TWI822447B - Movement monitor sensor - Google Patents

Abstract

The present invention discloses movement monitor sensor for implanting into human brain and connecting with a processor, which includes a body, a conduction area, at least one depth electrode set and one flat electrode set. The body has an axis. The conduction area and the flat electrode set is disposed relatively on both ends of the body along the axis. The depth electrode set has four depth electrodes which are disposed on the body and around the axis and relatively correspond to four directions. The flat electrode set has four flat electrodes which are disposed on substrate and around the axis and relatively correspond to four directions. Current is imported into the conduction area, depth electrodes and flat electrodes. Impedance value changing between depth electrodes, flat electrodes and/or the conduction area could be detected by a processor for electrical stimulation control when the human body is moving.

Description

motion monitoring sensor

The invention relates to the field of medical technology, and in particular, to an action monitoring sensor.

There are many nerve fiber connections between nuclei in brain regions. Take the subthalamic nucleus (STN) as an example. In order to produce smooth movements, the subthalamic nucleus generates electrical signals to activate other nerves. Nuclei, such as the globus pallidus interna (GPi), in turn prompt the putamen to secrete dopamine, and dopamine affects the starting and stopping of movements. If these neural networks fail to activate, clinical symptoms such as stiffness or tremors due to insufficient dopamine secretion will result. These are the typical clinical symptoms of Parkinson's disease.

The main movement disorders seen in people with Parkinson's disease include difficulty initiating movements (such as changing from sitting to standing) and difficulty transitioning movement states (such as turning).

In addition to drugs, one method that is currently commonly used is the implantation of neuromodulation probes. This type of probe is equipped with multiple electrodes, and each electrode is connected to a wire. The current is input into the electrode through the wire, and the electrode activates the neural network by stimulating the subthalamic nucleus or the medial globus pallidus, thereby improving the patient's movement disorder.

However, it has been clinically found that some patients do not respond well to continuous electrical stimulation only when the patient's movements change, for example, at switching points in the gait cycle (e.g., transitioning from sitting to standing or turning, heel strike and Only when the patient is off the ground can electrical stimulation be given to effectively improve walking ability.

Accordingly, how to develop a "motion monitoring sensor" that can sense the patient's movements as a characteristic of the timing of starting electrical stimulation is an issue that people in the relevant technical field urgently need to solve.

In one embodiment, the present invention proposes a motion monitoring sensor, which is disposed in the brain tissue of the human body and is suitable for connection with a processor. The motion monitoring sensor includes: a body with an axis, and the body moves along the axis The core has two opposite axial ends; a conductive area is provided at one of the axial ends of the body, and the conductive area is connected to a conductive wire; at least one depth electrode group, the depth electrode group includes four depth electrodes, and the four depth electrodes Arranged on the surface of the body around the axis, four depth electrodes correspond to four directions respectively, each depth electrode is connected to a first wire; and a planar electrode group includes a base material and four planar electrodes, the base material has an opposite direction The first and second sides, the base material is disposed on the other axial end of the body relative to the conductive area through the second surface, four planar electrodes are disposed on the base material around the axis, and the four planar electrodes respectively correspond to In four directions, each plane electrode is connected to a second wire; the current is introduced into the conductive area, each depth electrode and each plane electrode respectively through the conductive wire, each first wire and each second wire. When the movement of the human body changes, The processor compares the depth electrode set with The amount of impedance change produced by the planar electrode group and/or the conductive area serves as the basis for electrical stimulation control of the human brain tissue.

100,100A: motion monitoring sensor

10:Ontology

20: Conductive area

30A~30D: Depth electrode group

40: Planar electrode group

41:Substrate

411: Side 1

412:Second side

42:hole

43:Microstructure

44: Fixtures

202:Brain tissue

204:Skull

206: First side brain tissue

208:Third side brain tissue

C10: Axis

D1: first position

D2: Second position

D3: Third position

D4: The fourth position

D5: Maximum diameter

DE1: first depth electrode

DE2: Second depth electrode

DE3: The third depth electrode

DE4: The fourth depth electrode

FE1: first plane electrode

FE2: Second plane electrode

FE3: third plane electrode

FE4: The fourth plane electrode

ST: electrical stimulation

W1: first wire

W2: Second wire

W20: Conductive wire

△Z1: First impedance change amount

△Z2: Second impedance change amount

△Z3: The third impedance change amount

△Z4: The fourth impedance change amount

△Z5: The fifth impedance change amount

△Z6: The sixth impedance change amount

Figure 1 is a schematic three-dimensional structural diagram of an embodiment of the present invention.

