CN115414582A - Hydrocephalus diverging device - Google Patents
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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Abstract
Translated fromChinese
Description
Translated fromChinese技术领域technical field
本发明涉及医疗器械制造技术领域，具体涉及一种脑积水分流装置。The invention relates to the technical field of medical device manufacturing, in particular to a hydrocephalus diversion device.
背景技术Background technique
颅内压是指颅的内容物，对颅硬膜包括颅骨造成的压力。正常情况下，人的颅内压在80-180mmH2O之间，当人们发生头颅损伤等情况时，由于对颅内脑积水的吸收功能受损，因此，颅内压会急速上升。在现有技术中，当病患因颅脑受损等原因造成脑积水时，通常会采用脑室腹腔分流手术，即通过分流管将脑积水分流道腹腔吸收掉。为了及时排出颅内脊液，现有的分流管通常包括一个可设定分流压力的分流阀，当颅内压超过设定值时，分流阀导通，颅内脊液即可通过分流管分流到腹腔，以使颅内压维持在正常水平。Intracranial pressure is the pressure exerted by the contents of the cranium on the dura mater, including the skull. Under normal circumstances, the intracranial pressure of a person is between 80-180mmH2 O. When people suffer from head injury, etc., the intracranial pressure will rise rapidly due to the impaired absorption of intracranial hydrocephalus. In the prior art, when a patient suffers from hydrocephalus due to craniocerebral damage or other reasons, ventriculoperitoneal shunt surgery is usually performed, that is, the hydrocephalus is absorbed into the peritoneal cavity through a shunt tube. In order to discharge the intracranial spinal fluid in time, the existing shunt tube usually includes a shunt valve that can set the shunt pressure. When the intracranial pressure exceeds the set value, the shunt valve is turned on, and the intracranial spinal fluid can be shunted through the shunt tube to the abdominal cavity to maintain intracranial pressure at normal levels.
然而现有的分流管仍然存在如下技术缺陷：这些分流管均无法自动检测颅内压，导致无法精准分流。也就是说，医护人员只能根据经验事先做出判断，然后设置分流阀的启动压力。当颅内压达到设定的分流阀启动压力时，分流阀开通，从而将脑积水分流制腹腔。可以理解的是，由于分流阀的制造误差，尤其是，脑积水为具有一定粘性的液体，分流管在使用一定时间后，分流阀的实际启动压力与其设置的启动压力之间会存在一个误差值，导致无法准确分流“降压”。此外，由于分流阀是一种极为精密的装置，当具有粘性的脑积水较长时间分流后，容易导致分流阀的堵塞以致失效，此时，分流管将无法实现分流，而医护人员也无从得知，当病患出现较为严重的症状时，医护人员只能为病患重新更换分流管，从而严重影响病患的治疗。However, the existing shunt tubes still have the following technical defects: none of these shunt tubes can automatically detect the intracranial pressure, resulting in the inability to accurately shunt. That is to say, medical staff can only make judgments in advance based on experience, and then set the starting pressure of the shunt valve. When the intracranial pressure reaches the set shunt valve activation pressure, the shunt valve opens to divert the hydrocephalus into the abdominal cavity. It is understandable that due to the manufacturing error of the shunt valve, especially, hydrocephalus is a viscous liquid, after the shunt tube is used for a certain period of time, there will be an error between the actual starting pressure of the shunt valve and the set starting pressure value, resulting in the inability to accurately shunt the "buck". In addition, since the shunt valve is an extremely precise device, when the viscous hydrocephalus is shunted for a long time, it is easy to cause the blockage of the shunt valve and even fail. It is learned that when a patient has more serious symptoms, the medical staff can only replace the shunt for the patient, which seriously affects the treatment of the patient.
发明内容Contents of the invention
本发明的目的是为了提供一种脑积水分流装置，一方面，可实时检测病患的实际颅内压，方便医护人员及时调整医疗措施，另一方面，可实现自主模式的反馈性分流，以便使病患的颅内压稳定在设定水平。The purpose of the present invention is to provide a hydrocephalus shunt device. On the one hand, it can detect the actual intracranial pressure of the patient in real time, so that the medical staff can adjust the medical measures in time. On the other hand, it can realize the feedback shunt in the autonomous mode. In order to stabilize the patient's intracranial pressure at the set level.
为了实现上述目的，本发明采用以下技术方案：In order to achieve the above object, the present invention adopts the following technical solutions:
一种脑积水分流装置，包括主分流管，所述主分流管一端为吸液端，另一端为出液端，还包括脑积水处理单元，所述脑积水处理单元包括压力传感控制单元、分流泵、中央控制电路，先通过中央控制电路设定分流压力P，当压力传感控制单元检测到的颅内压P1大于等于设定的分流压力P时，中央控制电路使分流泵启动，从而通过主分流管将颅内脑积水分流到腹腔。A hydrocephalus shunt device, comprising a main shunt tube, one end of the main shunt tube is a liquid suction end, the other end is a liquid outlet end, and a hydrocephalus treatment unit, the hydrocephalus treatment unit includes a pressure sensor The control unit, the shunt pump, and the central control circuit first set the shunt pressure P through the central control circuit. When the intracranial pressure P1 detected by the pressure sensing control unit is greater than or equal to the set shunt pressure P, the central control circuit makes the shunt pump Activation, thereby shunting the intracranial hydrocephalus into the peritoneal cavity through the main shunt.
