A cutting and coagulation system based on blood vessel monitoring

Abstract

The present application relates to a cutting and coagulation system based on blood vessel monitoring, the system comprising at least a processing unit, a light source emitting unit and a light source receiving unit. The light source receiving unit receives the light emitted by the light source emitting unit after being absorbed and reflected by the blood vessel or tissue to form light information. The processing unit determines the blood flow speed and blood volume in the blood vessel of the patient based on the light information and controls the output power of the high-frequency cutter head assembly. In the present application, for the cutting or coagulation of the blood vessel of the patient, especially for the case that the patient has different blood vessel positions and blood vessel toughness, how to apply appropriate cutting or coagulation to the patient without damaging the remaining tissues of the patient is a problem that needs to be solved in the prior art. In the present application, through the non-external light signal detection components, the contact surface directly contacting the patient's tissue or blood vessel is used as the light path, which is conducive to the absorption of specific wavelength light by the blood, and the detection of the blood flow speed and flow of the patient is realized.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to a cutting and coagulation system based on vascular monitoring. Background Technology

[0002] High-frequency electrosurgical units are typically used for cutting patient tissue or for hemostasis. While they produce clean, non-bleeding cuts, they can cause local tissue blood supply obstruction, tissue cell damage, partial tissue carbonization, and fat liquefaction. High-frequency electrosurgical units apply high-frequency, high-voltage current to the affected area through electrodes, cauterizing and cutting tissue to remove lesions or achieve hemostasis, thus achieving either cutting (tissue separation) or coagulation (blood or tissue fluid). However, currently used or existing high-frequency electrosurgical units still have certain limitations in their application.

[0003] First, before performing actual tissue cutting with a conventional high-frequency electrosurgical unit, medical personnel need to assess the distribution of blood vessels in the tissue to be cut to avoid cutting the patient's arteries. The drawback of this method is that if the medical personnel make a mistake in their assessment, it can easily lead to massive bleeding, thus prolonging the operation time and affecting its efficiency. Second, the output power of a conventional high-frequency electrosurgical unit is entirely controlled by the medical personnel based on their experience. Therefore, for medical personnel lacking relevant experience, accurately controlling the output power is difficult. If inexperienced medical personnel apply too much output power when operating the high-frequency electrosurgical unit, it may cause irreversible damage to the patient's tissue. Even experienced medical personnel, when treating different patients, may cause tissue damage by adjusting the output power based on past experience due to individual differences in tissue thickness and toughness.

[0004] For example, Chinese patent application CN 115645029A discloses a high-frequency electrosurgical device with an electrode conduction structure, which includes a handle, an electrode conduction tube, and a high-frequency electrosurgical device. The electrode conduction tube includes a support tube mounted on the handle, a movable conductive tube sleeved on the support tube, a fixed spring plate relatively fixed to the support tube, and a conductive spring plate connected to the movable conductive tube. The movable conductive tube can move on the support tube. The high-frequency electrosurgical device is connected to the movable conductive tube. The fixed spring plate is used to connect to the electrodes of the power supply. When the movable conductive tube moves to any position on the support tube, the conductive spring plate remains in contact with the fixed spring plate, thereby connecting the high-frequency electrosurgical device to the power supply. The high-frequency electrosurgical device can rotate and extend relative to the handle with the cooperation of the movable conductive tube and the support tube, and can be connected to the power supply in any posture. This replaces the existing technology of conducting electricity by welding wires, and has advantages such as long service life and easy assembly. The high-frequency electrosurgical unit proposed in this patent relies entirely on the experience of medical personnel to control its output power. Therefore, for medical personnel lacking relevant experience, it is difficult to accurately control the output power, which may cause irreversible damage to the patient's tissues.

[0005] Chinese patent application CN 112545641A discloses a high-frequency electrosurgical unit, including a sheath, a first electrode, an insulating connector, and a second electrode. The first electrode is connected to the distal end of the sheath and can extend and retract along the axial direction of the sheath. The insulating connector is connected to the distal end of the first electrode. The second electrode is conductively connected to the distal end of the first electrode, and at least a portion of the second electrode is located at the distal end of the insulating connector. The resistance of the second electrode is greater than that of the first electrode. In this embodiment of the high-frequency electrosurgical unit, when the first electrode is extended, it can cut human tissue, while the second electrode can directly contact the human tissue without causing harm. When the first electrode is retracted, it does not contact the human body, and the second electrode can perform a marking operation. This allows the high-frequency electrosurgical unit to perform both cutting and marking functions. Furthermore, the function switching can be achieved through the extension and retraction of the first electrode. The structure is simple and the operation is convenient. However, the patent has a drawback: it can only perform marking operations through the second electrode, but it cannot determine the distribution of blood vessels in the tissue to be cut. This makes it easy for medical personnel to cut the patient's blood vessels during the cutting process using the high-frequency electrosurgical unit, causing massive bleeding in the patient, thereby prolonging the operation time and affecting the efficiency of the operation.