FIG. 2 is a schematic structural view from below of the embodiment of FIG. 1 .

Figure 3 is a schematic structural diagram of the A-A section in Figure 2.

FIG. 4 is a schematic structural view of the front view of the embodiment of FIG. 1 which is installed on the brain and is provided with a fixing member.

FIG. 5 is a schematic diagram of the electrode operation when the human body moves in parallel according to the embodiment of FIG. 1 .

FIG. 6 is a schematic diagram of electrode operation when the human body moves vertically according to the embodiment of FIG. 1 .

Figure 7 is a schematic diagram of the brain tissue acting on the electrode when the human body is moving according to the present invention.

FIG. 8 is a design example of a counter-synchronous sequential voltage measurement circuit applicable to the present invention.

9A to 11B are examples of multi-channel pairing switching applicable to the present invention.

Figure 12A is a schematic diagram of impedance changes when a human body stands up and moves forward.

Figure 12B is a schematic diagram of impedance changes of human walking.

Figure 13 shows a linear relationship between the amount of impedance change and the amount of displacement caused by brain tissue deformation when the human body moves in the same direction.

Figure 14 shows a linear relationship between the amount of impedance change and the amount of brain tissue compression caused by the brain tissue deformation caused by the human body moving in the same direction.

Figure 15 is a schematic diagram of the three-dimensional structure of another embodiment of the present invention, and a schematic diagram of the electrode action when the human body moves in parallel.

FIG. 16 is a schematic diagram of electrode operation when the human body moves vertically according to the embodiment of FIG. 15 .

The embodiments of the present invention are described in detail below with reference to the accompanying drawings. And the same or similar parts in the illustrations are marked with the same numbers. The dimensional proportions in the drawings are not drawn to the same proportions as the actual product, and therefore are not intended to limit the scope of the present invention.

Referring to the embodiment shown in FIG. 1 , a motion monitoring sensor 100 provided by the present invention is suitable for being installed in the brain tissue of the human body. The motion monitoring sensor 100 is adapted to be connected to a power supply device and a processor (not shown). The processor is adapted to control the power supply device to supply current to the motion monitoring sensor 100 , and can monitor the sensor 100 according to the motion. The generated impedance change controls the current to electrically stimulate the nerve fibers around the motion monitoring sensor 100 . The processor may be of any type, such as a computer device.

Referring to FIGS. 1 to 3 , the motion monitoring sensor 100 includes a body 10 , a conductive area 20 , four depth electrode groups 30A to 30D and a plane electrode group 40 .

The body 10 has an axis C10, and the conductive area 20 and the planar electrode group 40 are respectively disposed at two opposite axial ends of the body 10 along the axis C10.

The conductive area 20 is made of conductive material. The conductive area 20 is connected to a conductive wire W20.

The four depth electrode groups 30A to 30D are arranged on the body 10 parallel to the axis C10 of the body 10 . Each depth electrode group 30A to 30D includes a first depth electrode DE1, a second depth electrode DE2, a third depth electrode DE3, and a fourth depth electrode DE4.

The first depth electrode DE1, the second depth electrode DE2, the third depth electrode DE3, and the fourth depth electrode DE4 are arranged on the surface of the body 10 around the axis C10. The first depth electrode DE1, the second depth electrode DE2, the third depth electrode DE3, and the fourth depth electrode DE4 are respectively connected to a first wire W1.

The first depth electrode DE1, the second depth electrode DE2, the third depth electrode DE3, and the fourth depth electrode DE4 respectively face a first direction D1, a second direction D2, a third direction D3, a fourth direction D4, etc. Four directions.

The first orientation D1, the second orientation D2, the third orientation D3 and the fourth orientation D4 are perpendicular to the axis C10 and extend radially at equal angles with the axis C10 as the center. The first orientation D1 and the third orientation D3 are symmetrical with respect to both sides of the axis C10, and the second orientation D2 and the fourth orientation D4 are symmetrical with respect to the other two sides of the axis C10. The first orientation D1 is located between the second orientation D2 and the fourth orientation D4.

It should be noted that in this embodiment, each depth electrode group 30A to 30D includes four depth electrodes (ie, the first depth electrode DE1 , the second depth electrode DE2 , the third depth electrode DE3 and the fourth depth electrode DE3 ). Taking electrode DE4) as an example, it corresponds to four directions for motion detection or directional electrical stimulation. However, in other embodiments, the number of depth electrodes included in each depth electrode group can also be adjusted according to the needs and selective increase, and is not limited to this.

