CN113100774A - Intracranial electrode integrated with macro microelectrode - Google Patents
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- CN113100774A CN113100774A CN202110378970.5A CN202110378970A CN113100774A CN 113100774 A CN113100774 A CN 113100774A CN 202110378970 A CN202110378970 A CN 202110378970A CN 113100774 A CN113100774 A CN 113100774A
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Abstract
The application provides an intracranial electrode integrated with a macro microelectrode. The intracranial electrode integrated with the macro microelectrode comprises a sleeve (3), wherein a lead (4) is arranged inside the sleeve (3), and the macro electrode (1) and the microelectrode (2) are integrated on the side wall of the sleeve (3). The macro electrode (1) and the microelectrode (2) respectively transmit signals received by the macro electrode (1) and the microelectrode (2) to the outside through the lead (4). In the axial direction of the sleeve (3), the macro-electrode (1) and the micro-electrode (2) are arranged on the side wall of the sleeve (3) in a spaced manner and insulated from each other.
Description
Technical Field
The application relates to the technical field of stereotactic electroencephalogram, in particular to an intracranial electrode integrated with a macro microelectrode.
Background
Stereotactic electroencephalography (SEEG) is also known as stereotactic three-dimensional electroencephalography. The technology introduces the electroencephalogram technology from 2D to a 3D layer by a positioning method, and the electrodes are implanted by adopting a stereotactic method based on clinical symptoms, namely cortical discharge and neurodissection. The method uses electrodes to carry out three-dimensional coverage on the brain, thereby achieving the purposes of accurately positioning the focus and improving the treatment effect.
Patients with epilepsy which is difficult to treat by the medicine need to achieve the purpose of radical treatment through operations. Preoperative assessment is an important factor affecting the efficacy of surgery. The existing noninvasive detection method cannot accurately determine the position of the epileptogenic focus. The stereotactic electroencephalogram technology applies an intracranial electrode monitoring method, and can better perform high-resolution direct monitoring on the neural activity of the brain. Meanwhile, the method can eliminate the interference of scalp and skull by implanting the electrode into the bottom of the sulcus or deep part of the brain, thereby obtaining higher-quality electroencephalogram data. The stereotactic electroencephalogram technology can be used for directly placing electrodes to intracranial target parts, such as parts which cannot be reached by conventional cortical electrodes, such as the deep part of the frontal lobe, the inner side of the brain, the cingulate gyrus, the inner side of the temporal lobe and the like. The technology combines nuclear magnetic resonance, CTA or angiography and other imaging technologies, avoids intracranial arteries and veins by designing an electrode implantation path before an operation, and avoids brain injury to the maximum extent by a minimally invasive method.
The intracranial deep electrode is the most valuable auxiliary diagnosis and treatment means in the preoperative evaluation process of refractory epilepsy surgery. The intracranial deep electrode can be used for recording the action field potential of the brain tissue discharge initiation region of an epileptic, can help to determine a functional abnormal region and an irritable region, and can be used for judging the intensity and range of suspected epileptogenic cortex abnormal discharge.
Because the intracranial deep electrode is directly contacted with the cerebral cortex, the acquired electric signal can directly reflect the real electrophysiological activity of the implanted cerebral area. Therefore, the stereotactic electroencephalogram recording method can realize good monitoring of the electrophysiological activity of the cortical nerves from a three-dimensional space and has high regional accuracy. These properties make it irreplaceable in the location of clinical pathogenic foci or in basic research in brain science.
The surface area of the conventional intracranial deep electrode is usually 1-10 mm2The macro-electrodes in the field are usually of cylindrical design. What is recorded by the macro-electrodes is the Local Field Potential (LFP) at the location of the electrodes. The local field potential is about 100mm near the electrode surface3Linear summation of postsynaptic potentials of all neurons (in the order of millions) within a volume of brain tissue. Local field potential signals are acquired by using a macro electrode, and the signal to noise ratio is higher in a frequency band within 300Hz generally.