[0006] Furthermore, on the one hand, there are differences in understanding among those skilled in the art; on the other hand, the applicant studied a large number of documents and patents when making this invention, but due to space limitations, not all details and contents were listed in detail. However, this does not mean that the present invention does not possess the features of these prior art. On the contrary, the present invention already possesses all the features of the prior art, and the applicant reserves the right to add relevant prior art to the background art. Summary of the Invention

[0007] Existing high-frequency electrosurgical techniques may damage tissues or blood vessels, leading to necrosis, infection, or scarring. This is especially true for fragile tissues such as the skin and intestines, where secondary damage is highly likely. This depends heavily on the medical personnel's cutting experience and judgment of blood vessel distribution. At least part of these problems arise from abnormal bleeding caused by incorrect identification of blood vessel locations. Therefore, how to properly cut or coagulate blood vessels, especially in patients with varying vessel locations and resilience, without damaging other tissues, is a pressing issue that current technologies urgently need to address.

[0008] To address the shortcomings of existing technologies, this invention provides a cutting and coagulation system based on vascular monitoring, comprising at least a contact mechanism for cutting tissue or coagulating blood vessels. The system also includes a processing unit and a light source emitting unit and a light source receiving unit disposed on the contact mechanism. The light source emitting unit emits light to the contact area of ​​the blood vessel or tissue. The light source receiving unit receives the light absorbed and reflected by the blood vessel or tissue to form light information and sends the light information to the processing unit. Preferably, the processing unit is configured to: determine the blood flow velocity and blood volume within the blood vessel based on the spectral information image generated from the light information; determine the distribution of blood vessels based on the blood flow velocity and blood volume; and control the output power of the high-frequency blade assembly of the contact mechanism. This invention, through non-external optical signal detection components, uses the contact surface that directly contacts the patient's tissue or blood vessel as the light path, facilitating the absorption of specific wavelengths of light by the blood, thereby achieving the detection of the patient's blood flow velocity and volume. This avoids the need for extensive scanning of the patient's body using numerous existing external detection methods, reducing the need for more expensive, bulkier, and complex angiography equipment to assist in vascular monitoring. This invention achieves optimal surgical results through simple light transmission and reception and data processing.

[0009] According to a preferred embodiment, the step of the processing unit determining the blood flow velocity and blood volume in a patient's blood vessels based on a spectral information image generated from light information includes at least: determining the blood flow velocity in the patient's blood vessels based on waveform changes caused by the absorption of light emitted by the light source emitting unit by the blood; acquiring the spectrum of the light based on the light information to generate a spectral information image; and determining the blood volume in the blood vessels based on changes in the absorption peaks of the reflected light in the spectral information image. When contacting a patient's blood vessels or tissue through a contact mechanism, by activating the light source emitting unit and the light source receiving unit of this invention, the blood flow velocity in the patient's blood vessels can first be determined by the waveform changes caused by the absorption of light of a specific wavelength by the blood, and the blood volume can also be accurately or approximately determined based on changes in the absorption peaks. Compared to tissue cutting achieved by conventional high-frequency electrosurgical units, the system of this application can accurately determine the distribution of blood vessels under the tissue to be cut.

[0010] According to a preferred embodiment, the step of the processing unit determining the blood flow velocity within a patient's blood vessels based on waveform changes caused by the absorption of light emitted by the light source emitting unit by the blood includes at least: acquiring spectral information images of adjacent light source receiving units; and calculating the blood flow velocity within the patient's blood vessels based on the waveform delay of the spectral information images. The blood flow velocity calculated in this manner accurately reflects the condition of the blood vessels at the site to be cut, facilitating real-time monitoring of the vessels at that location by medical personnel. It also helps in determining the cutting position of the contact mechanism, preventing hemostasis complications such as thrombosis. Furthermore, this calculation method is simple, enables rapid calculation of blood flow velocity, improves hemostasis efficiency, and reduces processing delays during software operation.

[0011] According to a preferred embodiment, the step of the light source receiving unit receiving light after absorption and reflection by blood vessels or tissue to form light information includes at least: light emitted by the light source emitting unit is absorbed by hemoglobin in the blood and reflected to the light source receiving unit; the light source receiving unit acquires the waveform of the reflected light after reflection by blood vessels or tissue to form light information reflecting the amount of light absorption. This invention achieves the detection of blood in blood vessels through various optical signal detection components, simplifying the acquisition process as much as possible, thus eliminating the need for significant improvements to existing equipment. Complete light information analysis yields the distribution of blood vessels at the site to be cut, as well as the blood flow rate and velocity within them. The acquisition of light signals fully utilizes the special properties of hemoglobin in the blood, eliminating the need for manual operation by medical personnel. Accumulated data can form large datasets, thereby predicting the probability of bleeding in patients, improving hemostasis efficiency, and reducing the occurrence of complications.

[0012] According to a preferred embodiment, the step of the processing unit controlling the output power of the high-frequency blade assembly of the contact mechanism based on blood flow velocity and blood volume includes at least: controlling the output power of the high-frequency blade assembly of the contact mechanism based on blood volume and blood flow velocity; and controlling the output power of the high-frequency blade assembly of the contact mechanism based on blood flow acceleration. The high-frequency blade assembly configured in the above manner has a certain marginal effect in its output power, accelerating the coagulation process while avoiding damage to patient tissues.