The planar electrode group 40 includes a flat circular base material 41 and a first planar electrode FE1, a second planar electrode FE2, a third planar electrode FE3 and a fourth planar electrode FE4. The first planar electrode FE1, the second planar electrode FE2, the third planar electrode FE3 and the fourth planar electrode FE4 include facing the first direction D1, the second direction D2, the third direction D3 and the fourth direction D4 respectively.

It should be noted that in this embodiment, although the planar electrode group 40 includes four planar electrodes (namely, the first planar electrode FE1, the second planar electrode FE2, the third planar electrode FE3 and the fourth planar electrode FE4) as an example, , corresponding to four directions for motion detection. However, in other embodiments, the number of planar electrodes included in each planar electrode group 40 can also be adjusted according to the needs and optionally increased, and is not limited to this.

The base material 41 has a hole 42 extending through the base material 41 parallel to the axial direction C10. The material of the base material 41 is not limited, and may be, for example, silicone or thermoplastic polyurethane (TPU).

The shape and size of the base material 41 are not limited. For example, for a circle as shown in the figure, its maximum diameter D5 may be equal to or less than 10 millimeters (mm).

The base material 41 has a first surface 411 and a second surface 412 opposite to each other. The second surface 412 of the base material 41 is provided with microstructures 43 . The height of the microstructure 43 protruding from the base material 41 is not limited, and may be equal to or greater than 50 micrometers (μm), for example.

The first planar electrode FE1, the second planar electrode FE2, the third planar electrode FE3, and the fourth planar electrode FE4 are arranged on the base material 41 surrounding the hole 42.

The first planar electrode FE1, the second planar electrode FE2, the third planar electrode FE3, and the fourth planar electrode FE4 respectively correspond to the first orientation D1, the second orientation D2, the third orientation D3, and the fourth orientation D4. The first planar electrode FE1, the second planar electrode FE2, the third planar electrode FE3, and the fourth planar electrode FE4 are respectively connected to a second wire W2.

The base material 41 is disposed at an axial end of the body 10 relative to the conductive area 20 via the second surface 412 , and the hole 42 is correspondingly disposed at the axis C10 of the body 10 . Specifically, from the perspective of looking up, the center of the hole 42 coincides with the axis C10, so that the first planar electrode FE1 and the second planar electrode FE1 The two planar electrodes FE2, the third planar electrode FE3, and the fourth planar electrode FE4 are arranged on the base material 41 around the axis C10.

Each first wire W1 , each second wire W2 and the conductive wire W20 are respectively penetrated from the body 10 and the base material 41 through the hole 42 .

It must be noted that FIG. 1 and FIG. 3 only show that the first depth electrode DE1 , the second depth electrode DE2 , the third depth electrode DE3 , and the fourth depth electrode DE4 of one depth electrode group 30A are connected to the first wire W1 . However, , other depth electrode groups 30B~30D are also connected to the first wire W1, but are omitted in the figure.

Please refer to FIG. 4 to illustrate the setting method of the motion monitoring sensor 100 . The main body 10 is disposed in the brain tissue 202 of the human body. The second surface 412 of the base material 41 of the planar electrode group 40 is close to the brain tissue 202. The microstructure 43 disposed on the second surface 412 can provide a connection between the base material 41 and the brain tissue 202. The meningeal contact uses the adhesive properties to produce a fixation effect.

The first surface 411 of the base material 41 is provided with a fixing member 44. The fixing member 44 is suitable for being placed on the skull 204 of the human body, and the brain tissue 202 is located in the skull 204. The fixing member 44 is arranged on the skull 204 of the human body to seal the body 10 , the conductive area 20 , the depth electrode groups 30A to 30D and the plane electrode group 40 within the skull 204 . The fixing member 44 is made of rigid material, such as plastic. The fixing member 44 has a channel 441 for providing the first wire W1, the second wire W2 and the conductive wire W20 to extend out of the fixing member 44 and communicate to the outside of the skull 204.

The current is introduced into the depth electrode groups 30A to 30D, the planar electrode group 40 and the conductive area 20 respectively through the first wire W1, the second wire W2 and the conductive wire W20. When the movement of the human body changes, the processor compares the depth electrode group 30A ~30D and the impedance change generated by the planar electrode group 40 and/or the conductive area 20 serve as the basis for electrical stimulation control of the brain tissue 202.

Please refer to FIG. 5 . When the human body moves, the electrodes in the planar electrode group 40 (for example, the first planar electrode FE1 , the second planar electrode FE2 , the third planar electrode FE3 and the fourth planar electrode FE4 ) will move with it. Corresponding to the depth electrodes in the depth electrode group 30A that are closest to each other (for example, the first depth electrode DE1, the second depth electrode DE2, the third depth electrode DE3, and the fourth depth electrode DE4), a corresponding impedance change amount (for example, : the first impedance change amount △Z1, the second impedance change amount △Z2, the third impedance change amount △Z3, the fourth impedance change amount △Z4), the processor can control the application to the Electrical stimulation of brain tissue 202 ST.