Various modes of field potential rhythm oscillations (rhytmic oscillations) exist in the brain. These periodic oscillation signals with different frequency ranges provide a time synchronization for the encoding, storage and extraction of neural information by the group neurons in the brain, and also reflect different activity patterns of the brain neural network information processing.
In clinical practice, medical practitioners record the local field potential at a particular location within the cranium of an epileptic using a deep intracranial electrode having multiple macro electrodes. Epileptiform abnormal discharges occurring during the epileptic seizure and between seizures in patients are of great concern and resolution, including spike wave (spike wave), sharp wave (sharp wave), spike-and-slow-wave complex (spike-and-slow-wave complex), and spike-slow-wave complex (sharp-and-slow-wave complex). By analyzing the generation of the epileptiform abnormal discharge and the propagation and diffusion rule in the brain, medical workers can identify the structure of an epileptic network in the brain of an epileptic patient, further determine the position and range of an epileptogenic focus and provide support for further destructive surgery.
The existing intracranial stereotactic electroencephalogram diagnosis and treatment method depends on the analysis of intracranial abnormal discharge of a patient in the epileptic seizure period. Therefore, in clinical practice, 3-5 natural attacks corresponding to the usual attacks are often recorded to provide enough data for medical workers to confirm the position and range of the epileptogenic focus. After the electrode is implanted into the intracranial deep electrode, an epileptic patient must be subjected to long-time intracranial electroencephalogram monitoring so as to capture a sufficient number of epileptic seizure events, thus the occupation of medical resources is increased, and the risk of infection and other complications is also increased. Even some epileptic patients do not have seizures throughout the course of electroencephalogram monitoring, resulting in a failure of the diagnosis.
The fundamental reason for this is that the existing intracranial deep electrodes can only collect local field potential signals at specific locations in the cranium, and medical workers can only diagnose and analyze the signals according to the limited information provided by the local field potential.
Disclosure of Invention
In order to improve or solve the problems mentioned in the prior art, the present application provides an intracranial electrode integrated with a macro microelectrode.
The intracranial electrode integrated with the macro microelectrode comprises a sleeve, wherein a lead is arranged inside the sleeve,
the side wall of the sleeve is integrated with a macro electrode and a microelectrode, the macro electrode and the microelectrode respectively transmit signals received by the macro electrode and the microelectrode to the outside through the lead,
in the axial direction of the sleeve, the macro-electrode and the micro-electrode are arranged on the side wall of the sleeve in a spaced manner and insulated from each other.
In at least one embodiment, the shortest distance between adjacent macroelectrodes and microelectrodes in the axial direction of the cannula is between 0.5 mm and 2 mm.
In at least one embodiment, the macro microelectrode integrated intracranial electrode comprises a plurality of the macro electrodes and a plurality of the microelectrodes,
the macro-electrodes and the micro-electrodes are alternately arranged at intervals in the axial direction of the cannula.
In at least one embodiment, the macro microelectrode integrated intracranial electrode comprises a plurality of the macro electrodes and a plurality of the microelectrodes,
in the axial direction of the sleeve, the macro electrodes and the micro electrodes are arranged at equal intervals.
In at least one embodiment, the macro microelectrode integrated intracranial electrode comprises a plurality of the macro electrodes and a plurality of the microelectrodes,
in the axial direction of the sleeve, the macro electrodes and the micro electrodes are alternately arranged at equal intervals.
In at least one embodiment, the macro-electrode has a surface area between 1 and 10 square millimeters,
the surface area of the microelectrode is less than 4000 square microns.
In at least one embodiment, the macro-electrode serves as a stimulation electrode and/or a detection electrode and the micro-electrode serves as a detection electrode.
In at least one embodiment, the macro electrode is a ring-shaped electrode, the macro electrode is sleeved on the outer wall of the sleeve,
the microelectrode is a spherical electrode and is fixed on the outer wall of the sleeve.