[0013] According to a preferred embodiment, the processing unit is further configured to select the mode of the light source emitting unit based on changes in blood flow velocity and blood volume. Preferably, the processing unit sends a control signal to switch the light source emitting unit to a dynamic mode that emits intermittent light or a static mode that emits continuous light. Existing high-frequency electrosurgical procedures lack vascular monitoring of the tissue to be cut, leading to dangerous situations such as massive bleeding during subsequent cutting. The different modes provided by this invention are precisely to address the above problems. This invention indirectly monitors changes in the patient's blood flow velocity and blood volume by acquiring light information; however, the small size of the high-frequency electrosurgical unit prevents the light source emitting unit and light source receiving unit from being equipped with large batteries or power supply components, thus not supporting long surgical procedures. Therefore, in the initial use of the contact mechanism of this invention, a static mode can be used, i.e., continuous monitoring of the patient's blood is achieved through continuous light emission. After determining the cutting position, it switches to a dynamic mode to reduce the energy consumption of the light source emitting unit by emitting light intermittently, thereby supporting long surgical procedures. Furthermore, the dynamic mode can prevent the effects of specific wavelengths of light on the patient's body.

[0014] According to a preferred embodiment, the contact mechanism is provided with a hollow channel, in which the high-frequency cutter head assembly slides, and the high-frequency cutter head assembly can partially extend out of the first contact portion and the second contact portion. The high-frequency cutter head assembly configured in the above scheme can function as a push-out high-frequency electrosurgical unit, performing corresponding cutting or coagulation after monitoring the patient's vascular system. This invention can be used to identify vascular structures buried under the patient's solid tissue, thereby enabling subsequent clear cutting and achieving safety in the high-frequency electrosurgical cutting process.

[0015] According to a preferred embodiment, the light source emitting unit and the light source receiving unit within the first and second contact portions are arranged with their emitting and receiving surfaces close to the patient's contact area. The emitting and receiving surfaces of the light source emitting unit and the light source receiving unit have the same thickness as the first contact portion in a third direction. This ensures that the blood in the blood vessels within the contact area is accurately measured, preventing situations where insufficient measurement leads to the processing unit identifying a blood volume of 0 even when some blood is actually flowing. This improves the accuracy of blood volume identification and further enhances the precision of pressure control.

[0016] According to a preferred embodiment, light source emitting units and light source receiving units are arranged at intervals within a first contact portion and a second contact portion, with a fixed distance between adjacent light source emitting units and light source receiving units. Preferably, the processing unit is further configured to calculate the blood flow velocity within the patient's blood vessel based on the distance between adjacent light source emitting units and light source receiving units and the converted spectral information image. This invention calculates the patient's blood flow acceleration by measuring the distance between adjacent light source emitting units and light source receiving units, thereby adjusting the output power of the high-frequency blade assembly. When a rapid increase in blood flow occurs at the patient's blood vessel, this invention increases the output power of the high-frequency blade assembly to achieve rapid hemostasis during the subsequent coagulation process.

[0017] According to a preferred embodiment, in the case of secondary tissue cutting, the processing unit is further configured to: set the historical vessel location and the output power of the high-frequency blade assembly during the first cutting as reference values, and adjust the output power of the high-frequency blade assembly. The present invention provides the historical vessel location and the output power of the high-frequency blade assembly, and can also verify the vessel location and the output power of the high-frequency blade assembly by measuring the blood volume within the vessel using the light source emitting unit and the light source receiving unit. Attached Figure Description

[0018] Figure 1 This is a simplified planar structural diagram of a cutting and coagulation system based on vascular monitoring, according to a preferred embodiment of the present invention.

[0019] Figure 2 This is a partially enlarged structural schematic diagram of the contact mechanism according to a preferred embodiment of the present invention;

[0020] Figure 3 This is a simplified schematic diagram of the module connection relationship of a cutting and coagulation system based on vascular monitoring, according to a preferred embodiment of the present invention.

[0021] List of reference numerals

[0022] 100: Contact mechanism; 200: Holding mechanism; 110: First contact part; 120: Second contact part; 111: Light source emitting unit; 112: Light source receiving unit; 210: Processing unit; 220: High-frequency cutter head assembly; 230: Control module; 240: Holding part; 250: Limiting member; X: First signal; Y: Second signal. Detailed Implementation

[0023] The following is a detailed explanation with reference to the accompanying drawings.

[0024] Example 1

[0025] This invention relates to a cutting and coagulation system based on vascular monitoring, and particularly to an apparatus, system, and method for determining the cutting or coagulation location and coagulation effect based on the reflection of light beams from blood vessels. The system includes at least a contact mechanism 100 and a holding mechanism 200. The contact mechanism 100 is used for cutting tissue or coagulating blood vessels. The holding mechanism 200 is used for holding the contact mechanism 100. Preferably, a first contact portion 110 and a second contact portion 120 are arranged in parallel on the distal end of the contact mechanism 100 near the patient. Preferably, the system further includes a processing unit 210 disposed within the holding mechanism 200. Preferably, the processing unit 210 is capable of calculating the light parameters emitted by the first contact portion 110 and the second contact portion 120. Preferably, at least a plurality of light source emitting units 111 that emit light beams to the contact area with the patient and light source receiving units 112 matched with the light source emitting units 111 are disposed on the first contact portion 110 and the second contact portion 120. Preferably, the light source receiving unit 112 receives the light information absorbed and reflected by the patient's contact area and sends it to the processing unit 210. Processing unit 210 generates a spectral information image based on the light information acquired by light source receiving unit 112 and determines whether blood vessels exist at the patient's contact site and the amount of blood within the vessels based on the spectral information image. Processing unit 210 controls the signal coordination and data transmission of the remaining units. Communication between processing unit 210 and light source receiving unit 112 can be wireless. Light source emitting unit 111 can be a light-emitting diode or a laser diode. Light source emitting unit 111 emits light of a specific wavelength that can be absorbed by specific components in the patient's blood (e.g., hemoglobin). Light source receiving unit 112 can be a photosensitive element. When light source emitting unit 111 and light source receiving unit 112 are operating, light source emitting unit 111 emits light of a specific wavelength (660nm) (e.g., green light) that is easily absorbed by hemoglobin in the blood. The emitted light is absorbed by hemoglobin, and blood flow causes changes in blood density emission at that location. As blood density and flow change, the amount of light reflected also changes. After receiving the diffusely reflected light information from the patient's tissue, light source receiving unit 112 sends it to processing unit 210. After filtering, amplification, and analog-to-digital conversion, the processing unit 210 converts the light information into a spectral information image and uses it to determine the amount of blood in the blood vessels.

