Portable helicobacter pylori detection device

Abstract

The invention belongs to the technical field of gas detection sensors, and particularly relates to a portable helicobacter pylori detection device which comprises a signal acquisition system and a detection area, and the detection area comprises a sensor detection unit and a detection gas chamber; the sensor detection unit comprises a base, a substrate layer is arranged on the base, a specific sensing array is arranged on the substrate layer and comprises a first array, a second array, a third array and a fourth array which are distributed in a cross shape, and the first array and the second array are of a symmetrical structure and are axially distributed in the middle of the sensor detection unit; the third array and the fourth array are of a symmetrical structure and are transversely distributed along the middle part of the sensor detection unit; according to the device, by integrating the specific sensor array and the signal acquisition system, the recognition capability and the detection precision of the detection device are effectively improved, rapid and portable detection of helicobacter pylori is realized, and the device is suitable for clinical rapid screening, family self-inspection and portable medical treatment.

Description

Technical Field

[0001] The invention belongs to the technical field of gas detection sensors, and in particular relates to a portable Helicobacter pylori detection device. Background Art

[0002] Nasal gas sensors are widely used in environmental monitoring, food quality control, medical diagnosis and other fields. In particular, in medical diagnosis, early diagnosis of certain diseases can be achieved by detecting specific gas components in the patient's breath. Helicobacter pylori is closely related to diseases such as gastritis, gastric ulcer and gastric cancer. Rapid and accurate detection of Helicobacter pylori has important clinical significance.

[0003] Helicobacter pylori is a bacterium closely related to diseases such as gastritis, gastric ulcer and gastric cancer. Its rapid and accurate detection is of great significance for the prevention and treatment of diseases. However, traditional detection methods, such as gastroscopy, rapid urease test and serological testing, although with high accuracy, have the problems of complex operation, poor patient experience and high cost, making it difficult to achieve rapid and convenient detection. In addition, traditional Helicobacter pylori detection methods often rely on a single sensor or a single gas detection, which makes it difficult to accurately distinguish the specific gas produced by Helicobacter pylori from other background gases, and are easily subject to cross-interference, resulting in reduced detection accuracy.

[0004] Carbon nanotubes (CNTs) are widely used in the development of gas sensors due to their high surface area, excellent conductivity and chemical stability, which significantly improves the sensitivity and selectivity of the sensors. Metal oxide thin films, as gas-sensitive materials, have become a research hotspot due to their excellent gas-sensing properties and stability. Although the high specific surface area characteristics of carbon nanotubes (CNTs) (usually > 1000m 2 / g) can enhance gas adsorption capacity, and its interface coupling effect with metal oxides can also improve response sensitivity, but the existing CNTs-based arrays still have obvious shortcomings: first, the types of material combinations are limited, which makes it difficult to meet the needs of simultaneous detection of multiple markers; second, the spatial arrangement of the sensor does not match the gas adsorption kinetics, resulting in a long response recovery time (>180 seconds). Summary of the invention

[0005] In view of the above-mentioned deficiencies in the prior art, the present invention provides a portable Helicobacter pylori detection device, which solves the problems of traditional Helicobacter pylori detection devices, such as complex operation, low detection accuracy, difficulty in meeting the requirements of simultaneous detection of multiple markers and slow detection speed.

[0006] To achieve the above purpose, the technical solution adopted by the present invention is:

[0007] Provided is a portable Helicobacter pylori detection device, comprising a signal acquisition system and a detection area connected to the signal acquisition system, the detection area comprising a sensor detection unit and a detection air chamber arranged above the sensor detection unit, an air inlet being arranged on one side of the detection air chamber, and an air outlet being arranged on the other side of the detection air chamber;

[0008] The sensor detection unit includes a substrate, a substrate layer is arranged on the substrate, a specific sensor array is arranged on the substrate layer, the specific sensor array includes a first array, a second array, a third array and a fourth array, the first array, the second array, the third array and the fourth array are distributed in a "cross" shape, the first array and the second array are symmetrically structured and axially distributed along the middle of the sensor detection unit, the third array and the fourth array are symmetrically structured and horizontally distributed along the middle of the sensor detection unit; the first array is arranged at the output end of the air inlet, and the second array is arranged at the input end of the air outlet;

[0009] The first array, the second array, the third array and the fourth array all include at least three groups of sensors arranged equidistantly, and the sensors include a silicon dioxide layer, a carbon nanotube, a first test electrode and a metal oxide film layer which are sequentially bonded and fixed, and the metal oxide film layer is connected to the second test electrode through an electrode pin, and the second test electrode is arranged on the substrate layer.