我们可先通过中央控制电路设定分流压力P，当压力传感控制单元检测到的颅内压P1大于等于设定的分流压力P时，即可通过中央控制电路使分流泵启动，从而通过主分流管将颅内脑积水主动分流到腹腔。可以理解的是，分流泵作为一种微型电子泵，可主动地将主分流管的吸液端的脑积水通过出液端强制输出到腹腔，从而实现脑积水的主动分流。此外，压力传感控制单元可实时监测颅内压，一方面，当压力传感控制单元检测到的颅内压P1大于等于设定的分流压力P时，中央控制电路可使分流泵启动，从而通过主分流管将颅内脑积水分流到腹腔内，有效的避免因分流管的局部堵塞等原因造成分流不畅，有利于使病患的颅内压稳定在设定水平；另一方面，便于医护人员实时了解掌握病患的颅内压状态，以便根据症状随时调整分流量和治疗方案。We can first set the shunt pressure P through the central control circuit. When the intracranial pressure P1 detected by the pressure sensing control unit is greater than or equal to the set shunt pressure P, the shunt pump can be activated through the central control circuit, thereby passing the main The shunt actively shunts the intracranial hydrocephalus into the peritoneal cavity. It can be understood that the shunt pump, as a micro electronic pump, can actively output the hydrocephalus at the suction end of the main shunt tube to the peritoneal cavity through the liquid outlet, so as to realize the active shunting of hydrocephalus. In addition, the pressure sensing control unit can monitor the intracranial pressure in real time. On the one hand, when the intracranial pressure P1 detected by the pressure sensing control unit is greater than or equal to the set shunt pressure P, the central control circuit can start the shunt pump, thereby The intracranial hydrocephalus is diverted into the abdominal cavity through the main shunt tube, which can effectively avoid the shunt blockage caused by the partial blockage of the shunt tube, and help stabilize the patient's intracranial pressure at the set level; on the other hand, It is convenient for medical staff to understand the intracranial pressure status of patients in real time, so as to adjust the shunt flow and treatment plan at any time according to the symptoms.
作为优选，还包括可无线充电的电池模块、可为电池模块无线充电的电池充电、可无线接收颅内压P1信号并显示的无线信号接收装置。Preferably, it also includes a battery module that can be charged wirelessly, a battery charging device that can charge the battery module wirelessly, and a wireless signal receiving device that can wirelessly receive and display the intracranial pressure P1 signal.
由于本发明的脑积水分流装置优选地需要植入体内，以避免脑部受到污染，因此，本发明包括可无线充电的电池模块、可为电池模块无线充电的电池充电，其中的电池模块用于为分流泵等供电，其同样需要植入体内，可理解的是，电池模块的体积越小越好，因此在使用过程中需要及时充电。而电池充电则可为电池模块无线充电，从而方便本发明的正常使用。由于此类小功率的无线充电电池、电池充电均属于现有技术，在此不做详细的描述。Since the hydrocephalus shunt device of the present invention preferably needs to be implanted in the body to avoid contamination of the brain, the present invention includes wirelessly rechargeable battery modules, battery rechargeable battery modules that can be wirelessly recharged, wherein the battery modules are used As for powering the shunt pump, etc., it also needs to be implanted in the body. It is understandable that the smaller the battery module, the better, so it needs to be charged in time during use. The charging of the battery can be wireless charging of the battery module, thereby facilitating the normal use of the present invention. Since such low-power wireless rechargeable batteries and battery charging belong to the prior art, no detailed description will be given here.
特别是，当本发明被植入病患体内时，医护人员难以及时观察、了解颅内压P1的实际数据。为此，本发明还包括可无线接收颅内压P1信号并显示的无线信号接收装置，这样，外部的无线信号接收装置即在显示屏上实时显示颅内压P1。In particular, when the present invention is implanted in a patient, it is difficult for medical staff to observe and understand the actual data of the intracranial pressure P1 in time. Therefore, the present invention also includes a wireless signal receiving device capable of wirelessly receiving and displaying the intracranial pressure P1 signal, so that the external wireless signal receiving device displays the intracranial pressure P1 in real time on the display screen.
作为优选，所述分流泵为压电陶瓷水泵。Preferably, the shunt pump is a piezoelectric ceramic water pump.
压电陶瓷水泵具有体积小，灵敏度高等优点。The piezoelectric ceramic water pump has the advantages of small size and high sensitivity.
作为优选，还包括与主分流管并联的次分流管，所述次分流管上设有分流阀，所述分流阀的启动压力为P2，允许的颅内压最高值为P3，并且P＜P2≤P3。Preferably, it also includes a secondary shunt pipe connected in parallel with the main shunt pipe, the secondary shunt pipe is provided with a shunt valve, the starting pressure of the shunt valve is P2, the maximum allowable intracranial pressure is P3, and P<P2 ≤P3.