[0026] The aforementioned processing unit 210 may be a microcontroller unit, a central processing unit, a general-purpose processor, a digital signal processor, an application-specific integrated circuit, a field-programmable gate array, or other programmable logic devices, transistor logic devices, hardware components, or any combination thereof.

[0027] According to a preferred embodiment, the contact mechanism 100 and the holding mechanism 200 are connected. Preferably, a high-frequency blade assembly 220 is further provided inside the contact mechanism 100 and the holding mechanism 200. The high-frequency blade assembly 220 is a high-frequency electrosurgical unit. Medical personnel can use the high-frequency blade assembly 220 to cut the patient's tissue. In this invention, the high-frequency blade assembly 220 can be used to cut patient tissue or to prevent blood clotting during the cutting process. When medical personnel need to cut a patient's tissue, it is usually difficult for them to determine the condition of blood vessels inside the tissue to be cut. If surgery is performed rashly, it can easily lead to massive bleeding in the patient. If the patient's artery is cut, due to its large diameter, the high-frequency electrosurgical unit cannot clot blood in the artery, and may even endanger the patient's life. This invention uses a first contact portion 110 and a second contact portion 120 provided in the contact mechanism 100 to monitor whether blood vessels are distributed under the patient's tissue, and then the medical personnel determine the cutting position and cutting direction of the high-frequency blade assembly 220, thereby shortening the operation time and reducing the amount of blood loss and bleeding in the patient.

[0028] Preferably, the first contact portion 110 and the second contact portion 120 are disposed at the distal end of the contact mechanism 100. The first contact portion 110 and the second contact portion 120 form a structure with a cavity in the middle at the end of the contact mechanism 100. That is, the first contact portion 110 and the second contact portion 120 are connected end to end as a cylinder, a rectangle, or other structure with a cavity in the middle. The contact mechanism 100 and the holding mechanism 200 are provided with a hollow channel. The hollow channel is connected to the cavity formed by the first contact portion 110 and the second contact portion 120. Preferably, a high-frequency cutter head assembly 220 is disposed in the hollow channel. The high-frequency cutter head assembly 220 can slide freely in the hollow channel and can partially extend out of the first contact portion 110 and the second contact portion 120. A limiting member 250 is provided on the holding mechanism 200. The limiting member 250 restricts the movement of the high-frequency cutter head assembly 220 in the hollow channel by means of a slot, magnetic attraction, or threaded fixation. For example, the limiting member 250 is fixedly connected to the high-frequency blade assembly 220, thereby controlling the extension distance of the high-frequency blade assembly 220 by sliding it into slots with different scale distances. As another example, the limiting member 250 can be fixedly connected to the high-frequency blade assembly 220, thereby locking it at a certain position on the holding mechanism 200 via threads to restrict the movement of the high-frequency blade assembly 220. This locking method, for example, increases the pressure between the limiting member 250 and the holding mechanism 200, thereby increasing the friction between them to restrict the movement of the limiting member 250 itself and achieve locking of the high-frequency blade assembly 220. It should be noted that the distal end of this invention refers to the end farther from the surgeon, and the proximal end refers to the end closer to the surgeon.

[0029] The high-frequency cutting head assembly 220 configured as described above can function as an ejectable high-frequency electrosurgical unit, performing corresponding cutting or coagulation after monitoring the blood vessels in the patient's tissue. For example, medical personnel first restrict the high-frequency cutting head assembly 220 within the hollow channel using the limiting member 250, preventing it from contacting the patient's tissue. The medical personnel then contact the first contact portion 110 and the second contact portion 120 with the patient's tissue, obtaining information about the blood vessels at the contact location by transmitting and receiving light. If a blood vessel with high blood flow or velocity is detected at the contact location, the medical personnel change the cutting or coagulation location to reduce the patient's bleeding. If internal bleeding is detected within the patient's tissue, the medical personnel can also use the high-frequency cutting head assembly 220 to coagulate the affected area. Once the desired cutting location is determined, the medical personnel first release the locking of the high-frequency cutting head assembly 220 using the limiting member 250 and then eject the high-frequency cutting head assembly 220 from the hollow channel to cut the patient's tissue. The ejection distance is suitable for cutting the tissue. Medical personnel then use the limiting component 250 to lock the extension distance, thereby performing the cut at the determined desired cutting position. This invention can be used to identify vascular structures buried under the patient's solid tissue, thereby enabling subsequent clear cutting and ensuring the safety of the high-frequency electrosurgical cutting process.