[0010] The beneficial effects of adopting the above technical solution are as follows: the device realizes high sensitivity and selective detection of Helicobacter pylori breath markers by integrating a specific sensor array and a signal acquisition system, and is suitable for clinical rapid screening, home self-examination and portable medical treatment, wherein the air inlet of the detection chamber is used to introduce the gas to be tested (such as the patient's exhalation), and the air outlet is used to discharge the gas, and the detection chamber is arranged above the sensor detection unit, which can ensure that the gas flows through the sensor detection unit evenly and stably, thereby improving the accuracy of the detection; at the same time, the sensor detection unit includes a specific sensor array, and the specific sensor array is distributed in a "cross" shape. The specific sensor array distributed in the "cross" shape optimizes the spatial arrangement and combination of the sensors, and significantly improves the specificity and response speed of the sensors. The specific sensor array includes a first array, a second array, a third array and a fourth array, and each array includes at least three groups of sensors arranged equidistantly, which can reduce the crosstalk of gas molecules between adjacent sensors. In addition, each group of sensors is provided with a metal oxide film layer deposited by an electron beam evaporation process, and different metal oxide film layers are sensitive and selective to specific markers in the exhaled breath of Helicobacter pylori, thereby improving the accuracy and stability of the detection. The signal acquisition system is electrically connected to the sensor unit in the detection area, and is used to collect the voltage signal output by the sensor and convert it into data for further processing and analysis. The detection data can be transmitted to the mobile terminal in real time via a USB data cable so that the user can view the detection results at any time.

[0011] Furthermore, the first array, the second array, the third array and the fourth array are divided according to the gas adsorption kinetic characteristics, the first array is a response array, and the second array is a desorption array.

[0012] The beneficial effects of adopting the above technical solution are as follows: by dividing the specific sensor array according to the gas adsorption kinetics, the coordinated work of multiple arrays can be achieved. The first array of fast response type can be placed at the air inlet, where the air flow speed is faster, and the sensor can contact the target gas faster, using the fast response material to quickly adsorb gas molecules and generate signals. The slow desorption type array can be placed at the air outlet, where the air flow is slower and there may even be backflow. The slow desorption material needs a longer time to release the adsorbed gas molecules to avoid residual effects on subsequent detection. This layout can form a gradient and reduce interference between different sensors.

[0013] Furthermore, the metal oxide film layers of the three groups of sensors in the first array are SnO 2 Film, WO 3 The metal oxide film layers of the three groups of sensors in the second array are ZnO film, TiO 2 Thin film and MnO 2 The metal oxide film layers of the three groups of sensors in the third array are Cu 2 O thin film, CeO 2 Thin film and Fe 3 O 4 The metal oxide film layers of the three groups of sensors in the fourth array are NiO film, Co 3 O 4 Thin films and MgO thin films.

[0014] The beneficial effects of the above technical solution are as follows: the first array, the second array, the third array and the fourth array are arranged orthogonally in a "3×4 cross distribution", wherein the metal oxide film layers of the three groups of sensors in the first array are SnO 2 Film, WO 3 Thin films and CuO thin films, SnO 2 , WO 3 and CuO have excellent gas-sensing properties, which can not only reduce the response to other non-target gases to a certain extent and improve the detection selectivity, but also can efficiently adsorb and respond to target gas molecules in exhaled breath, thereby improving the detection sensitivity; the metal oxide film layers of the three groups of sensors in the second array are ZnO film, TiO 2 Thin film and MnO 2 Thin films, ZnO, TiO 2 and MnO 2It can have higher sensitivity to the breath markers that are not fully covered by the first array, broaden the detection range, and help maintain the accuracy of the test results; the metal oxide film layers of the three groups of sensors in the third array are Cu2O film, CeO 2 Thin film and Fe 3 O 4 The metal oxide film layers of the three groups of sensors in the fourth array are NiO film, Co 3 O 4 Thin films and MgO thin films help improve the accuracy and reliability of detection.