Specifically, when the human body moves parallel to the first orientation D1 and the third orientation D3 (for example, when moving forward and backward horizontally), the first plane electrode FE1 and the first depth electrode DE1 of the depth electrode group 30A that are closest to each other generate the first The impedance change amount ΔZ1 is generated by the third plane electrode FE3 and the third depth electrode DE3 of the depth electrode group 30A that is closest to each other to produce a third impedance change amount ΔZ3. After the processor compares the first impedance change amount ΔZ1 and the third impedance change amount ΔZ3, it is used as a basis for electrical stimulation control of the brain tissue 202, and then controls the two depth electrode groups 30B and 30C located in the middle to control the electrical stimulation of the brain tissue 202. The nerve fibers of the surrounding brain tissue 202 are electrically stimulated ST. In this embodiment, the electrodes in the depth electrode groups 30B and 30C can serve as stimulation electrodes and provide electrical stimulation ST.

In the same way, when the human body moves parallel to the second orientation D2 and the fourth orientation D4 (for example, when moving horizontally left and right), the second plane electrode FE2 and the second depth electrode DE2 of the depth electrode group 30A that are closest to each other generate a second impedance. The change amount ΔZ2, the fourth plane electrode FE4 and the fourth depth electrode DE4 of the depth electrode group 30A that are closest to each other produce a fourth impedance change amount ΔZ4. After the second impedance change amount ΔZ2 and the fourth impedance change amount ΔZ4 are compared by the processor, as The basis for controlling the electrical stimulation of the brain tissue 202 is to control the two depth electrode groups 30B and 30C located in the middle to electrically stimulate the nerve fibers of the surrounding brain tissue 202 ST. In this embodiment, the electrodes in the depth electrode groups 30B and 30C can serve as stimulation electrodes and provide electrical stimulation ST.

Please refer to FIG. 6 . When the human body moves parallel to the axis C10 (for example, when moving vertically up and down), the plane electrode group 40 will generate a corresponding impedance change amount with the depth electrode group 30A that is closest to the corresponding distance, that is, the first plane The electrode FE1, the second planar electrode FE2, the third planar electrode FE3 and the fourth planar electrode FE4 are respectively the first depth electrode DE1, the second depth electrode DE2, the third depth electrode DE3 and the closest depth electrode group 30A. The four-depth electrode DE4 generates a fifth impedance variation ΔZ5. In addition, the conductive area 20 will produce a corresponding impedance change amount with the depth electrode group 30D that is closest to the corresponding distance, that is, the first depth electrode DE1, the second depth electrode DE2, and the third depth electrode DE3 of the conductive area 20 and the depth electrode group 30D. A sixth impedance variation ΔZ6 is generated with the fourth depth electrode DE4. The processor compares the fifth impedance change amount ΔZ5 with the sixth impedance change amount ΔZ6 as a basis for electrical stimulation control of the brain tissue 202, and then controls the two depth electrode groups 30B and 30C located in the middle to detect the surrounding areas. The nerve fibers of the brain tissue 202 are electrically stimulated ST. In this embodiment, the electrodes in the depth electrode groups 30B and 30C can serve as stimulation electrodes and provide electrical stimulation ST.

Please refer to Figure 7. The working principle of the present invention is that when the human body moves forward and backward horizontally (that is, moving parallel to the first direction D1 or the third direction D3), the brain tissue 202 will move parallel to the first direction D1 or the third direction D3. The orientation D3 produces deformation. For example, the first side brain tissue 206 is in a relaxed state, the third side brain tissue 208 is in a compressed state, and the electrode movement direction is shown by the arrow in Figure 7 . Therefore, it is possible to measure the first side brain tissue 206 and the third side brain tissue 208 produced during human body movements. The instantaneous impedance change caused by the deformation to the first depth electrode DE1 and the third depth electrode DE3 (ie, the comparison of the first impedance change amount ΔZ1 and the third impedance change amount ΔZ3).

In the same way, when the human body moves horizontally left and right or vertically up and down, the brain tissue 202 on opposite sides will be relatively deformed, so different instantaneous impedance changes may occur. For example, when moving horizontally left and right, the ratio of the second impedance change △Z2 to the fourth impedance change △Z4, or when moving vertically up and down, the ratio of the fifth impedance change △Z5 to the sixth impedance change △Z6 right.