[0030] According to a preferred embodiment, the light source emitting unit 111 and the light source receiving unit 112 within the first contact portion 110 and the second contact portion 120 are arranged with their emitting and receiving surfaces close to the patient's contact area. Several pairs of paired light source emitting units 111 and light source receiving units 112 are arranged along the extending direction of the first contact portion 110. The emitting and receiving surfaces of the light source emitting unit 111 and the light source receiving unit 112 have the same thickness as the first contact portion 110 in a third direction, ensuring accurate measurement of blood in the blood vessels within the contact area. This avoids situations where insufficient measurement leads to the processing unit 210 identifying a blood volume of 0 even when some blood is actually flowing, thus improving the accuracy of blood volume recognition and further enhancing the precision of pressure control. In this invention, the first direction is set as the length extension direction of the first contact portion 110 and the second contact portion 120, the second direction is set as a direction perpendicular to the first direction on the plane where the length extension directions of the first contact portion 110 and the second contact portion 120 are located, and the third direction is set as a direction perpendicular to the plane where the length extension directions of the first contact portion 110 and the second contact portion 120 are located.

[0031] According to a preferred embodiment, light source emitting units 111 and light source receiving units 112 are arranged at intervals within the first contact portion 110 and the second contact portion 120. Preferably, the distance between each pair of light source emitting units 111 and light source receiving units 112 is fixed, thereby obtaining the direction of blood flow in the patient. Preferably, the processing unit 210 calculates the blood flow velocity and changes carrying hemoglobin based on the distance between each pair of light source emitting units 111 and light source receiving units 112 and the converted spectral information image. The light source emitting unit 111 on the first contact portion 110 emits green light that can be absorbed by hemoglobin in the blood. The green light emitted by the light source emitting unit 111 is partially absorbed. The unabsorbed green light is scattered and / or reflected and then acquired by the light source receiving unit 112 to form light information that can reflect the amount of light absorption. The processing unit 210 determines the amount of blood in the patient's contact area based on the amount of light absorption in the spectral information image. The processing unit 210 compares the spectral image emitted by the light source emitting unit 111 with the spectral information image acquired by the light source receiving unit 112 to determine the light absorption and thus estimate the blood volume. Preferably, the processing unit 210 also calculates the blood flow velocity and its changes within the patient's blood vessels based on the difference between each pair of light source emitting units 111 and light source receiving units 112.

[0032] Specifically, the processing unit 210 acquires light information from two adjacent light source receiving units 112. This light information contains the waveform of reflected light collected by the light source receiving unit 112. The processing unit 210 calculates the blood flow velocity within the patient's blood vessels based on the time delay between two adjacent waveforms. Since several light source receiving units 112 are arranged sequentially at intervals on the first contact portion 110, and the distance between two adjacent light source receiving units 112 is known, the blood flow velocity between two adjacent light source receiving units 112 can be obtained. That is, by detecting the flow direction of the same hemoglobin group in the blood vessel, the blood flow velocity is calculated based on the time difference between the arrival of the hemoglobin group at several light source receiving units 112. For example, the processing unit 210 acquires light information from two adjacent light source receiving units 112. This light information contains the first moment when the reflected light waveform acquired by one light source receiving unit 112 reaches its peak value in a certain period, and the second moment when the reflected light waveform acquired by the other adjacent light source receiving unit 112 reaches its peak value in a certain period. Thus, the processing unit 210 obtains the time delay between the two adjacent waveforms through the difference between the first moment and the second moment. According to the velocity formula, the blood flow velocity within the blood vessel is the distance between two adjacent light source receiving units 112 divided by the time delay of two adjacent waveforms. Preferably, the processing unit 210 calculates the blood flow velocity within the blood vessel in contact with the first contact portion 110 based on the waveform time delay and distance between different light source receiving units 112. The light source emitting unit 111 and the light source receiving unit 112 on the second contact portion 120 operate on the same principle and will not be described again.

[0033] The processing unit 210 also acquires the spectrum of the light based on the light information, thereby obtaining a spectral information image. The light information includes the waveform collected by the light source receiving unit 112. The processing unit 210 obtains the spectrum of the waveform by filtering, amplifying, and performing analog-to-digital conversion on the waveform. The spectral information image characterizes the state of hemoglobin flow through the detection location in the patient's blood vessels, thereby indirectly reflecting the blood volume at the detection location. The aforementioned detection location refers to the patient tissue location where the light source emitting unit 111 and the light source receiving unit 112 are aligned.