In at least one embodiment, the sleeve has a plurality of through holes, the wires include a first type of wire and a second type of wire,
one end of the wire of the same type is connected to the macro electrode through the through hole,
one end of the second type wire is fused into a sphere, the spherical tail end of the second type wire is the microelectrode, and the diameter of the microelectrode is larger than that of the through hole.
In at least one embodiment, the one type of lead is connected to the inside of the ring of the macro-electrode.
According to the method, the macroelectrode and the microelectrode are simultaneously integrated on the sleeve, so that medical workers can simultaneously obtain a traditional epileptiform abnormal discharge signal and a high-quality high-frequency oscillation signal in a specific area. Is expected to remarkably shorten the electroencephalogram monitoring time of epileptics and improve the accuracy of focus positioning.
Drawings
FIG. 1 shows a schematic structural diagram of an intracranial electrode integrated with a macro-microelectrode according to an embodiment of the present application.
FIG. 2 shows a schematic structural view of a cannula of an intracranial electrode integrated with a macro-microelectrode according to an embodiment of the present application.
FIG. 3 shows a schematic diagram of a wire bond on a macro-electrode of an intracranial electrode integrated with a macro-microelectrode according to an embodiment of the present application.
Fig. 4 and 5 show schematic diagrams of the installation of a single macro-electrode of an intracranial electrode integrated with a macro-microelectrode on the outer wall of a cannula according to an embodiment of the application.
FIG. 6 shows a schematic structural view of a single microelectrode of an intracranial electrode integrated with a macro-microelectrode according to an embodiment of the present application.
Fig. 7 and 8 show schematic diagrams of the installation of a single microelectrode of an intracranial electrode integrated with a macro microelectrode on the outer wall of a cannula according to an embodiment of the application.
FIG. 9 shows a schematic structural diagram of a macro-microelectrode integrated intracranial electrode on a cannula with a plurality of macro-electrodes and microelectrodes integrated thereon according to an embodiment of the present application.
Fig. 10 and 11 show the packaged structure of fig. 9.
Description of the reference numerals
1 a macro electrode; 2 microelectrodes; 3, sleeving a sleeve; 31 a through hole; 4, conducting wires; 41 a wire insulation sheath; 42 a conductive line metal layer; class 43 conductive lines; a class 44 conducting wire; 5 connecting a plug; 6, a binder; 7 end macro-electrodes.
Detailed Description
Exemplary embodiments of the present application are described below with reference to the accompanying drawings. It should be understood that the detailed description is only intended to teach one skilled in the art how to practice the present application, and is not intended to be exhaustive or to limit the scope of the application.
High Frequency Oscillations (HFOs) are brain electrical activity with frequencies above 80 Hz. The high-frequency oscillation is closely related to an epileptic initiation region, and the high-frequency oscillation is a reliable biomarker for epileptic initiation and epileptogenesis. Meanwhile, the high-frequency oscillation can reflect the severity of the epilepsy, and can help to evaluate the curative effect of epilepsy treatment, judge the susceptibility of the epilepsy and predict the epileptic seizure.
The high-frequency oscillation may be classified into physiological high-frequency oscillation and pathological high-frequency oscillation. The present studies indicate that pathological oscillations occur in the epileptogenic zone (seizure onset zone) or first-propagation zone (first-propagation zone) of epilepsy. On the basis, a clinician can judge whether the brain area is positioned in an epileptogenic area or a first propagation area of the epilepsy by analyzing whether pathological high-frequency oscillation can be acquired at the position of the specific brain area. Meanwhile, pathological high-frequency oscillation occurs in the seizure period and the intermission period of epilepsy, and is not dependent on the generation of epileptic seizure events. Therefore, the comprehensive analysis of epileptiform abnormal discharge in the seizure stage and pathological high-frequency wavelets is expected to remarkably shorten the electroencephalogram monitoring time of epileptics and improve the positioning accuracy.