本发明在主分流管上还并联有带分流阀的次分流管，也就是说，次分流管类似于现有的被动式分流管。这样，即使主分流管因分流泵等元件出现故障等造成无法分流的极端情况时，次分流管也可作为应急分流通道而分流，避免出现完全无法分流的情况。可以理解的是，由于此处的次分流管只是作为主分流管的备份，因此，不会出现因长时间分流导致的堵塞等现象，进而可大大提升分流的可靠性和稳定性。In the present invention, a secondary shunt pipe with a shunt valve is also connected in parallel on the main shunt pipe, that is to say, the secondary shunt pipe is similar to the existing passive shunt pipe. In this way, even if the main shunt pipe cannot be shunted due to the failure of components such as the shunt pump, etc., the secondary shunt pipe can also be used as an emergency shunt channel to shunt the flow, avoiding the situation where the flow cannot be shunted at all. It can be understood that since the secondary shunt here is only used as a backup of the main shunt, there will be no clogging caused by long-time shunting, which can greatly improve the reliability and stability of shunting.
特别是，本发明将分流阀的启动压力P2、允许的颅内压最高值P3、以及设定的分流压力P之间形成如下关系：P＜P2≤P3，也就是说，次分流管上分流阀的启动压力P2要大于设定的分流压力P，因此，可确保主分流管相比较次分流管优先分流，并且次分流管上分流阀的启动压力P2要小于允许的颅内压最高值P3，避免因分流不及时导致的病患颅内压过高。由于现有包括分流阀的分流管属于现有技术，本发明的次分流管可参考借鉴现有分流管的技术，在此不做详细的描述。In particular, the present invention forms the following relationship among the starting pressure P2 of the shunt valve, the maximum allowable intracranial pressure P3, and the set shunt pressure P: P<P2≤P3, that is to say, the shunt on the secondary shunt tube The starting pressure P2 of the valve must be greater than the set shunt pressure P, therefore, it can ensure that the main shunt pipe is preferentially shunted compared with the secondary shunt pipe, and the starting pressure P2 of the shunt valve on the secondary shunt pipe is lower than the maximum allowable intracranial pressure P3 , to avoid excessive intracranial pressure in patients caused by untimely shunt. Since the existing shunt pipe including the shunt valve belongs to the prior art, the secondary shunt pipe of the present invention can refer to the technology of the existing shunt pipe, and will not be described in detail here.
作为优选，所述压力传感控制单元包括一端与主分流管的吸液端连通的测压分管，测压分管的另一端封闭，在测压分管内设有可移动的磁铁柱，磁铁柱在测压分管内分隔出靠近吸液端的受压腔、靠近封闭端的承压腔，在测压分管外设有可轴向移动的磁感应线圈。Preferably, the pressure sensing control unit includes a pressure measuring sub-pipe with one end connected to the suction end of the main shunt pipe, the other end of the pressure measuring sub-pipe is closed, and a movable magnet column is arranged in the pressure measuring sub-pipe, and the magnet post is in the The pressure measuring sub-pipe separates a pressure chamber close to the liquid suction end and a pressure chamber close to the closed end, and an axially movable magnetic induction coil is arranged outside the pressure measurement sub pipe.
本发明的压力传感控制单元包括一端封闭、另一端与主分流管的吸液端连通的测压分管，而测压分管内可移动的磁铁柱则在测压分管内分隔出靠近吸液端的受压腔、靠近封闭端的承压腔。这样，当颅内压升高时，测压分管内的受压腔压力同步上升，从而驱动磁铁柱向承压腔一侧移动，此时，测压分管外的磁感应线圈在移动的磁铁柱磁场作用下产生相应的电信号，即可感测颅内压。可以理解的是，当磁铁柱向承压腔一侧移动时，封闭的承压腔内的空气压力会线性的逐步上升，也就是说，承压腔的空气所形成的阻力类似于弹簧的弹力，其力的大小和磁铁柱的移动距离成正比。当然，我们可在测压分管标注相应的压力值数据，以便于医护人员正确地观察颅内压力P1。The pressure sensing control unit of the present invention includes a pressure measuring sub-pipe with one end closed and the other end in communication with the liquid suction end of the main shunt pipe, and the movable magnet column in the pressure measuring sub pipe separates a section close to the liquid suction end in the pressure measurement sub pipe. Pressure chamber, pressure chamber near the closed end. In this way, when the intracranial pressure rises, the pressure of the pressure chamber in the manometry tube rises synchronously, thereby driving the magnet column to move to the pressure chamber side. At this time, the magnetic induction coil outside the manometry tube is in the magnetic field of the moving magnet column Under the action, corresponding electrical signals can be generated to sense intracranial pressure. It can be understood that when the magnet column moves to the side of the pressure chamber, the air pressure in the closed pressure chamber will gradually increase linearly, that is to say, the resistance formed by the air in the pressure chamber is similar to the elastic force of a spring , the magnitude of its force is proportional to the moving distance of the magnet column. Of course, we can mark the corresponding pressure value data on the manometry branch, so that the medical staff can correctly observe the intracranial pressure P1.