Please refer to Figure 8 for the design example of the opposite synchronous timing voltage measurement circuit in the first position D1, the second position D2, the third position D3 and the fourth position D4. Four directions, including the second direction D2, the third direction D3, and the fourth direction D4, are measured/switched to detect changes in voltage impedance.

Please refer to Figures 9A~9B, 10A~10B, and 11A~11B, which show that multi-channel switching continuously detects the impedance change in each direction, and the sampling frequency can be set to at least 100Hz, for example. Numbers 1, 2, 3, and 4 at the top of Figures 9A, 10A, and 11A respectively represent the first orientation D1, the second orientation D2, the third orientation D3, and the fourth orientation D4. The circles in the first column represent the four directions of the planar electrode group 40. planar electrodes (ie, the first planar electrode FE1, the second planar electrode FE2, the third planar electrode FE3 and the fourth planar electrode FE4). The circles in the second column represent the depth electrodes (ie, the first depth electrodes) in the depth electrode group 30A. electrode DE1, the second depth electrode DE2, the third depth electrode DE3 and the fourth depth electrode DE4), the circles in the fifth column represent the depth electrodes in the depth electrode group 30D (ie, the first depth electrode DE1, the second depth electrode DE2 , the third depth electrode DE3 and the fourth depth electrode DE4), the circles in the sixth column represent the electrodes of the conductive region 20 .

9A and 9B show the planar electrode group for detecting the deformation of the brain tissue 202 when moving parallel to the first direction D1, the second direction D2, the third direction D3 and the fourth direction D4. 40 and the corresponding impedance change of the depth electrode group 30A, and the state of its electrode channel switching. FIG. 9A shows the transformation from the electrode channels in the first orientation D1 and the third orientation D3 to the electrode channels in the second orientation D2 and the fourth orientation D4, and so on. Specifically, when the electrode channels of the first orientation D1 and the third orientation D3 are connected, the first plane electrode FE1 of the plane electrode group 40 is connected to the first depth electrode DE1 of the depth electrode group 30A, and the first electrode can be measured. The impedance change amount ΔZ1 is measured, and the third planar electrode FE3 of the planar electrode group 40 is connected to the third depth electrode DE3 in the depth electrode group 30A, and the third impedance change amount ΔZ3 can be measured. When the electrode channels are transformed to the second orientation D2 and the fourth orientation D4, the electrode channels of the first orientation D1 and the third orientation D3 are disconnected, and the first planar electrode FE1, the third planar electrode FE3, and the depth electrode of the planar electrode group 40 The first depth electrode DE1 and the third depth electrode DE3 in the group 30A are both disconnected. At this time, the second plane electrode FE2 of the plane electrode group 40 and the second depth electrode DE2 in the depth electrode group 30A are connected, and the third depth electrode DE2 can be measured. The second impedance change amount ΔZ2, and the fourth planar electrode FE4 of the planar electrode group 40 is connected to the fourth depth electrode DE4 in the depth electrode group 30A, the fourth impedance change amount ΔZ4 can be measured. Thereby, the processor can control the electrical stimulation ST applied to the brain tissue 202 based on the comparison of multiple impedance changes.

10A and 10B show the corresponding deformation of the detected brain tissue 202 for the planar electrode group 40 when moving in an oblique direction parallel to the detection of the first orientation D1, the second orientation D2, the third orientation D3, and the fourth orientation D4. The amount of impedance change of the depth electrode group 30A and the state of its electrode channel switching. Figure 10A shows the transformation of the electrode channels from the first orientation D1 and the second orientation D2, and the third orientation D3 and the fourth orientation D4 to the first orientation D1 and the fourth orientation D4, and the second orientation D2 and the third orientation D3. the electrode channel, and so on. Specifically, the left picture of FIG. 10A represents the four planar electrodes in the planar electrode group 40 and the four deep electrodes in the depth electrode group 30A. Both electrodes are turned on at the same time, and the processor will simultaneously communicate with the third position D3 based on the impedance changes representing the first position D1 and the second position D2 (i.e., the first impedance change ΔZ1 and the second impedance change ΔZ2). Compare it with the impedance change amount in the fourth direction D4 (ie, the third impedance change amount ΔZ3 and the fourth impedance change amount ΔZ4) to control the electrical stimulation ST applied to the brain tissue 202 . In the embodiment on the right side of FIG. 10A , the four planar electrodes representing the planar electrode group 40 and the four depth electrodes in the depth electrode group 30A are all turned on at the same time, and the processor will simultaneously act according to the parameters representing the first orientation D1 and the fourth orientation. The impedance change amount of D4 (that is, the first impedance change amount ΔZ1 and the fourth impedance change amount ΔZ4) is related to the impedance change amount of the second position D2 and the third position D3 (that is, the second impedance change amount ΔZ2 and the third impedance change amount ΔZ2). The impedance change amount ΔZ3) is compared to control the electrical stimulation ST applied to the brain tissue 202.