The key to implementing this technique is the efficient acquisition of high frequency oscillations and the accurate discrimination between physiological and pathological high frequency wavelets. The high-frequency oscillation belongs to a transient local field potential signal, and both the macro electrode and the microelectrode can acquire the high-frequency oscillation signal. Generally, the pathological high-frequency oscillations are located in a higher frequency band than the physiological high-frequency oscillations. However, many studies have shown that both physiological and pathological high frequency wavelets have a large overlap in both area and frequency. In local field potential signals collected by the macro electrode, the difficulty of distinguishing physiological and pathological high-frequency wavelets is high.
The surface area of the contact point of the microelectrode is smaller, so that the number of neurons capable of receiving the electrical activity of the neurons is smaller compared with that of the macro electrode, and relatively more information of high frequency bands can be reserved in local field potentials acquired by the microelectrode. In the signals collected by the microelectrode, physiological high-frequency oscillation has a specific regional and lamellar distribution mode, and the shape and other characteristic differences between the physiological high-frequency oscillation and the pathological high-frequency oscillation are more obvious, so that the microelectrode is favorable for better distinguishing the physiological high-frequency oscillation from the pathological high-frequency oscillation.
Therefore, by arranging the macro electrode and the microelectrode in the vicinity of the intracranial deep electrode at the same time, medical workers can obtain the traditional epileptiform abnormal discharge signal and the high-frequency oscillation signal with higher quality in a specific position area at the same time, and the electroencephalogram monitoring time of epileptics is hopefully shortened and the positioning accuracy is improved by matching with a corresponding analysis method.
Based on the above principle, the present application proposes an intracranial electrode integrated with a macro microelectrode. As shown in figure 1, the intracranial electrode integrated with the macro microelectrode comprises a macro electrode 1, a microelectrode 2, a sleeve 3, a lead 4 and a connecting plug 5. In the present application, the surface area of the macro-electrode 1 may be between 1mm and 10mm, and the surface area of the micro-electrode 2 may be less than 4000 μm. It should be understood that macroelectrodes and microelectrodes are not strictly limited in the industry. Generally, electrodes with a particularly small working area, or electrodes with at least one dimension on the order of micrometers (less than 100 micrometers), are microelectrodes. The application does not limit the specific size of the macro microelectrode.
Wherein, the lateral wall of the sleeve 3 is integrated with the macro-electrode 1 and the microelectrode 2, and the macro-electrode 1 and the microelectrode 2 have a distance to prevent the macro-microelectrode from contacting with each other, thereby preventing the macro-microelectrode from generating mutual influence. Further, the shortest distance between the macro-electrode 1 and the micro-electrode 2 in the axial direction of the cannula 3 may be between 0.5 and 2 mm. Preferably, the shortest distance is between 0.5 and 1 mm.
In the present application, the macro microelectrodes are closer to each other, and the adjacent macro-electrodes 1 and microelectrodes 2 can be considered to be approximately at the same position in a clinical scene. The macro microelectrode exists at the same position, so that doctors can simultaneously obtain low-frequency electroencephalogram signals which are acquired by the macro electrode contact and relatively high-frequency electroencephalogram signals which are acquired by the microelectrode contact. Can be used for better contrast analysis and distinguishing pathological from non-pathological high-frequency wavelets.
The combination of the two signals provides the physician with more information and fosters new clinical diagnostic logic than with conventional electrodes in which only macro electrode contacts are present at the same location. For example, a combination of high frequency wavelets and conventional epileptic waves.
Furthermore, a part of the area can be hollowed out on the whole macro electrode, and a microelectrode can be placed. The macro microelectrodes are not in contact with each other (e.g., an insulating material or member is disposed between the macro microelectrodes and the microelectrodes), and the distances are very close to each other while avoiding mutual influence. Alternatively, as shown in fig. 1, the macro microelectrodes are disposed at intervals in the axial direction of the cannula 3. The embodiment mode that the sleeve is arranged at intervals in the axial direction does not damage the integrity of the macro electrode, avoids adding complex and sharp boundaries and gaps on the surface of the macro electrode, and avoids some negative effects possibly existing in the acquisition of electroencephalogram signals of the macro electrode.