需要说明的是，由于磁感应线圈在测压分管外是可轴向移动的，因此，通过调节磁感应线圈在测压分管外的位置，即可方便地调节颅内压P1的测量精度。It should be noted that since the magnetic induction coil can move axially outside the pressure measuring tube, the measurement accuracy of the intracranial pressure P1 can be adjusted conveniently by adjusting the position of the magnetic induction coil outside the pressure measuring tube.
作为优选，所述测压分管包括直径外扩的检测段，所述磁铁柱包括位于检测段内的滑动块，滑动块在检测段内分隔出靠近吸液端的施压腔、靠近封闭端的泄压腔，在施压腔和泄压腔之间设有包括单向阀的泄压管，滑动块靠近承压腔一侧设有位于测压分管内的压力柱，压力柱的端部为具有磁性的感应端，所述磁感应线圈设置在靠近承压腔一侧的测压分管上，滑动块的直径为压力柱直径的2-3倍。Preferably, the pressure measuring sub-pipe includes a detection section with an outwardly expanded diameter, and the magnet column includes a sliding block located in the detection section. The sliding block separates a pressure chamber near the liquid suction end and a pressure relief chamber near the closed end in the detection section. A pressure relief pipe including a one-way valve is provided between the pressure application chamber and the pressure relief chamber. The side of the sliding block close to the pressure chamber is provided with a pressure column in the pressure measurement branch pipe. The end of the pressure column is a magnetic The induction end, the magnetic induction coil is arranged on the pressure measuring sub-tube close to the side of the pressure chamber, and the diameter of the sliding block is 2-3 times the diameter of the pressure column.
为了提升颅内压的测量精度，本发明测压分管包括直径外扩的检测段，这样，当颅内压升高时，其压力会作用在直径较大（面积较大）的滑动块上，继而可驱动滑动块的移动，相反地，位于测压分管内的压力柱由于直径较小（面积较小），所承受的空气阻力也较小。可以知道的是，当两者之间的直径之比为2-3时，其面积之比为4-9，也就是说，磁铁柱对颅内压有一个力的放大作用，确保磁铁柱的灵活移动，有利于提升颅内压的检测精度。In order to improve the measurement accuracy of intracranial pressure, the pressure measurement branch tube of the present invention includes a detection section with an outwardly expanded diameter, so that when the intracranial pressure rises, its pressure will act on the sliding block with a larger diameter (larger area), Then the sliding block can be driven to move. On the contrary, the pressure column located in the pressure measuring sub-pipe has a smaller diameter (smaller area), and the air resistance it bears is also smaller. It can be known that when the diameter ratio between the two is 2-3, the area ratio is 4-9, that is to say, the magnet column has a force amplification effect on the intracranial pressure, ensuring the magnet column Flexible movement is conducive to improving the detection accuracy of intracranial pressure.
特别是，当磁铁柱向承压腔一侧移动时，封闭的泄压腔内的空气压力也会逐渐上升，从而对滑动块形成阻力，为此，本发明在施压腔和泄压腔之间设有包括单向阀的泄压管，当泄压腔内的空气压力上升时，可通过泄压管泄压回流到施压腔内，从而消除泄压腔内的气体对滑动块形成的阻力。当然，其中的单向阀应为从泄压腔至施压腔正向导通，从而避免颅内压通过泄压管泄压而无法驱动磁铁柱移动。In particular, when the magnet column moves to the side of the pressure chamber, the air pressure in the closed pressure relief chamber will gradually rise, thereby forming resistance to the sliding block. A pressure relief pipe including a one-way valve is arranged between them. When the air pressure in the pressure relief chamber rises, the pressure can be released and flowed back into the pressure application chamber through the pressure relief pipe, thereby eliminating the impact of the gas in the pressure relief chamber on the sliding block. resistance. Of course, the one-way valve therein should be positively conducted from the pressure relief chamber to the pressure application chamber, so as to prevent the intracranial pressure from being released through the pressure relief tube and unable to drive the magnet column to move.
作为优选，所述测压分管为透明管，所述磁感应线圈包括螺接在测压分管外的支架，绕设在支架上的若干线圈，所述线圈在测压分管的轴向上等间距分布，当颅内压升高时，磁铁柱向承压腔一侧移动，从而压缩承压腔内的空气；当磁铁柱移动至与其中一个线圈对应时，该线圈即可输出一个代表颅内压P1的电信号。Preferably, the pressure measuring sub-tube is a transparent tube, the magnetic induction coil includes a bracket screwed outside the pressure measuring sub-tube, several coils wound on the bracket, and the coils are equally spaced in the axial direction of the pressure measuring sub-tube , when the intracranial pressure rises, the magnet column moves to the side of the pressure chamber, thereby compressing the air in the pressure chamber; when the magnet column moves to correspond to one of the coils, the coil can output a signal representing the intracranial pressure Electrical signal of P1.