[0015] Furthermore, the metal oxide thin film layer is prepared by electron beam evaporation.

[0016] The beneficial effects of adopting the above technical solution are: the electron beam evaporation method can achieve uniform deposition of the metal oxide thin film layer and can accurately control the thickness of the metal oxide thin film, which is beneficial to maintain the consistency of the sensor resistance change, thereby ensuring the accuracy and stability of the detection.

[0017] Furthermore, the thickness of the metal oxide thin film layer is 30-100 nm.

[0018] The beneficial effects of adopting the above technical solution are: the thickness range of 30 to 100 nm can ensure that the film has sufficient sensitivity and can respond quickly to the specific marker gas of Helicobacter pylori in the exhaled breath, while enabling the metal oxide film layer to more effectively adsorb and desorb gas molecules, thereby improving the response speed and recovery time of the sensor.

[0019] Furthermore, the signal acquisition module includes a power supply voltage stabilization module, a microprocessing module, an operational amplifier module and a USART serial port communication module which are electrically connected.

[0020] The beneficial effects of adopting the above technical solution are as follows: the design of the signal acquisition module is highly integrated, making the entire detection device more compact and lightweight, while ensuring performance, it also achieves lower power consumption, prolongs the battery life, and improves the portability and practicality of the device, wherein the power supply voltage regulator module can ensure the stable voltage supply of the signal acquisition circuit, avoid voltage fluctuations, and ensure the normal operation of the sensor and subsequent circuits, the microprocessor module is responsible for receiving the signal from the sensor and performing preliminary processing, and can quickly and accurately obtain the output voltage change of the sensor, and convert it into a digital signal, which is convenient for subsequent analysis and reality, and the microprocessor module improves the speed and efficiency of data processing and the accuracy of the detection result; the operational amplifier module is used to amplify the weak voltage signal output by the sensor, ensure the accuracy and readability of the signal, and reduce interference, thereby further improving the accuracy of the detection result; the USART serial port communication module is responsible for transmitting the data processed by the microprocessor module to the mobile terminal (such as a mobile phone) through the serial port, so that the user can view the detection results in real time, which greatly improves the convenience and flexibility of use, and at the same time, the USART serial port communication module also supports remote transmission and storage of data, which is conducive to subsequent data analysis and health management.

[0021] Furthermore, the material of the first test electrode is Au / Cr / Pt.

[0022] The beneficial effects of adopting the above technical solution are: the first test electrode made of Au / Cr / Pt material can ensure the high efficiency and stability of electrical signal transmission between the test electrode and the specific sensor array, which helps the specific sensor array to accurately detect tiny changes in gas concentration in exhaled breath, thereby improving detection accuracy.

[0023] In summary, the portable Helicobacter pylori detection device provided by the present invention has the following beneficial effects:

[0024] (1) The device integrates a specific sensor array and a signal acquisition system to effectively improve the recognition capability and detection accuracy of the detection device, and realizes rapid and portable detection of Helicobacter pylori. It is suitable for rapid clinical screening, home self-examination and portable medical treatment.

[0025] (2) The signal acquisition system includes a power module, a main control module, an operational amplifier module and a USART serial communication module, which is highly integrated and can quickly and accurately acquire the output voltage signal of the sensor, and transmit the detection data to the mobile terminal through the serial port, realizing real-time data analysis and display of detection results. At the same time, the system is powered by a mobile phone, making the overall device more portable, and the collected sensor data can be directly displayed on the mobile phone, improving the user experience.

[0026] (3) The specific sensor array is composed of a variety of metal oxide thin film gas sensors based on carbon nanotubes. At least 12 different metal oxides are deposited by electron beam evaporation process, which not only improves the sensitivity, selectivity and stability of the sensor to the specific marker gas of Helicobacter pylori, but also reduces the interference to non-target gases. At the same time, the topological structure of the array-specific sensor array can more comprehensively describe the target characteristics by integrating the data of multiple sensors, thereby improving the recognition and distinction ability (selectivity) of the target, which can not only improve the response speed but also reduce cross-interference. BRIEF DESCRIPTION OF THE DRAWINGS

[0027] Figure 1 A schematic diagram of the structure of the sensor detection unit provided by the present invention;

[0028] Figure 2 It is an enlarged cross-sectional schematic diagram of point A in the present invention;