It is understood that the specific arrangement and combination of the macroelectrodes 1 and microelectrodes 2 in the cannula 3 is not limited in this application. In one embodiment of the present application, as shown in fig. 1, macro-electrodes 1 and micro-electrodes 2 are alternately arranged at intervals. Preferably, the macroelectrodes 1 and the microelectrodes 2 are alternately arranged at equal intervals in the axial direction of the bushing 3.
For medical workers, the arrangement mode that macro microelectrodes are alternately arranged at equal intervals is adopted, the electrodes can be simply and clearly used as scales, the implantation depth of the electrodes can be easily judged under the condition of not needing complex calculation or table lookup, and the method has important significance in clinical operation. Meanwhile, in a Magnetic Resonance (MRI) image, the electrodes arranged at equal intervals can also be used as scales, so that medical workers can relatively conveniently judge the positions of the electrodes in the image and the like.
Of course, it is also possible to arrange a plurality of macro-electrodes 1 at equal intervals, arrange a plurality of micro-electrodes 2 at equal intervals, and arrange a micro-electrode 2 at unequal distances from two adjacent macro-electrodes 1, that is, one micro-electrode 2 and one macro-electrode 1 (especially, the macro-electrode 1 closest to the micro-electrode 2) form one macro-micro-electrode (or macro-micro-electrode group).
In addition, it will be appreciated that a plurality of microelectrodes may be associated with a macro-electrode, such that the plurality of microelectrodes and the macro-electrode form a macro-microelectrode (or macro-microelectrode group).
In the present application, the macro-electrode 1 can be used as a stimulation electrode and a detection electrode, and the micro-electrode 2 can be used as a detection electrode. The macro microelectrode design has the advantage that high-quality low-frequency electroencephalogram signals (characteristic of macro electrodes) and high-quality high-frequency electroencephalogram signals (characteristic of microelectrodes) can be received at a specific position in the brain at the same time. In addition, the macro electrode contact has a large current which can be loaded, and can be used for stimulating the nerve nuclei at specific positions in the brain. Therefore, the electrical stimulation is performed by using the macro electrode, and after the electrical stimulation is stopped for a certain period of time (e.g., several tens to several hundreds of milliseconds), the electrical activity of the neuron is collected by using the macro electrode 1 and the micro-electrode 2. The application paradigm can be used as a tool for some brain science research.
The various nerve cells and intercellular fluid in the brain form a volume conductor in which transmembrane potential changes caused by action potentials of individual neuronal cells propagate, with the potential decaying with increasing distance. Theoretical analysis shows that one microelectrode can record action potential signals of 60-100 neurons in a region of about 50 μm around the microelectrode. The surface area of the microelectrode contact is small, so that the range of the neuron activity potential which can be recorded by the microelectrode contact is limited, and action potential signals of 60-100 neuron activities in the region have high signal-to-noise ratio. The method has very important significance for recording and analyzing neuron action potential (Spike), researching electrophysiological mechanisms of epilepsy, expanding intracranial deep electrodes to application fields such as brain-computer interfaces and the like.
In one embodiment, the inside of the casing 3 is provided with a lead 4, and the macro-electrode 1 and the micro-electrode 2 transmit signals received by the macro-electrode 1 and the micro-electrode 2 to the outside through the lead 4.
The application also provides a manufacturing method of the intracerebral electrode integrated with the macro microelectrode. For convenience of description, the present application classifies the lead wires 4 into one type of lead wires 43 connecting the macro-electrodes 1 and two types of lead wires 44 connecting the micro-electrodes 2. The wire 4 may be an enameled wire.
The manufacturing method of the intracranial electrode integrated with the macro microelectrode comprises the following steps:
as shown in fig. 2, a plurality of through holes 31 are formed in the sleeve 3. Further, the sleeve 3 may be a polymer tube such as a thermoplastic polyurethane elastomer rubber (TPU) tube, a silicon material tube, a polyvinyl chloride (PVC) tube, a Polyimide (PI) tube, or the like. The reference diameter of the sleeve 31 may be 0.8 to 1.3 mm. The reference diameter of the through hole 31 may be 30 to 50 μm.