11A and 11B show the impedance changes of the flat electrode group 40 and the corresponding depth electrode group 30A and the conductive area 20 and the corresponding depth electrode group 30D when the deformation of the brain tissue 202 is detected when moving parallel to the axis C10. The state during electrode stimulation. FIG. 11A shows that the four planar electrodes in the planar electrode group 40 and the four depth electrodes in the depth electrode group 30A, as well as the electrodes in the conductive area 20 and the four depth electrodes in the depth electrode group 30D are all conductive at the same time. The processor will conduct according to the planar electrode group. 40 and the fifth impedance change amount ΔZ5 generated by the depth electrode group 30A are compared with the sixth impedance change amount ΔZ6 generated by the electrodes in the conductive area 20 and the depth electrode group 30D to control the impedance applied to the brain tissue 202 Electrical stimulation of ST.

Please refer to Figures 12A and 12B. Combining the aforementioned detection of instantaneous impedance changes caused by human body movements, opposite synchronous sequential voltage measurement, and multi-channel pairing switching, it can be applied to the detection of continuous human body movements. And give electrical stimulation to ST at the appropriate time.

|△Z3|時，判斷此時動作為人體起身或身軀向前，便啟動電刺激模式，控制深度電極組30B、30C給予電刺激ST。 Figure 12A represents the change in impedance value when a human body stands up or moves forward, which can comprehensively correspond to the detection state during parallel movement shown in Figure 5 and the channel switching state in Figure 9A. In this embodiment, assuming that the first orientation D1 is the front, when the human body stands up or moves forward, the first impedance change amount ΔZ1 and the third impedance change amount ΔZ3 are as shown in FIG. 12A . In one embodiment, the processor calculation satisfies: |ΔZ3-ΔZ1|

When |△Z3|, it is judged that the action at this time is that the human body stands up or the body moves forward, and the electrical stimulation mode is started, and the depth electrode groups 30B and 30C are controlled to provide electrical stimulation ST.

Figure 12B represents the change in impedance value of the human body walking, which can comprehensively correspond to the detection state during vertical movement shown in Figure 6. Figure 12B shows the changes in the fifth impedance change amount ΔZ5 and the sixth impedance change amount ΔZ6 when the human body walks. In one embodiment, when the differential characteristics of the impedance changes ΔZ5 and ΔZ6 are determined to occur three times within a set period, it is determined that the action at this time is a walking state, and the electrical stimulation mode is started to control the depth electrode groups 30B and 30C. Give electrical stimulation to ST.

It is worth noting that when the motion monitoring sensor provided by the present invention is implanted into the human brain, the orientation has been confirmed first, so that the orientation of each electrode can be known to facilitate control and detection of human body motion.

Please refer to Figure 13, which shows that the amount of impedance change caused by the deformation of the brain tissue caused by the human body's movement in the same direction is linearly related to the amount of displacement. For example, when the human body is displaced by 1 mm, the impedance change value is approximately 0.55 kiloohms; when the human body is displaced by 2 mm, the impedance change value is approximately 1.2 kiloohms.

Please refer to Figure 14, which shows that the amount of impedance change caused by the brain tissue deformation caused by the human body's movement in the same direction is linearly related to the amount of brain tissue compression. For example, when the brain tissue compression rate is 10%, the impedance change value is about 8 ohms; when the brain tissue compression rate is 40%, the impedance change value is about 30 ohms.

Figures 13 and 14 illustrate that the working principle of the present invention using human body displacement and brain tissue compression to detect impedance changes to provide electrical stimulation of the human brain is indeed feasible.

Referring to the embodiment shown in FIG. 15 , the motion monitoring sensor 100A includes a body 10 , a conductive area 20 , a depth electrode group 30A and a planar electrode group 40 .

Please refer to FIG. 15 . When the human body moves parallel to the first orientation D1 and the third orientation D3 (for example, when moving forward and backward horizontally), the first plane electrode FE1 and the first depth electrode DE1 of the depth electrode group 30A generate a first The third plane electrode FE3 and the third depth electrode DE3 of the depth electrode group 30A generate a third impedance change amount ΔZ3. After the processor compares the first impedance change amount ΔZ1 with the third impedance change amount ΔZ3, it is used as a basis for electrical stimulation control of the brain tissue 202, and then controls the depth electrode group 30A to stimulate the nerves of the surrounding brain tissue 202. Fibers are electrically stimulated ST. In this embodiment, the electrodes in the depth electrode group 30A can also serve as stimulation electrodes and provide electrical stimulation ST.