本发明的磁感应线圈包括螺接在测压分管外的支架、以及绕设在支架上的若干等间距分布的线圈，这样，我们可通过中央控制电路方便地设定分流压力P。当颅内压升高至设定的分流压力P时，磁铁柱向承压腔一侧移动至对应的线圈位置，该线圈即可输出一个代表颅内压P1的电信号，此时该颅内压P1即等于分流压力P。可以理解的是，在磁铁柱向承压腔一侧移动而经过前面的线圈时，同样会相应地输出一个小于分流压力P的颅内压P1，此时的中央控制电路不会启动分流泵工作。The magnetic induction coil of the present invention includes a bracket screwed on the outside of the pressure measuring branch tube, and several equally spaced coils wound on the bracket, so that we can conveniently set the shunt pressure P through the central control circuit. When the intracranial pressure rises to the set shunt pressure P, the magnet column moves to the side of the pressure chamber to the corresponding coil position, and the coil can output an electrical signal representing the intracranial pressure P1. The pressure P1 is equal to the split pressure P. It can be understood that when the magnet column moves to the side of the pressure chamber and passes through the front coil, an intracranial pressure P1 lower than the shunt pressure P will be output correspondingly, and the central control circuit at this time will not start the shunt pump to work .
当然，我们可在所述磁感应线圈上设置计量刻度，当我们转动支架、以使磁感应线圈轴向移动时，即可方便地调教压力传感控制单元的准确性。Of course, we can set a measurement scale on the magnetic induction coil, and when we rotate the bracket to move the magnetic induction coil axially, the accuracy of the pressure sensing control unit can be adjusted conveniently.
作为优选，所述泄压管包括与泄压腔连通的第一管、与施压腔连通的第二管，第二管套接在第一管外面，所述单向阀包括部分粘结在第一管上连接第二管开口处的硅胶膜片，当第二管相对第一管形成正向压力时，所述硅胶膜片紧密贴靠第一管开口，此时的泄压管处于正向截止状态；当第一管相对第二管形成反向压力时，所述硅胶膜片部分地离开第一管开口，此时的泄压管处于反向导通状态。Preferably, the pressure relief pipe includes a first pipe communicated with the pressure relief chamber, a second pipe communicated with the pressure application chamber, the second pipe is sleeved outside the first pipe, and the one-way valve includes a part bonded to the The first tube is connected to the silicone diaphragm at the opening of the second tube. When the second tube forms a positive pressure relative to the first tube, the silicone diaphragm is closely attached to the opening of the first tube. At this time, the pressure relief tube is in a positive position. To the cut-off state; when the first pipe forms a reverse pressure relative to the second pipe, the silicone diaphragm partly leaves the opening of the first pipe, and the pressure relief pipe at this time is in a reverse conduction state.
由于泄压管包括与泄压腔连通的第一管、与施压腔连通的第二管，并第二管套接在第一管外面，因此，当泄压管内具有正向压力时，可推开硅胶膜片而导通；当泄压管内具有反向压力时，可推动硅胶膜片紧密贴靠第一管开口而截止。Since the pressure relief pipe includes a first pipe communicating with the pressure relief chamber, a second pipe communicating with the pressure application chamber, and the second pipe is sleeved outside the first pipe, therefore, when there is positive pressure in the pressure relief pipe, it can Push away the silicone diaphragm to conduct; when there is reverse pressure in the pressure relief pipe, the silicone diaphragm can be pushed tightly against the opening of the first pipe to stop.
因此，本发明具有如下有益效果：一方面，可实时检测病患的实际颅内压，方便医护人员及时调整医疗措施，另一方面，可实现自主模式的反馈性分流，以便使病患的颅内压稳定在设定水平。Therefore, the present invention has the following beneficial effects: on the one hand, the actual intracranial pressure of the patient can be detected in real time, which is convenient for medical staff to adjust medical measures in time; The internal pressure is stabilized at the set level.
附图说明Description of drawings
图1是实施例1的一种结构示意图。Fig. 1 is a kind of structural schematic diagram of
图2是实施例1各部件的电连接示意图。FIG. 2 is a schematic diagram of the electrical connections of the components in
图3是实施例1分流泵的压力曲线图。Fig. 3 is a pressure curve diagram of the shunt pump of
图4是实施例1中体位传感单元的功能示意图。FIG. 4 is a functional schematic diagram of the body position sensing unit in
图5是实施例2的一种结构示意图。FIG. 5 is a schematic structural view of
图6是实施例2的另一种结构示意图。FIG. 6 is another structural schematic diagram of
图7是实施例2测压分管的一种结构示意图。Fig. 7 is a schematic structural view of the pressure measuring sub-pipe in
图8是实施例2磁感应线圈的一种结构示意图。Fig. 8 is a schematic structural view of the magnetic induction coil in
图9是实施例2压力传感控制单元的一种结构示意图。Fig. 9 is a schematic structural diagram of the pressure sensing control unit in
图10是实施例2泄压管的一种结构示意图。Fig. 10 is a schematic structural view of the pressure relief pipe in
图中：1、主分流管 11、吸液端 12、出液端 2、分流泵 3、次分流管 31、分流阀 4、测压分管 41、受压腔 42、承压腔 43、检测段 431、施压腔 432、泄压腔 5、磁铁柱 51、滑动块 52、压力柱 521、感应端 6、磁感应线圈 61、支架 62、线圈 7、泄压管 71、第一管 72、第二管 8、单向阀 81、硅胶膜片 9、压力传感控制单元。In the figure: 1,
具体实施方式Detailed ways
下面结合附图与具体实施方式对本发明做进一步的描述。The present invention will be further described below in conjunction with the accompanying drawings and specific embodiments.