[0029] Figure 3 It is a structural schematic diagram of the detection air chamber in the present invention;

[0030] Figure 4 It is a detection circuit diagram of the present invention;

[0031] Figure 5 It is a schematic diagram of the flow of the signal acquisition system in the present invention;

[0032] Figure 6 A voltage response curve diagram of the Helicobacter pylori detection marker provided by the present invention being acetone;

[0033] Figure 7 A voltage response curve diagram of nitrogen gas as the Helicobacter pylori detection marker provided by the present invention;

[0034] Figure 8 A voltage response curve diagram of the Helicobacter pylori detection marker provided by the present invention being ethyl acetate;

[0035] Fig. 9 A voltage response curve diagram of nitric oxide, which is a Helicobacter pylori detection marker provided by the present invention;

[0036] Among them, 1. sensor detection unit; 11. substrate; 12. substrate layer; 13. first array; 14. second array; 15. third array; 16. fourth array; 2. silicon dioxide layer; 3. first test electrode; 4. carbon nanotube; 5. metal oxide film layer; 6. USART serial communication module; 7. operational amplifier module; 8. microprocessor module; 9. power supply voltage regulator module; 10. detection gas chamber; 101. air inlet; 102. air outlet; 12. second test electrode. DETAILED DESCRIPTION

[0037] The specific implementation modes of the present invention are described below so that those skilled in the art can understand the present invention. However, it should be clear that the present invention is not limited to the scope of the specific implementation modes. For those of ordinary skill in the art, as long as various changes are within the spirit and scope of the present invention as defined and determined by the attached claims, these changes are obvious, and all inventions and creations utilizing the concept of the present invention are protected.

[0038] Example 1

[0039] like Figure 1 to Figure 5 As shown, the portable Helicobacter pylori detection device provided by the present invention includes a signal acquisition system and a detection area connected to the signal acquisition system, the signal acquisition module includes an electrically connected power supply voltage stabilization module 9, a microprocessor module 8, an operational amplifier module 7 and a USART serial communication module 6; the detection area includes a sensor detection unit 1 and a detection air chamber 10 arranged above the sensor detection unit 1, as shown in FIG. Figure 3 As shown, an air inlet 101 is provided on one side of the detection air chamber 10, and an air outlet 102 is provided on the other side of the detection air chamber 10; wherein, the detection air chamber 10 can ensure that the gas to be tested can enter through the air inlet 101, and be discharged from the air outlet 102 after being detected by the sensor detection unit 1. The sensor detection unit 1 has high sensitivity and selectivity to the specific marker gas of Helicobacter pylori, and can realize efficient identification of the target gas. The signal acquisition system can quickly and accurately collect the voltage signal output by the sensor, thereby ensuring the accuracy of the detection data and providing a reliable basis for subsequent real-time data analysis and display of detection results.

[0040] like Figure 1 and Figure 2As shown, the sensor detection unit 1 includes a substrate 11, on which a substrate layer 12 made of silicon dioxide is arranged, and on which a specific sensor array is arranged, the specific sensor array includes a first array 13, a second array 14, a third array 15 and a fourth array 16, the first array 13, the second array 14, the third array 15 and the fourth array 16 are distributed in a "cross" shape, the first array 13 and the second array 14 are symmetrically structured and axially distributed along the middle of the sensor detection unit 1, the third array 15 and the fourth array 16 are symmetrically structured and laterally distributed along the middle of the sensor detection unit 1; the first array 13 is arranged at the output end of the air inlet 101, and the second array 14 is arranged at the input end of the air outlet 102. Among them, the first array 13, the second array 14, the third array 15 and the fourth array 16 are divided according to the gas adsorption kinetic characteristics. The first array 13 is a response array, and the second array 14 is a desorption array. The substrate 11 plays a supporting role, and the substrate layer 12 plays an isolation and protection role, and can isolate the interference of electrical signals, thereby improving the stability of the sensor. The specific sensor array can directly contact the gas to be measured and generate a response signal. The first array 13, the second array 14, the third array 15 and the fourth array 16 distributed in a "cross" shape are helpful to optimize the gas diffusion kinetic characteristics and reduce the crosstalk of gas molecules between adjacent sensors. When in use, the first array 13 is arranged at the output end of the air inlet 101, and can first contact the gas to be measured and respond quickly to generate an initial signal. The second array 14 is arranged at the input end of the air outlet 102, and further detects the remaining gas passing through the first array 13, the third array 15 and the fourth array 16, and the third array 15 and the fourth array 16 can perform comprehensive detection of the gas to be measured from different angles. Through the "cross"-shaped distribution layout of the first array 13, the second array 14, the third array 15 and the fourth array 16, a detection gradient can be formed in the detection area, thereby reducing interference between different sensors.