In the same way, when the human body moves parallel to the second orientation D2 and the fourth orientation D4 (for example, when moving horizontally left and right), the second plane electrode FE2 and the second depth electrode DE2 of the depth electrode group 30A generate a second impedance change amount Δ. Z2, the fourth planar electrode FE4 and the fourth depth electrode DE4 of the depth electrode group 30A generate a fourth impedance change amount ΔZ4. After the processor compares the second impedance change amount ΔZ2 with the fourth impedance change amount ΔZ4, it is used as a basis for electrical stimulation control of the brain tissue 202, and then controls the depth electrode group 30A to stimulate the nerves of the surrounding brain tissue 202. Fibers are electrically stimulated ST.

Please refer to Figure 16. When the human body moves parallel to the axis C10 (for example, when moving vertically up and down), the first planar electrode FE1, the second planar electrode FE2, the third planar electrode FE3 and the fourth planar electrode FE4 are respectively in contact with the depth. The first depth electrode DE1 and the second depth electrode DE1 of the electrode group 30A The depth electrode DE2, the third depth electrode DE3 and the fourth depth electrode DE4 generate a fifth impedance variation ΔZ5. In addition, the conductive area 20 and the first depth electrode DE1, the second depth electrode DE2, the third depth electrode DE3 and the fourth depth electrode DE4 of the depth electrode group 30D generate a sixth impedance variation ΔZ6. The processor compares the fifth impedance change amount ΔZ5 with the sixth impedance change amount ΔZ6 as a basis for electrical stimulation control of the brain tissue 202, and then controls the depth electrode group 30A to stimulate the nerve fibers of the surrounding brain tissue 202. Perform electrical stimulation ST.

It should be noted that the embodiment of FIG. 1 has four depth electrode groups 30A˜30D, while the embodiment of FIG. 15 only has one depth electrode group 30A. According to the above description, it can be known that the desired effect of the present invention can be achieved by using only one depth electrode group 30A. Regardless of using one depth electrode group 30A or four depth electrode groups 30A~30D, the working principles include detection of instantaneous impedance changes caused by human body movements, opposite synchronous sequential voltage measurement, and multi-channel pairing switching. Similarly, it can be used to detect the continuous movements of the human body and provide electrical stimulation at the appropriate time. By analogy, two groups, three groups, or more than four groups of depth electrode groups can be used, which can be designed according to actual needs.

To sum up, the action monitoring sensor provided by the present invention as an electrical stimulation control device measures the instantaneous impedance changes caused by the deformation of brain tissue during action through planar electrodes, depth electrodes and conductive areas, and determines the patient's actions. The start or change of state is used as a characteristic judgment of the start time of electrical stimulation, so that patients who originally had poor response to continuous electrical stimulation can be used at the switching point of the gait cycle (for example, switching from sitting to standing or turning, heel contact Electrical stimulation is only given when the patient is on or off the ground, so it can effectively improve the patient's ability to move and walk.

Although the present invention has been disclosed above through embodiments, they are not intended to limit the present invention. Anyone with ordinary skill in the relevant technical field will not deviate from the spirit and scope of the present invention. Some modifications and embellishments may be made, so the scope of protection of the present invention shall be determined by the appended patent application scope.

100:Motion monitoring sensor

10:Ontology

20: Conductive area

30A~30D: Depth electrode group

40: Planar electrode group

41:Substrate

411: Side 1

412:Second side

42:hole

43:Microstructure

C10: Axis

D1: first position

D2: Second position

D3: Third position

D4: The fourth position

DE1: first depth electrode

DE2: Second depth electrode

DE3: The third depth electrode

DE4: The fourth depth electrode

FE1: first plane electrode

FE2: Second plane electrode

FE3: third plane electrode

FE4: The fourth plane electrode

W1: first wire

W2: Second wire

W20: Conductive wire

Claims (14)