As shown in fig. 3, one end of one type of wire 43 is connected to the macro electrode 1. In one embodiment, the macro electrode 1 may be a ring-shaped electrode, and the macro electrode 1 is sleeved on the outer wall of the sleeve 3. One end of the one-type wire 43 may be connected to the inner surface of the annular macro-electrode 1, and one end of the one-type wire 43 may be welded to the inner surface of the annular macro-electrode 1 by, for example, laser welding. The outer surface of the macro electrode 1 is directly contacted with brain tissue for collecting brain electrical signals.
This embodiment avoids sharp protrusions of the outer surface due to the welding spots when welding to the outer surface. The outer surface of the macro electrode 1 is kept smooth and flat, and the acquisition quality of the electroencephalogram signals is guaranteed to the greatest extent. It will be appreciated that the welding of a type of wire 43 to the inner surface of the macro-electrode 1 is a preferred embodiment of the present application and the present application is not limited to a particular welding location of the wire to the electrode.
As shown in fig. 4 and 5, one end of the wire 43 of the same type, which is not connected to the macro-electrode 1, passes through the through-hole 31, and the macro-electrode 1 connected to the wire 43 of the same type is fixed at the position of the through-hole 31 by tensioning the wire 43 of the same type.
As shown in FIG. 6, one end of the second-type wire 44 may be fused into a ball shape to constitute the micro-electrode 2. For example, the lead insulating sheath 41 is burned off to expose the lead metal layer 42, and the end portion is melted into a spherical shape to form a base of the micro-electrode 2. For convenience of description, the present application directly refers to the globular tip as the microelectrode 2.
Furthermore, a nano-coating (such as hydrogel, iridium oxide and platinum oxide coatings) can be formed on the spherical surface of the end of the enameled wire by an electrochemical method, so that the surface impedance of the microelectrode 2 is reduced. The diameter of the spherical micro-electrode 2 may be larger than that of the through-hole 31.
As shown in FIGS. 7 and 8, the end of the second type wire 44 not connected to the micro-electrode 2 is passed through the through-hole 31, and the micro-electrode 2 connected to the second type wire 44 is fixed to the outside of the through-hole 31 by tensioning the second type wire 44. (it will be understood that the microelectrodes 2 and the macroelectrodes 1 are fixed in different positions).
The above steps are repeated to obtain the electrode arrangement shown in fig. 9. It is to be understood that the present application is not limited to the combined arrangement of the electrodes. For example, the macroelectrodes 1 and microelectrodes 2 may be spaced apart in the axial direction of the cannula 3. The macro-microelectrodes are spaced at equal distances by making the distances between the respective through holes 31 equal in the axial direction of the cannula 3.
As shown in FIG. 10, after the macro-electrode 1 and micro-electrode 2 are disposed, an adhesive may be injected into the bushing 3, for example, to fill the position including the through-hole 31, and further fix the lead wire 4.
As shown in fig. 11, a hemispherical end macro-electrode 7 or a polymer material (e.g., rubber) may be provided at the end of the cannula 3 that protrudes into the cranium, thereby completing the encapsulation of the intracranial electrode into which the macro-microelectrode is integrated.
The non-intracranial-extending end of the sleeve 3 can be provided with a connecting plug 5, the connecting plug 5 is provided with pins, one ends of the non-connecting macro electrode 1 and the microelectrode 2 of the lead 4 can be connected with the pins of the connecting plug 5 one by one, and signals detected by the intracranial electrode integrated with the macro microelectrode are transmitted to external equipment through the connecting plug 5. Finally, the manufacture of the intracranial electrode integrated with the macro microelectrode shown in the figure 1 is realized.
It will be appreciated that the most basic function of an intracranial electrode is to detect and record signals, possibly with some degree of stimulation. All applications of the intracranial electrodes integrated with the macro microelectrode, such as epilepsy detection, treatment, brain-computer interface and the like, are all within the protection scope of the present application.