实施例1：如图1-图4所示，一种脑积水分流装置，包括脑室压力检测单元，所述脑室压力检测单元一端为连接闹市的压力传感器，另一端通过压电陶瓷单相水泵连通腹腔，当然，所述脑室压力检测单元还包括控制电路，控制电路可进行体位检测并无线传输信号。另外，所述脑室压力检测单元还包括高密度电池模块，以便为脑室压力检测单元提供电能；电池充电模块，以便为高密度电池模块充电；IMU体位检测，以检测体位。Embodiment 1: As shown in Figures 1-4, a hydrocephalus diversion device includes a ventricular pressure detection unit. One end of the ventricular pressure detection unit is a pressure sensor connected to a downtown, and the other end is passed through a piezoelectric ceramic single-phase water pump. It is connected to the abdominal cavity. Of course, the ventricular pressure detection unit also includes a control circuit, which can detect the body position and transmit signals wirelessly. In addition, the cerebroventricular pressure detection unit also includes a high-density battery module to provide electrical energy for the cerebroventricular pressure detection unit; a battery charging module to charge the high-density battery module; and an IMU body position detection to detect body position.
使用时，当压力检测单元检测到的颅内压大于等于某一值时，控制电路使压电陶瓷单相水泵启动，从而通过将颅内脑积水分流到腹腔，有效的避免分流不畅情况的出现，有利于使病患的颅内压稳定在设定水平。When in use, when the intracranial pressure detected by the pressure detection unit is greater than or equal to a certain value, the control circuit will start the piezoelectric ceramic single-phase water pump, thereby effectively avoiding the poor flow of the intracranial hydrocephalus by diverting the intracranial hydrocephalus to the abdominal cavity The emergence of , is conducive to the stability of the patient's intracranial pressure at the set level.
需要说明的是，脑室压力检测单元应优选地植入体内，以避免脑部受到污染，因此，在使用过程中需要通过电池充电模块为高密度电池模块及时充电。It should be noted that the ventricle pressure detection unit should preferably be implanted in the body to avoid contamination of the brain. Therefore, the high-density battery module needs to be charged in time by the battery charging module during use.
实施例2：如图5-图10所示，一种脑积水分流装置，包括主分流管1，所述主分流管一端为位于脑室内的吸液端11，另一端为位于腹腔内的出液端12，还包括脑积水处理单元，所述脑积水处理单元包括可感测控制颅内压的压力传感控制单元9、设置在主分流管上的分流泵2、以及中央控制电路（图中未示出）。使用时，可先通过中央控制电路设置合适的分流压力P，当压力传感控制单元检测到的颅内压P1大于等于设定的分流压力P时，中央控制电路使分流泵启动，从而通过主分流管将颅内脑积水分流到腹腔，有效的避免分流不畅情况的出现，有利于使病患的颅内压稳定在设定水平。优选地，分流泵可采用压电陶瓷水泵。Embodiment 2: As shown in Figures 5-10, a hydrocephalus shunt device includes a
此外，压力传感控制单元可实时监测颅内压，一方面，当压力传感控制单元检测到的颅内压P1大于等于设定的分流压力P时，中央控制电路可使分流泵启动分流；另一方面，便于医护人员实时了解掌握病患的颅内压状态，以便根据症状随时调整分流量和治疗方案。In addition, the pressure sensing control unit can monitor the intracranial pressure in real time. On the one hand, when the intracranial pressure P1 detected by the pressure sensing control unit is greater than or equal to the set shunt pressure P, the central control circuit can enable the shunt pump to start the shunt; On the other hand, it is convenient for medical staff to understand the intracranial pressure status of patients in real time, so as to adjust the shunt flow and treatment plan at any time according to the symptoms.
需要说明的是，本发明的脑积水分流装置应优选地植入体内，以避免脑部受到污染，因此，本发明还包括可无线充电的电池模块、可为电池模块无线充电的电池充电，当然，电池模块的体积越小越好，因此在使用过程中需要及时充电。由于此类小功率的无线充电电池、电池充电均属于现有技术，在此不做详细的描述。It should be noted that the hydrocephalus diversion device of the present invention should preferably be implanted in the body to avoid contamination of the brain. Therefore, the present invention also includes wirelessly chargeable battery modules and battery chargers that can wirelessly charge the battery modules. Of course, the smaller the battery module, the better, so it needs to be charged in time during use. Since such low-power wireless rechargeable batteries and battery charging belong to the prior art, no detailed description will be given here.