[0034] Preferably, the processing unit 210 determines the blood volume at the detection location based on the change in the absorption peak of the reflected light in the spectral information image. The processing unit 210 is configured to determine the blood volume at the detection location based on the different distributions of the absorption peaks of the light emitted by the light source emitting unit 111 and the reflected light reflected from the blood in the patient's blood vessels. This determination method can be a fixed relationship expressed as a formula, function, or data table. For example, by integrating the relationship between the absorption peaks of light information from a typical patient and the blood volume, the basic formula, function, and data table for this determination method can be obtained. In this embodiment, how to apply appropriate cutting or clotting techniques to a patient's blood vessels, especially when the patient has different blood vessel locations and vascular toughness, without damaging other tissues, is a problem that the prior art urgently needs to solve. During the contact process of the contact mechanism 100 with the patient's blood vessels or tissues, by activating the light source emitting unit 111 and the light source receiving unit 112 of this invention, the blood flow velocity within the patient's blood vessels can first be determined by the waveform changes generated by the absorption of light of a specific wavelength by the blood, and the blood volume can also be accurately or approximately determined based on the changes in the absorption peaks. Compared to existing conventional high-frequency electrosurgical units (HFEMUs), the system in this application can accurately determine the distribution of blood vessels beneath the tissue to be cut. Existing HFEMUs often result in damage to the patient's blood vessels during the cutting process due to the difficulty for medical personnel to assess the underlying blood vessels. If medical personnel lack extensive cutting experience, the presence of large blood vessels at the cutting site can lead to excessive bleeding, causing significant harm to the patient and postoperative complications. Therefore, improving the accuracy of HFEMUs and rapidly determining the distribution of blood vessels, blood flow, and blood velocity beneath the tissue to be cut are crucial technical solutions. This invention incorporates an integrated optical signal detection component. By using the contact surface directly in contact with the patient's tissue or blood vessels as the light path, and utilizing the principle of absorption of specific wavelengths of light by blood components, it improves the accuracy of HFEM cutting and enables rapid detection of blood vessels, avoiding the need for more expensive angiography equipment to assist in cutting. This invention achieves optimal surgical results through simple light transmission and reception and data processing.

[0035] According to a preferred embodiment, a reflective layer formed by coating or vapor deposition is provided on the inner surfaces of the emitting and receiving surfaces of the light source emitting unit 111 and the light source receiving unit 112. The reflective layer is capable of reflecting specific light emitted by the light source emitting unit 111 and is fixedly guided to the removed patient tissue, preventing leakage from other directions.

[0036] According to a preferred embodiment, the processing unit 210 controls the output power of the high-frequency blade assembly 220 between the first contact portion 110 and the second contact portion 120 based at least on the blood volume. The high-frequency blade assembly 220 of the present invention is also used for coagulation of some blood vessels in the patient; that is, by contacting the bleeding site with the cauterizing high-frequency blade assembly 220, the cells at the bleeding site contract due to the thermal effect, thereby achieving hemostasis. Preferably, when the acquired blood volume is above a preset value, the processing unit 210 controls the high-frequency blade assembly 220 to perform coagulation with a higher output power. The aforementioned higher output power does not refer to the maximum output power of the high-frequency blade assembly 220, but rather to a higher output power capable of rapid coagulation without cutting tissue. Even when the first contact portion 110 and the second contact portion 120 are not in contact with the patient's site to be cut, the processing unit 210 can still make a fuzzy judgment of the amount of bleeding at the site to be cut based on scattered light. That is, during the process of extending the high-frequency blade assembly 220 to cut tissue, the processing unit 210 can make a fuzzy judgment of the amount of bleeding at the cutting location based on changes in light of a specific wavelength. The aforementioned fuzzy judgment refers to the ability to determine the range of bleeding volume with low precision. When the monitored bleeding volume decreases to a preset value, the processing unit 210 reduces the output power of the high-frequency blade assembly 220, thereby reducing the high-frequency current applied to the blood vessel. In other words, when the processing unit 210 determines that medical personnel have completed coagulation work through the high-frequency blade assembly 220, it reduces the output power of the high-frequency blade assembly 220 to avoid damage to other tissues of the patient. Even if medical personnel inadvertently perform continuous coagulation work, it will not cause damage to the patient's tissues. Preferably, the smaller the bleeding volume, the smaller the output power of the high-frequency blade assembly 220. In fact, the output power of the high-frequency blade assembly 220 is only higher at the beginning of coagulation because the patient has not yet stopped bleeding at this time. To accelerate the efficiency of hemostasis, coagulation is performed with a higher output power in the initial stage. The output power is reduced in the short time after contact to avoid damage to the patient's tissues.

[0037] Preferably, the processing unit 210 further controls the output power of the high-frequency blade assembly 220 based on the flow acceleration of the patient's blood. This flow acceleration can be derived from changes in blood flow velocity. Specifically, since several light source receiving units 112 are arranged sequentially at intervals on the first contact portion 110, and the distance between two adjacent light source receiving units 112 is known, based on the calculation of blood flow velocity within the blood vessel in the above embodiment, the processing unit 210 calculates the blood flow velocity within the patient's blood vessel through the time delay of two adjacent waveforms. The processing unit 210 obtains the blood flow velocity between the several light source receiving units 112. The processing unit 210 also obtains the blood flow velocity at the beginning and end of the displacement based on the blood flow direction. Preferably, the processing unit 210 obtains the flow acceleration based on the quotient of the difference between the blood flow velocity at the beginning and end of the displacement and the time delay of the waveforms at the beginning and end. Preferably, when the flow acceleration is too fast, the processing unit 210 controls the output power of the high-frequency blade assembly 220 to increase. That is, when a rapid increase in blood flow occurs at a particular blood vessel, it indicates a risk of significant bleeding. The processing unit 210 increases the output power of the high-frequency cutter head assembly 220 to achieve rapid hemostasis during the subsequent clotting process. It should be noted that the processing unit 210 controls the output power of the high-frequency cutter head assembly 220 based on both blood volume and flow acceleration. Specifically, when the blood volume calculated by the processing unit 210 is above a preset value, the processing unit 210 controls the high-frequency cutter head assembly 220 to preheat (preheating at a higher output power), and the processing unit 210 increases or decreases the output power of the high-frequency cutter head assembly 220 based on the flow acceleration. When the blood loss calculated by the processing unit 210 decreases to the preset value, the processing unit 210 decreases the output power of the high-frequency cutter head assembly 220.