[0041] like Figure 1 and Figure 2As shown, the first array 13, the second array 14, the third array 15 and the fourth array 16 all include at least three groups of sensors arranged equidistantly, and the sensors include a silicon dioxide layer 2, a carbon nanotube 4, a first test electrode 3 and a metal oxide film layer 5 which are sequentially attached and fixed, and the metal oxide film layer is connected to the second test electrode 12 through an electrode pin, and the second test electrode 12 is arranged on the substrate layer 12. The three groups of sensors arranged equidistantly form spatial clusters in the array, and through a specific arrangement (such as a 3×4 cross-shaped distribution), not only the gas diffusion kinetics are optimized, the gas molecule crosstalk between adjacent sensors is reduced, but also the sensor can contact the target gas molecules faster, shorten the response recovery time, and thus improve the detection efficiency. The silicon dioxide layer 2 as an insulating material layer can prevent the current from flowing in an unexpected path, ensuring the normal operation of the sensor. The carbon nanotubes 4 are transferred to the top of the silicon dioxide layer 2 by Langmuir-Blodgett (LB) technology, and then the required pattern is left on the transferred carbon nanotube 4 layer by photolithography, etching, etc., and Au / Cr / Pt is deposited as the first test electrode 3. Finally, a specific different metal oxide film layer is evaporated on the first test electrode 3 by electron beam evaporation. The thickness of the metal oxide film layer 5 is 30 to 100 nm. Different metal oxides have specific adsorption capacity and sensitivity to different gases. By selecting a specific combination of metal oxides, high-selective detection of Helicobacter pylori specific marker gases can be achieved. The combination of the metal oxide film layer 5 and the carbon nanotubes 4 significantly enhances the sensor's response sensitivity to the target gas, reduces cross interference, and thus improves detection accuracy.

[0042] In this embodiment, the metal oxide film layers of the three groups of sensors in the first array 13 are SnO 2 Film, WO 3 The metal oxide film layers of the three groups of sensors in the second array 14 are ZnO film, TiO 2 Thin film and MnO 2 The metal oxide film layers of the three groups of sensors of the third array 15 are Cu2O film, CeO 2 Thin film and Fe 3 O 4 The metal oxide film layers of the three groups of sensors of the fourth array 16 are NiO film, Co 3 O 4 The metal oxide film layers of the three groups of sensors in the first array 13 are SnO 2 Film, WO 3 Thin films and CuO thin films, SnO 2 , WO 3and CuO have excellent gas-sensing properties, which can not only reduce the response to other non-target gases to a certain extent and improve the detection selectivity, but also can efficiently adsorb and respond to target gas molecules in the exhaled breath, thereby improving the detection sensitivity; the metal oxide film layers of the three groups of sensors in the second array 14 are ZnO film, TiO 2 Thin film and MnO 2 Thin films, ZnO, TiO 2 and MnO 2 It can have higher sensitivity to the breath markers that are not completely covered by the first array 13, broaden the detection range, and help maintain the accuracy of the detection results; the metal oxide film layers of the three groups of sensors in the third array 15 are Cu 2 O thin film, CeO 2 Thin film and Fe 3 O 4 The metal oxide film layers of the three groups of sensors in the fourth array 16 are NiO film, Co 3 O 4 Thin films and MgO thin films help improve the accuracy and reliability of detection.

[0043] Example 2

[0044] This embodiment uses the portable Helicobacter pylori detection device in embodiment 1 to detect the specific gas component whose marker is acetone. During the detection, the detection concentration of the specific gas is 100 ppb, the gas flow rate is 100 sccm, and the corresponding voltage response curve is as shown in FIG. Figure 6 shown.