作为一种优选方案，如图2所示，所述主分流管上还并联有次分流管3，所述次分流管上设有分流阀31，需要说明的是，分流阀为启动压力等于P2的泄压阀，也就是说，次分流管类似于现有的被动式分流管。这样，即使主分流管因分流泵等元件出现故障等造成无法分流的极端情况时，次分流管也可作为应急分流通道而分流，避免出现完全无法分流的情况。可以理解的是，由于此处的次分流管只是作为主分流管的备份，因此，不会出现因长时间分流导致的堵塞等现象，进而可大大提升分流的可靠性和稳定性。As a preferred solution, as shown in Figure 2, the main shunt pipe is also connected in parallel with a
我们知道，正常的颅内压有一个大致在80-180mmH2O之间的范围，为此，我们将允许的颅内压最高值设为P3，分流阀的启动压力设为P2，并确保P＜P2≤P3。也就是说，次分流管上分流阀的启动压力P2要大于设定的分流压力P，因此，可确保主分流管相比较次分流管优先分流，并且次分流管上分流阀的启动压力P2要小于允许的颅内压最高值P3，避免因分流不及时导致的病患颅内压过高。由于现有包括分流阀的分流管属于现有技术，本发明的次分流管可参考借鉴现有分流管的技术，在此同样不做详细的描述。We know that the normal intracranial pressure has a range of approximately 80-180mmH2 O, so we set the maximum allowable intracranial pressure as P3, the start pressure of the shunt valve as P2, and ensure that P <P2≤P3. That is to say, the actuation pressure P2 of the diverter valve on the sub-distributor is greater than the set diversion pressure P, therefore, it can be ensured that the main diverter is preferentially diverted compared with the sub-divider, and the actuation pressure P2 of the diverter valve on the sub-divider must be Less than the maximum allowable intracranial pressure P3, to avoid excessive intracranial pressure in patients caused by untimely shunt. Since the existing shunt pipe including the shunt valve belongs to the prior art, the secondary shunt pipe of the present invention can refer to the technology of the existing shunt pipe, and will not be described in detail here.
作为另一种优选方案，如图2、图3所示，所述压力传感控制单元包括一端与主分流管的吸液端连通的测压分管4，测压分管的另一端封闭，在测压分管内设有可移动的磁铁柱5，磁铁柱在测压分管内分隔出靠近吸液端的受压腔41、靠近封闭端的承压腔42，在测压分管外设有可轴向移动的磁感应线圈6。As another preferred solution, as shown in Fig. 2 and Fig. 3, the pressure sensing control unit includes a pressure measuring
当颅内压升高时，测压分管内的受压腔压力同步上升，从而驱动磁铁柱向承压腔一侧移动，此时，测压分管外的磁感应线圈在移动的磁铁柱磁场作用下产生相应的电信号，即可感测颅内压。When the intracranial pressure rises, the pressure of the pressure chamber in the pressure measuring tube rises synchronously, thereby driving the magnet column to move to the side of the pressure chamber. At this time, the magnetic induction coil outside the pressure measuring tube is under the action of the magnetic field of the moving magnet column Generate corresponding electrical signals to sense intracranial pressure.
可以理解的是，当磁铁柱向承压腔一侧移动时，封闭的承压腔内的空气压力会线性的逐步上升，也就是说，承压腔的空气所形成的阻力类似于弹簧的弹力，其力的大小和磁铁柱的移动距离成正比。当然，我们可在测压分管上标注相应的压力值数据，以便于医护人员正确地观察颅内压力P1。It can be understood that when the magnet column moves to the side of the pressure chamber, the air pressure in the closed pressure chamber will gradually increase linearly, that is to say, the resistance formed by the air in the pressure chamber is similar to the elastic force of a spring , the magnitude of its force is proportional to the moving distance of the magnet column. Of course, we can mark the corresponding pressure value data on the manometry branch, so that the medical staff can correctly observe the intracranial pressure P1.
需要说明的是，由于磁感应线圈在测压分管外是可轴向移动的，因此，通过调节磁感应线圈在测压分管外的位置，即可方便地调节颅内压P1的测量精度。It should be noted that since the magnetic induction coil can move axially outside the pressure measuring tube, the measurement accuracy of the intracranial pressure P1 can be adjusted conveniently by adjusting the position of the magnetic induction coil outside the pressure measuring tube.
当然，此处的磁铁柱是一个具有磁性、并且和测压分管形成类似活塞和缸体的可移动连接关系的构件。Of course, the magnet column here is a component that has magnetism and forms a movable connection relationship with the pressure measuring branch tube similar to a piston and a cylinder.
此外，我们可去除病患脑壳内的一块“无用”的颅骨，以便“腾出空间”将本发明的脑积水分流装置部分构件植入病患的大脑内。In addition, we can remove a piece of "useless" skull in the patient's braincase to "make room" for implanting some components of the hydrocephalus shunt device of the present invention in the patient's brain.
进一步地，如图4所示，所述磁感应线圈包括螺接在测压分管外的支架61，绕设在支架上的若干线圈62，所述线圈在测压分管的轴向上等间距分布。这样，我们可通过中央控制电路先设定好分流压力P。当颅内压逐渐上升时，磁铁柱会向着承压腔一侧移动；当颅内压升高至设定的分流压力P时，磁铁柱向承压腔一侧移动至对应的线圈位置，该线圈即可输出一个代表颅内压P1的电信号，此时该颅内压P1即等于分流压力P。可以理解的是，在磁铁柱向承压腔一侧移动而经过前面的线圈时，同样会相应地输出一个小于分流压力P的颅内压P1，此时的中央控制电路不会启动分流泵工作。为了便于观察，所述测压分管以及支架优选地可采用透明塑料制成。Further, as shown in FIG. 4 , the magnetic induction coil includes a
当然，我们可通过转动支架、以使磁感应线圈轴向移动，继而调教压力传感控制单元的准确性。Of course, we can adjust the accuracy of the pressure sensing control unit by rotating the bracket to move the magnetic induction coil axially.
