfusion (119 mM NaCl, 25mM NaHCO) 3 、1.2mM NaH 2 PO 4 、1.0mM MgSO 4 ·6H 2 O、4.0mM KCl、1.8mM CaCl 2 、10mM D-GlucoseH 2 O)
1.3 apparatus
PC-100 glass electrode drawing instrument; 2A-M1800 amplifiers; digidata 1440B digital to analog converter;
2. method of
2.1 improved Langendorff ex vivo cardiac perfusion
Heparin anticoagulation (3125U/kg) was injected into the abdominal cavity of rabbits, and after 15 minutes, the experimental animals were anesthetized with 10% chloral hydrate, hearts were removed after thoracotomy, and placed in saturated gas (95% O) 2 +5％CO 2 ) Improved bench buffer (119 mM NaCl, 25mM NaHCO) 3 、1.2mM NaH 2 PO 4 、1.0mM MgSO 4 ·6H 2 O、4.0mM KCl、1.8mM CaCl 2 、10mM D-GlucoseH 2 O) connective tissue and lung tissue were removed rapidly, leaving the 3-5mm aorta, cannulating the aorta and connecting to Langendorff perfusion system, and perfusing the Table fluid retrograde to the aorta at a pumping rate of 8-10 mL/min. Constant temperature and continuous oxygen supply (95% O) of the perfusion liquid at 35+/-1 ℃ in the whole process 2 +5％CO 2 )。
2.2 manufacturing of monopolar composite microelectrode System
The manufacturing process of the monopolar composite microelectrode system is prepared by adopting the preparation method of the embodiment.
2.3 intra-atrial and ventricular interfacial tissue area within-region electrophysiology mapping
After the isolated heart was fixed to the Langendorff perfusion device, the right atrium was cut to expose the atrioventricular junction, and a reference electrode (HIS electrode, high right atrium electrode, tudaro tendon lateral electrode), stimulation electrode (atrial stimulation electrode, ventricular stimulation electrode) was placed. And a dual-channel Axiopatch 200B patch clamp amplifier or an AM1800 multichannel amplifier is connected, and a Digidata 1440B digital-to-analog converter is used for outputting an analog signal. And mapping the target continuously by applying the micro-control mapping ultra-microelectrode. Up to 3 microelectrodes may be placed on the region of interest. All channel field potentials were monitored in real time using the clamtex 10 sampling software.
3. Results
(1) Fig. 7 shows pathological sections of the atrioventricular junction area compared to the size of the mapping electrodes, and the spacing between the tips of the monopolar electrodes is about 3-5 cells in size.
(3) FIG. 8 shows mapping of atrioventricular junction using an ultra-microelectrode.
Record under application of Clampex software. The electrodes clearly record atrial, his, and ventricular potentials showing sinus rhythm. The baseline noise was less than 50uv.
Embodiment two:
the second embodiment is to record the intracardiac electrical signal by applying the unipolar composite microelectrode in the utility model under the electrophysiological program control, and the specific implementation process is as follows:
1. material
1.1 animals
Adult New Zealand white rabbits
1.2 reagents
Anticoagulant for intraperitoneal injection, heparin (3125U/kg)
10% chloral hydrate for anesthesia of experimental animals
Saturated gas for continuous infusion (95% O) 2 +5％CO 2 )
Improved bench perfusion (119 mM NaCl, 25mM NaHCO) 3 、1.2mM NaH 2 PO 4 、1.0mM MgSO 4 ·6H 2 O、4.0mM KCl、1.8mM CaCl 2 、10mM D-GlucoseH 2 O)
1.3 apparatus
PC-100 glass electrode drawing instrument; 2A-M1800 amplifiers; digidata 1440B digital to analog converter;
2. method of
2.1 improved Langendorff ex vivo cardiac perfusion
Heparin anticoagulation (3125U/kg) for intraperitoneal injection of mice, 15 minutesAfter the bell, the experimental animals were anesthetized with 10% chloral hydrate, the hearts were removed after chest opening and placed in saturated gas (95% o) 2 +5％CO 2 ) Improved bench buffer (119 mM NaCl, 25mM NaHCO) 3 、1.2mMNaH 2 PO 4 、1.0mM MgSO 4 ·6H 2 O、4.0mM KCl、1.8mM CaCl 2 、10mM D-GlucoseH 2 O) connective tissue and lung tissue were removed rapidly, leaving the 3-5mm aorta, cannulating the aorta and connecting to Langendorff perfusion system, and perfusing the Table fluid retrograde to the aorta at a pumping rate of 8-10 mL/min. Constant temperature and continuous oxygen supply (95% O) of the perfusion liquid at 35+/-1 ℃ in the whole process 2 +5％CO 2 )。
2.2 electrophysiological procedure stimulation subscript
After the isolated heart is fixed to the Langendorff perfusion device, the reference electrode and the mapping electrode, the stimulation electrode (atrial stimulation electrode, ventricular stimulation electrode) are placed. And a dual-channel Axiopatch 200B patch clamp amplifier or an AM1800 multichannel amplifier is connected, and a Digidata 1440B digital-to-analog converter is used for outputting an analog signal. And mapping the target continuously by applying the micro-control mapping ultra-microelectrode. All channel field potentials were monitored in real time using the clamtex 10 sampling software.