While the foregoing is directed to the preferred embodiment of the present application, it will be understood by those skilled in the art that various changes and modifications may be made without departing from the spirit and scope of the application.
Claims (10)
1. An intracranial electrode integrated with a macro microelectrode, which is characterized in that,
the intracranial electrode integrated with the macro microelectrode comprises a sleeve (3), a lead (4) is arranged inside the sleeve (3),
the side wall of the sleeve (3) is integrated with a macro electrode (1) and a microelectrode (2), the macro electrode (1) and the microelectrode (2) respectively transmit signals received by the macro electrode (1) and the microelectrode (2) to the outside through the lead (4),
in the axial direction of the sleeve (3), the macro-electrode (1) and the micro-electrode (2) are arranged on the side wall of the sleeve (3) in a spaced manner and insulated from each other.
2. The macro microelectrode integrated intracranial electrode as recited in claim 1,
the shortest distance between the adjacent macro-electrodes (1) and the micro-electrodes (2) in the axial direction of the cannula (3) is between 0.5 mm and 2 mm.
3. The macro microelectrode integrated intracranial electrode as recited in claim 1,
the macro microelectrode integrated intracranial electrode comprises a plurality of macro electrodes (1) and a plurality of microelectrodes (2),
in the axial direction of the casing (3), the macroelectrodes (1) and the microelectrodes (2) are alternately arranged at intervals.
4. The macro microelectrode integrated intracranial electrode as recited in claim 1,
the macro microelectrode integrated intracranial electrode comprises a plurality of macro electrodes (1) and a plurality of microelectrodes (2),
in the axial direction of the sleeve (3), the macro electrodes (1) and the micro electrodes (2) are arranged at equal intervals.
5. The macro microelectrode integrated intracranial electrode as recited in claim 1,
the macro microelectrode integrated intracranial electrode comprises a plurality of macro electrodes (1) and a plurality of microelectrodes (2),
in the axial direction of the sleeve (3), the macro electrodes (1) and the micro electrodes (2) are alternately arranged at equal intervals.
6. The macro microelectrode integrated intracranial electrode as recited in claim 1,
the surface area of the macro-electrode (1) is between 1 and 10 square millimetres,
the surface area of the microelectrode (2) is less than 4000 square micrometers.
7. The macro microelectrode integrated intracranial electrode as recited in claim 1,
the macroelectrode (1) serves as a stimulation electrode and/or a detection electrode and the microelectrodes (2) serve as detection electrodes.
8. The macro microelectrode integrated intracranial electrode as recited in claim 1,
the macro electrode (1) is a circular ring-shaped electrode, the macro electrode (1) is sleeved on the outer wall of the sleeve (3),
the microelectrode (2) is a spherical electrode, and the microelectrode (2) is fixed on the outer wall of the sleeve (3).
9. The macro microelectrode integrated intracranial electrode as recited in claim 8,
the sleeve (3) is provided with a plurality of through holes (31), the lead (4) comprises a first type lead (43) and a second type lead (44),
one end of the wire (43) of the same type is connected to the macro electrode (1) through the through hole (31),
one end of the second type wire (44) is fused into a sphere, the spherical tail end of the second type wire (44) is the microelectrode (2), and the diameter of the microelectrode (2) is larger than that of the through hole (31).
10. The macro microelectrode integrated intracranial electrode as recited in claim 9,
the wire (43) of the same type is connected to the inner side of the circular ring of the macro electrode (1).
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| WO2019200046A1 (en) * | 2018-04-11 | 2019-10-17 | Fort Wayne Metals Research Products Corp | A wire for a high density and biostable microelectrode array for neural electrode stimulation and recording |
| CN109431486A (en) * | 2018-12-30 | 2019-03-08 | 北京华科恒生医疗科技有限公司 | The detection method of stereo electrod, the production method of stereo electrod and electrical activity |
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