由于本发明使用时优选地需要被植入病患体内，此时医护人员难以及时观察、了解颅内压P1的实际数据。为了实时显示压力传感控制单元检测到的颅内压P1，本发明还包括可无线接收颅内压信号并显示的无线信号接收装置，当颅内压升高、磁铁柱移动至与其中一个线圈对应时，该线圈即可因切割磁力线而产生电流，继而产生一个代表对应颅内压P1的磁信号，无线信号接收装置接收该信号后即可显示颅内压P1。Since the present invention preferably needs to be implanted into the patient's body, it is difficult for medical staff to observe and understand the actual data of the intracranial pressure P1 in time. In order to display the intracranial pressure P1 detected by the pressure sensing control unit in real time, the present invention also includes a wireless signal receiving device that can wirelessly receive and display the intracranial pressure signal. When the intracranial pressure rises, the magnet column moves to one of the coils When corresponding, the coil can generate current by cutting the magnetic force line, and then generate a magnetic signal representing the corresponding intracranial pressure P1, and the wireless signal receiving device can display the intracranial pressure P1 after receiving the signal.
由于此类无线信号传输原理及装置已经在现有技术中有广泛的应用，本实施例中同样不做详细的描述。Since such wireless signal transmission principles and devices have been widely used in the prior art, no detailed description will be given in this embodiment.
为了提升压力传感控制单元的灵敏度，如图5所示，所述测压分管包括直径外扩的检测段43，所述磁铁柱包括位于检测段内的滑动块51，滑动块在检测段内分隔出靠近吸液端的施压腔431、靠近封闭端的泄压腔432，滑动块靠近承压腔一侧设有位于测压分管内的压力柱52，压力柱的端部为具有磁性的感应端521，所述磁感应线圈设置在靠近承压腔一侧的测压分管上。也就是说，检测段和靠近承压腔一侧的测压分管之间形成阶梯。可以理解的是，由于滑动块的直径大于压力柱的直径，因此滑动块的面积大于压力柱的面积。当颅内压升高时，其压力会作用在面积较大的滑动块上，继而可驱动滑动块的移动，相反地，位于测压分管内的压力柱由于面积较小，所承受的空气阻力也较小。因此，当颅内压有微小的变化时，即可导致压力柱较大的轴向移动，有利于提升颅内压的检测精度。In order to improve the sensitivity of the pressure sensing control unit, as shown in Figure 5, the pressure measuring sub-pipe includes a
优选地，我们可使滑动块的直径为压力柱直径的2-3倍，从而使两者之间的面积之比为4-9，继而使磁铁柱对颅内压有一个力的放大作用，确保磁铁柱的灵活移动。Preferably, we can make the diameter of the sliding block 2-3 times the diameter of the pressure column, so that the ratio of the area between the two is 4-9, and then the magnet column has a force amplification effect on the intracranial pressure, Ensure the flexible movement of the magnet post.
可以理解的是，当磁铁柱向承压腔一侧移动时，封闭的泄压腔内的空气压力也会逐渐上升，从而对滑动块的移动形成阻力，为此，我们可在施压腔和泄压腔之间设置包括单向阀8的泄压管7，当泄压腔内的空气压力上升时，可通过泄压管泄压回流到施压腔内，从而消除泄压腔内的气体对滑动块形成的阻力。当然，其中的单向阀应为从泄压腔至施压腔正向导通，从而避免颅内压通过泄压管泄压而无法驱动磁铁柱移动。It can be understood that when the magnet column moves to the side of the pressure chamber, the air pressure in the closed pressure relief chamber will gradually rise, thereby forming resistance to the movement of the sliding block. A
为了尽量缩小单向阀的外形尺寸，并确保其具有足够的灵敏度，如图6所示，所述泄压管包括与泄压腔连通的第一管71、与施压腔连通的第二管72，第二管套接在第一管外面，也就是说，第二管的管径大于第一管的管径，以方便第一关于第二管的装配连接。此外，所述单向阀包括硅胶膜片81，所述硅胶膜片一侧（大致占开口周长的1/4）粘结在第一管上与第二管连接的开口处、并贴靠开口。这样，当第二管相对第一管形成正向压力时，所述硅胶膜片会更加紧密贴靠第一管开口，此时的泄压管处于正向截止状态；当第一管相对第二管形成反向压力时，所述硅胶膜片部分地离开第一管开口，此时的泄压管处于反向导通状态。In order to minimize the size of the check valve and ensure that it has sufficient sensitivity, as shown in Figure 6, the pressure relief pipe includes a
当然，所述第一管、第二管可谓圆管，也可为方管。Of course, the first tube and the second tube can be called round tubes or square tubes.
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