[0045] Example 3

[0046] This embodiment uses the portable Helicobacter pylori detection device in Embodiment 1 to detect the specific gas component whose marker is nitrogen. During the detection, the detection concentration of the specific gas is 100 ppb, the gas flow rate is 100 sccm, and the corresponding voltage response curve is as shown in FIG. Figure 7 shown.

[0047] Example 4

[0048] This embodiment uses the portable Helicobacter pylori detection device in embodiment 1 to detect the specific gas component whose marker is ethyl acetate. During the detection, the detection concentration of the specific gas is 100 ppb, the gas flow rate is 100 sccm, and the corresponding voltage response curve is as shown in FIG. Figure 8 shown.

[0049] Example 5

[0050] This embodiment uses the portable Helicobacter pylori detection device in Example 1 to detect the specific gas component whose marker is nitric oxide. During the detection, the detection concentration of the specific gas is 100 ppb, the gas flow rate is 100 sccm, and the corresponding voltage response curve is as shown in FIG. Fig. 9 shown.

[0051] In the embodiments 2 to 5, the specific gases are introduced into the detection chamber 10 at 25 seconds, and the response of the sensor can be observed. At the 90th second, air is introduced to clean the sensor, and the sensor response is observed to return to the baseline. Figure 6 to Figure 9 It can be seen that the tactile sensor arrays containing different metal oxide layers have different response patterns to specific gases.

[0052] In summary, the portable Helicobacter pylori detection device provided by the present invention effectively improves the recognition ability and detection accuracy of the detection device by integrating a specific sensor array and a signal acquisition system, thereby realizing rapid and portable detection of Helicobacter pylori, and is suitable for rapid clinical screening, home self-examination and portable medical treatment.

Claims

1. A portable Helicobacter pylori detection device, characterized in that: It includes a signal acquisition system and a detection area connected to the signal acquisition system, wherein the detection area includes a sensor detection unit and a detection air chamber arranged above the sensor detection unit, an air inlet is arranged on one side of the detection air chamber, and an air outlet is arranged on the other side of the detection air chamber; The sensor detection unit comprises a substrate, a substrate layer is arranged on the substrate, a specific sensor array is arranged on the substrate layer, the specific sensor array comprises a first array, a second array, a third array and a fourth array, the first array, the second array, the third array and the fourth array are distributed in a "cross" shape, the first array and the second array are symmetrically structured and axially distributed along the middle of the sensor detection unit, the third array and the fourth array are symmetrically structured and transversely distributed along the middle of the sensor detection unit; the first array is arranged at the output end of the air inlet, and the second array is arranged at the input end of the air outlet; The first array, the second array, the third array and the fourth array all include at least three groups of sensors arranged at equal intervals, and the sensors include a silicon dioxide layer, a carbon nanotube, a first test electrode and a metal oxide film layer that are sequentially bonded and fixed, and the metal oxide film layer is connected to the second test electrode through an electrode pin, and the second test electrode is arranged on a substrate layer.

2. The portable Helicobacter pylori detection device according to claim 1, characterized in that: The first array, the second array, the third array and the fourth array are divided according to the gas adsorption kinetic characteristics, the first array is a response array, and the second array is a desorption array.

3. The portable Helicobacter pylori detection device according to claim 2, characterized in that: The metal oxide film layers of the three groups of sensors in the first array are SnO2 film, WO3 film and CuO film respectively; the metal oxide film layers of the three groups of sensors in the second array are ZnO film, TiO2 film and MnO2 film respectively; the metal oxide film layers of the three groups of sensors in the third array are Cu2O film, CeO2 film and Fe3O4 film respectively; the metal oxide film layers of the three groups of sensors in the fourth array are NiO film, Co3O4 film and MgO film respectively.

4. The portable Helicobacter pylori detection device according to claim 3, characterized in that: The metal oxide thin film layer is prepared by electron beam evaporation.

5. The portable Helicobacter pylori detection device according to claim 4, characterized in that: The thickness of the metal oxide film layer is 30-100 nm.

6. The portable Helicobacter pylori detection device according to claim 1, characterized in that: The signal acquisition module includes a power supply voltage stabilization module, a microprocessing module, an operational amplifier module and a USART serial port communication module which are electrically connected.

7. The portable Helicobacter pylori detection device according to claim 1, characterized in that: The material of the first test electrode is Au / Cr / Pt.

Images