[0038] To accelerate coagulation efficiency, this invention introduces blood flow acceleration to adjust the output power of the high-frequency blade assembly 220. This increases the output power of the high-frequency blade assembly 220 when a rapid increase in blood flow occurs at the patient's blood vessel, enabling rapid hemostasis during the subsequent coagulation process. The high-frequency blade assembly 220, configured in this way, exhibits a certain marginal effect in its output power, accelerating the coagulation process while avoiding damage to the patient's tissues.

[0039] Preferably, the processing unit 210 selects different modes of the light source emitting unit 111 based on changes in blood flow velocity and blood volume. These different modes include at least a dynamic mode and a static mode. The dynamic mode refers to the light source emitting unit 111 emitting light intermittently. The static mode refers to the light source emitting unit 111 emitting light continuously. Preferably, the processing unit 210 sends a control signal to switch the light source emitting unit 111 to either the dynamic or static mode. For example, during the initial screening of tissue to be cut by medical personnel, if the area to be screened is too large, the processing unit 210 sends a control signal to switch the light source emitting unit 111 to the static mode to save surgical time. In the static mode, the processing unit 210 can continuously and in real-time acquire blood flow velocity and blood volume through the light source emitting unit 111 and the light source receiving unit 112. The processing unit 210 achieves accurate monitoring of blood vessel distribution through continuous detection, thereby quickly screening the blood vessel distribution of the tissue to be cut and shortening the surgical time. When the processing unit 210 detects that the blood flow velocity and / or blood volume in the patient's blood vessels or tissues at the current location are within normal limits, the processing unit 210 determines that the location is suitable for cutting and sends a control signal to switch the light source emitting unit 111 to dynamic mode. In dynamic mode, the processing unit 210 can intermittently acquire blood flow velocity and blood volume through the light source emitting unit 111 and the light source receiving unit 112. The processing unit 210 controls the light source emitting unit 111 and the light source receiving unit 112 to acquire light information at a low frequency, thereby reducing the energy consumption of the light source emitting unit 111 and the light source receiving unit 112, and also enables real-time monitoring of bleeding in the patient's blood vessels or tissues. During a long surgical procedure, the light source emitting unit 111 and the light source receiving unit 112 can be used multiple times for continuous cutting. To enable the light source emitting unit 111 and the light source receiving unit 112 to continuously complete their work, this invention reduces the power consumption of the light source emitting unit 111 and the light source receiving unit 112 by switching modes, thus extending the usage time.

[0040] Existing high-frequency electrosurgical procedures lack vascular monitoring of the tissue being cut, leading to dangerous situations such as massive bleeding during subsequent cutting. The different modes provided in this invention address these issues. This invention indirectly monitors changes in the patient's blood flow velocity and volume by acquiring light information. However, the small size of the high-frequency electrosurgical unit prevents the inclusion of large batteries or power supply components in the light source emitting unit 111 and light source receiving unit 112, thus hindering prolonged surgical procedures. Therefore, in the initial use of the contact mechanism 100 of this invention, a static mode can be employed, i.e., continuous monitoring of the patient's blood is achieved through continuous light emission. After determining the cutting position, a dynamic mode is switched to intermittently emit light, reducing the energy consumption of the light source emitting unit 111, thereby supporting prolonged surgical procedures. Furthermore, the dynamic mode prevents specific wavelengths of light from affecting the patient's body.

[0041] According to a preferred embodiment, the processing unit 210 controls the electro-cutting and electro-coagulation of the high-frequency blade assembly 220 based on a first signal and a second signal transmitted by the control module 230 on the holding mechanism 200, respectively. The first signal is the electro-cutting signal transmitted by the user through the control module 230, and the second signal is the electro-coagulation signal transmitted by the user through the control module 230. The holding mechanism 200 includes at least a holding part 240 for holding. The control module 230 is disposed at the front end of the holding part 240. The control module 230 has at least two buttons, an electro-cutting button and an electro-coagulation button. The placement of the control module 230 at the front end of the holding part 240 facilitates the operator's operation of the buttons on the control module 230 during holding. The action of the electro-cutting button corresponds to transmitting the first signal to the processing unit 210, and the action of the electro-coagulation button corresponds to transmitting the second signal to the processing unit 210.

[0042] According to a preferred embodiment, the control module 230 also has a memory setting function. When performing a second cut on the same patient tissue, the control module 230 can directly display the historical blood vessel position and the output power of the high-frequency blade assembly 220 from the previous cut to the user and send them to the processing unit 210 via a communication-connected display screen. This allows the processing unit 210 to adjust the output power of the high-frequency blade assembly 220 at a faster rate. The processing unit 210 sets the historical blood vessel position and the output power of the high-frequency blade assembly 220 from the first cut as a reference value to adjust the output power of the high-frequency blade assembly 220. The present invention provides the historical blood vessel position and the output power of the high-frequency blade assembly 220, and can also verify the blood vessel position and the output power of the high-frequency blade assembly 220 by measuring the blood volume in the blood vessel through the light source emitting unit 111 and the light source receiving unit 112.

[0043] Throughout the text, the features referred to by “preferred” are only optional and should not be construed as mandatory. Therefore, the applicant reserves the right to abandon or delete the relevant preferred features at any time.