An action monitoring sensor is provided in the brain tissue of the human body and is suitable for connection with a processor. The action monitoring sensor includes: A body has an axis, and the body has two opposite axial ends along the axis; A conductive area is provided at one of the axial ends of the body, and the conductive area is connected to a conductive wire; At least one depth electrode group. The depth electrode group includes four depth electrodes. The four depth electrodes are arranged on the surface of the body around the axis. The four depth electrodes respectively correspond to four directions. Each depth electrode is connected to a first conductor; and A planar electrode group includes a base material and four planar electrodes. The base material has an opposite first surface and a second surface. The base material is disposed on the body relative to the conductive area through the second surface. At the other axial end, the four planar electrodes are arranged on the base material around the axis, the four planar electrodes respectively correspond to the four directions, and each of the planar electrodes is connected to a second wire; Current is introduced into the conductive area, each depth electrode and each plane electrode respectively through the conductive wire, each first wire and each second wire. When the movement of the human body changes, the processor compares the depth The amount of impedance change produced by the electrode group, the planar electrode group and/or the conductive area serves as the basis for electrical stimulation control of the brain tissue of the human body. The motion monitoring sensor of claim 1, wherein the base material has a hole penetrating the base material parallel to the axial direction, and the planar electrodes are arranged on the base material surrounding the hole. Such as the motion monitoring sensor of claim 2, wherein each of the first wires, each of the second wires and the conductive wire are respectively penetrated from the body and the base material through the hole. The motion monitoring sensor of claim 1, wherein the second surface of the substrate is provided with microstructures. For example, the motion monitoring sensor of claim 4, wherein the height of the microstructure protruding from the substrate is equal to or greater than 50 micrometers (μm). The motion monitoring sensor of claim 1, wherein the four directions include a first direction, a second direction, a third direction and a fourth direction, and the first direction, the second direction, the third direction The orientation and the fourth orientation are perpendicular to the axis and extend radially at equal angles with the axis as the center. The first orientation and the third orientation are symmetrical with respect to both sides of the axis, and the second orientation and the fourth orientation The orientation is symmetrical with respect to the other two sides of the axis, and the first orientation is between the second orientation and the fourth orientation; the four depth electrodes include electrodes facing the first orientation, the second orientation, and the third orientation respectively. The first depth electrode, the second depth electrode, the third depth electrode and the fourth depth electrode are oriented in the same direction as the fourth direction, and the four planar electrodes include electrodes facing the first direction, the second direction and the third depth electrode respectively. The first planar electrode, the second planar electrode, the third planar electrode and the fourth planar electrode are in the fourth orientation. The motion monitoring sensor of claim 6, wherein when the human body moves parallel to the first direction and the third direction, the first plane electrode and the first depth electrode of the depth electrode group produce a first impedance change. The third plane electrode and the third depth electrode of the depth electrode group generate a third impedance change amount, and the processor compares the first impedance change amount with the third impedance change amount, as a result for the human body The basis for electrical stimulation control of the brain tissue. The motion monitoring sensor of claim 6, wherein when the human body moves parallel to the second direction and the fourth direction, the second plane electrode and the second depth electrode of the depth electrode group produce a second impedance change. The fourth plane electrode and the fourth depth electrode of the depth electrode group generate a fourth impedance change amount, and the processor compares the second impedance change amount with the fourth impedance change amount, as a result for the human body The basis for electrical stimulation control of the brain tissue. The motion monitoring sensor of claim 6, wherein when the human body moves parallel to the axis, the first planar electrode, the second planar electrode, the third planar electrode and the fourth planar electrode are respectively in contact with the depth electrode. The first depth electrode, the second depth electrode, the third depth electrode and the fourth depth electrode of the group generate a fifth impedance change amount, and the conductive area and the first depth electrode, the second depth electrode of the depth electrode group The depth electrode, the third depth electrode and the fourth depth electrode generate a sixth impedance change, and the processor compares the fifth impedance change and the sixth impedance change as a result of the brain tissue of the human body. The basis for electrical stimulation control. The motion monitoring sensor of claim 1, wherein the first surface of the base material is provided with a fixing member, and the fixing member is suitable for being placed on the skull of the human body, and the brain tissue is located in the skull. The motion monitoring sensor of claim 10, wherein the fixing member has a channel for providing each of the first wires, each of the second wires and the conductive wires to extend out of the fixing member and be connected to the outside of the skull. Such as the motion monitoring sensor of claim 1, wherein the base material is flat and circular, and the maximum diameter of the base material is equal to or less than 10 millimeters (mm). For example, the motion monitoring sensor of claim 1, wherein the material of the base material is one of silicone or thermoplastic polyurethane (TPU). Such as the motion monitoring sensor of claim 1, which has four groups of depth electrode groups, the four groups of depth electrode groups are arranged on the body parallel to the axis, and the four depth electrodes of each depth electrode group respectively correspond to The four directions and part of the depth electrode groups are used as stimulation electrodes to electrically stimulate the brain tissue of the human body.

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