3 results
FIG. 9 shows the mapping of cardiac electrical activity using an ultra-microelectrode under procedural stimulation.
Record under application of Clampex software. The upper graph shows that the electrodes can clearly record atrial, his and ventricular potentials under atrial stimulation. The baseline noise was less than 50uv. The lower panel shows that the electrodes can clearly register the retrograde atrial potential under ventricular stimulation. The baseline noise was less than 50uv.
The foregoing has shown and described the basic principles, principal features and advantages of the utility model. It will be understood by those skilled in the art that the present utility model is not limited to the embodiments described above, and that the above embodiments and descriptions are merely illustrative of the principles of the present utility model, and various changes and modifications may be made without departing from the spirit and scope of the utility model, which is defined in the appended claims. The scope of the utility model is defined by the appended claims and equivalents thereof.
Claims (7)
1. The utility model provides a monopole composite microelectrode, includes the electrode body, its characterized in that: an outer shielding layer is arranged outside the electrode body, and the front end and the rear end of the electrode body penetrate through the outer shielding layer;
the electrode body comprises a detection electrode inner core and an electrode tail end, the detection electrode inner core comprises a composite metal control electrode and a glass tube (3) covered outside the composite metal control electrode, the front end and the rear end of the composite metal control electrode penetrate through the glass tube (3), and the rear end of the composite metal control electrode is fixedly connected with the electrode tail end.
2. The monopolar composite microelectrode according to claim 1, wherein: the composite metal control electrode comprises a tungsten wire inner core (1) and a gold-plating layer (2), wherein the gold-plating layer (2) is arranged outside the front end of the tungsten wire inner core (1).
3. A monopolar composite microelectrode according to claim 2 and characterized in that: the front end and the rear end of the glass tube (3) are of an opening structure, the rear end of the glass tube (3) is fixedly connected with the tungsten filament inner core (1) through the sealing block (4), and the rear end of the tungsten filament inner core (1) penetrates through the sealing block (4) and then is fixedly connected with the tail end of the electrode.
4. A monopolar composite microelectrode according to claim 3 and wherein: the front end of the composite metal control electrode penetrates through the glass tube (3) to be less than 30um in length.
5. A monopolar composite microelectrode according to claim 3 and wherein: the electrode tail end comprises a copper wire (5), an inner insulating layer (6) is coated outside the copper wire (5), and the front end and the rear end of the copper wire (5) penetrate through the inner insulating layer (6).
6. The monopolar composite microelectrode according to claim 5, wherein: the rear end of the tungsten wire inner core (1) in the detection electrode inner core is fixedly connected with the front end of the copper wire (5) in the electrode tail end through a tin transition section (7) in a welding mode.
7. The monopolar composite microelectrode according to claim 6, wherein the outer shielding layer comprises a red copper mesh layer (8), an aluminum foil layer (9) and an outer insulating layer (10) from inside to outside in sequence, and the front end of the inner core of the detection electrode and the rear end of the tail end of the electrode penetrate through the outer shielding layer.
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| CN202320646023.4U CN219962889U (en) | 2023-03-29 | 2023-03-29 | Single-pole composite microelectrode |
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| CN202320646023.4U CN219962889U (en) | 2023-03-29 | 2023-03-29 | Single-pole composite microelectrode |
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