[0044] It should be noted that the specific embodiments described above are exemplary. Those skilled in the art can devise various solutions inspired by the disclosure of this invention, and these solutions all fall within the scope of this invention and its protection. Those skilled in the art should understand that this specification and its accompanying drawings are illustrative and not intended to limit the scope of the claims. The scope of protection of this invention is defined by the claims and their equivalents. This specification contains multiple inventive concepts; terms such as "preferredly," "according to a preferred embodiment," or "optionally" indicate that the corresponding paragraph discloses an independent concept. The applicant reserves the right to file divisional applications based on each inventive concept.

Claims

1. A cutting and coagulation system based on vascular monitoring, comprising at least: Contact mechanism (100) for cutting tissue or clotting blood vessels; The feature is that it further includes a processing unit (210), a limiting member (250), and a light source emitting unit (111) and a light source receiving unit (112) disposed on the contact mechanism (100). The end of the contact mechanism (100) is provided with a first contact portion (110) and a second contact portion (120), and the first contact portion (110) and the second contact portion (120) form a structure with a cavity in the middle; The contact mechanism (100) is provided with a hollow channel connected to the cavity. The high-frequency blade assembly (220) can move within the hollow channel under the restriction of the limiting member (250) and can partially extend out of the first contact portion (110) and the second contact portion (120). The limiting member (250) can restrict the high-frequency blade assembly (220) within the hollow channel to avoid contact with the patient's tissue. The light source emitting unit (111) emits light to the contact site of the blood vessel or tissue. The light source receiving unit (112) receives light rays absorbed and reflected by the blood vessel or tissue to form light information and sends the light information to the processing unit (210), wherein the processing unit (210) is configured to: The blood flow velocity and blood volume within the blood vessels are determined based on the spectral information image generated from the light information; the distribution of the blood vessels is determined based on the blood flow velocity and blood volume, and the output power of the high-frequency blade assembly (220) of the contact mechanism (100) is controlled. When the calculated blood volume is above a preset value, the high-frequency blade assembly (220) is controlled to preheat.

2. The cutting and coagulation system based on vascular monitoring according to claim 1, characterized in that, The processing unit (210) determines the blood flow velocity and blood volume within the blood vessel based on the spectral information image generated from the light information, including at least the following steps: The blood flow velocity in the blood vessel is determined based on the waveform change caused by the absorption of light emitted by the light source emitting unit (111) by the blood. The spectrum of light is obtained based on the light information to generate a spectral information image; The blood volume in the blood vessel is determined based on the changes in the absorption peak of the reflected light in the spectral information image.

3. The cutting and coagulation system based on vascular monitoring according to claim 2, characterized in that, The step of the processing unit (210) determining the blood flow velocity in the blood vessel based on the waveform change caused by the absorption of light emitted by the light source emitting unit (111) by the blood includes at least the following: Acquire the spectral information image of the adjacent light source receiving unit (112); The blood flow velocity within the blood vessel is calculated based on the waveform delay of the spectral information image.

4. The cutting and coagulation system based on vascular monitoring according to claim 1, characterized in that, The step of the light source receiving unit (112) receiving light absorbed and reflected by the blood vessel or tissue to form light information includes at least the following: The light emitted by the light source emitting unit (111) is absorbed by the hemoglobin in the blood and reflected to the light source receiving unit (112). The light source receiving unit (112) acquires the waveform of the reflected light after being reflected by the blood vessel or tissue to form the light information reflecting the amount of light absorption.

5. The cutting and coagulation system based on vascular monitoring according to claim 1, characterized in that, The step of the processing unit (210) controlling the output power of the high-frequency blade assembly (220) of the contact mechanism (100) based on the blood flow velocity and the blood volume includes at least the following steps: The output power of the high-frequency cutter head assembly (220) of the contact mechanism (100) is controlled based on the blood volume and the blood flow velocity; and the output power of the high-frequency cutter head assembly (220) of the contact mechanism (100) is controlled based on the blood flow acceleration.

6. The cutting and coagulation system based on vascular monitoring according to claim 1, characterized in that, The processing unit (210) is further configured to: The mode of the light source emitting unit (111) is selected based on the changes in blood flow velocity and blood volume, wherein, The processing unit (210) sends a control signal to switch the light source emitting unit (111) to either a dynamic mode that emits intermittent light or a static mode that emits continuous light.

7. The cutting and coagulation system based on vascular monitoring according to claim 1, characterized in that, The light source emitting unit (111) and the light source receiving unit (112) in the first contact portion (110) and the second contact portion (120) are arranged such that the emitting surface and the receiving surface are close to the patient contact portion.

8. The cutting and coagulation system based on vascular monitoring according to claim 1, characterized in that, The light source emitting unit (111) and the light source receiving unit (112) are arranged at intervals within the first contact portion (110) and the second contact portion (120), and the distance between adjacent light source emitting units (111) and light source receiving units (112) is fixed. The processing unit (210) is further configured to: The blood flow velocity in the patient's blood vessels is calculated based on the distance between adjacent light source emitting units (111) and light source receiving units (112) and the converted spectral information image.

9. The cutting and coagulation system based on vascular monitoring according to claim 1, characterized in that, In the case of secondary cutting of the tissue, the processing unit (210) is further configured to: The historical blood vessel location during a single cut and the output power of the high-frequency cutter head assembly (220) are set as reference values ​​to adjust the output power of the high-frequency cutter head assembly (220).

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