Field effect transistor assembly machine using method and biosensing detection device

Abstract

The invention provides a field effect transistor assembly machine using method and a biosensing detection device. The field effect transistor assembly is used for biosensing detection, and comprises: a substrate configured as a substrate; the transistor is arranged on one surface of the substrate and is configured to detect a target object; the piezoelectric transducer is arranged on the substrate and is configured to generate a flow field; the micro-fluidic chip is arranged on one side of the transistor and is configured to control a flow field; the transistor comprises a probe, the probe is located at one end of the transistor, and sulfydryl of the probe is roughly located at the middle position of a nucleic acid chain. The micro-fluidic chip is used for controlling the flow field, fluid law disturbance control is achieved through the flow field, and Brownian motion of a to-be-detected target is reduced and eliminated. The sulfydryl of the probe is arranged in the middle of the nucleic acid chain, so that after the functionalized surface of the transistor is combined with the to-be-detected target, the distance between the to-be-detected target and the surface of the transistor is greatly shortened, the intensity of a detection signal can be effectively improved, and the sensitivity is improved.

Description

Technical Field

[0001] The present disclosure relates to the field of biosensor technology, and in particular to a method for using a field effect transistor component machine and a biosensor detection device. Background Art

[0002] Field effect transistor (FET) biosensors play an important role in life sciences due to their high degree of miniaturization and integration. The working principle of FET sensors is based on the change in conductance in the FET channel caused by binding to the target. It has the advantages of instant response, label-free, high specificity, high sensitivity, and repeatable detection. It can perform ultra-high sensitive real-time detection of biological and chemical substances such as ions, nucleic acids, proteins, viruses, cells, and sugars. At present, FET biosensors have made great progress in the fields of medical testing, biopharmaceuticals, environmental monitoring, and cell research.

[0003] However, the current application of FET biosensors is mainly in the detection of low ionic strength solutions. The research on direct detection of target molecules in high ionic strength solutions has encountered a bottleneck. Due to the influence of the Debye screening effect, the detection sensitivity of high ionic strength biological molecules will be reduced, or even the signal cannot be detected, which limits the application of FET biosensors in many fields. Summary of the invention

[0004] The purpose of the present disclosure is to provide a method for using a field effect transistor assembly machine and a biosensor detection device, which can solve at least one of the above-mentioned technical problems. The specific solution is as follows:

[0005] According to a specific embodiment of the present disclosure, on the one hand, the present disclosure provides a field effect transistor component, the field effect transistor component is used for biosensing detection, the field effect transistor component includes: a substrate, the substrate is configured to provide a substrate; a transistor, the transistor is arranged on one side of the substrate, the transistor is configured to detect a target; a piezoelectric transducer, the piezoelectric transducer is arranged on the substrate, the piezoelectric transducer is configured to generate a flow field; a microfluidic chip, the microfluidic chip is arranged on one side of the transistor, the microfluidic chip is configured to control the flow field; wherein the transistor includes: a probe, the probe is located at one end of the transistor, and the thiol group of the probe is approximately located in the middle of the nucleic acid chain.

[0006] In an optional embodiment, the transistor is multiple and the multiple transistor arrays are heterogeneously integrated.

[0007] In an optional embodiment, one end of a plurality of the transistors are connected in series via a bubble coupling.

[0008] In an optional embodiment, the piezoelectric transducer is disposed on the substrate and connected to the microfluidic chip, and the piezoelectric transducer is configured to generate ultrasonic waves to achieve vibration.

[0009] In an optional embodiment, the microfluidic chip is configured as a flow field ultrasonic bubble flow field.

[0010] According to a specific embodiment of the present disclosure, on the other hand, the present disclosure provides a method for using a field effect transistor component, which is applied to biosensing detection, including: using a low ion concentration liquid as a solvent for the target to be detected; achieving flow field law disturbance control for the target to be detected; contacting the target to be detected with a transistor, and detecting the target to be detected after being captured by a probe.

[0011] In an optional embodiment, the controlling of flow field disturbance on the target to be detected includes:

[0012] Use ultrasonic bubbles to achieve regular fluid disturbance control.

[0013] In an optional embodiment, the method for using the field effect transistor component further includes: performing flow field simulation analysis on the tip structure, the bubble structure, and the tip-coupled bubble structure under flow field excitation.

[0014] In an optional embodiment, the method for using the field effect transistor component further includes: using simulation to explore the impact on the acoustic field and flow field in the microfluidic cavity; and controlling the flow field based on the results of the simulation exploration and the flow field simulation analysis.

[0015] According to a specific embodiment of the present disclosure, on another aspect, the present disclosure provides a biosensor detection device, comprising: a field effect transistor component as described in any one of the above technical solutions.

[0016] Compared with the prior art, the above solution of the embodiment of the present disclosure has at least the following beneficial effects:

[0017] The present invention uses a microfluidic chip to control the flow field, realizes fluid regularity disturbance control through the flow field, reduces and eliminates the Brownian motion of the target to be detected. In addition, by setting the thiol group of the probe in the middle position of the nucleic acid chain, after the functionalized transistor surface is combined with the target to be detected, the distance between the target to be detected and the transistor surface is greatly shortened. The improved transistor probe can effectively increase the intensity of the detection signal and improve the sensitivity.

[0018] It should be understood that the content described in this section is not intended to identify the key or important features of the embodiments of the present disclosure, nor is it intended to limit the scope of the present disclosure. Other features of the present disclosure will become easily understood through the following description. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] Figure 1 A schematic structural diagram of a field effect transistor assembly in the related art is shown.

[0020] Figure 2 A schematic structural diagram of a field effect transistor assembly according to an embodiment of the present disclosure is shown.

[0021] Figure 3 A schematic diagram of the structure of a transistor and a microfluidic chip according to an embodiment of the present disclosure is shown.

[0022] Figure 4 A schematic structural diagram of a bubble body according to an embodiment of the present disclosure is shown.

[0023] Figure 5 A schematic diagram of the structure of a probe according to an embodiment of the present disclosure is shown.

[0024] Figure 6 A flow chart of a method for using a field effect transistor assembly according to an embodiment of the present disclosure is shown.

[0025] Reference numerals:

[0026] 100: substrate;

[0027] 200: transistor; 210: probe; 211: thiol; 212: nucleic acid chain; 213: bubble;

[0028] 300: piezoelectric transducer;

[0029] 400: Microfluidic chip.

[0030] Related technologies:

[0031] 900: transistor; 910: probe. DETAILED DESCRIPTION

[0032] In order to make the purpose, technical solutions and advantages of the present disclosure clearer, the present disclosure will be further described in detail below in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present disclosure, rather than all of the embodiments. Based on the embodiments in the present disclosure, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present disclosure.

[0033] The terms used in the embodiments of the present disclosure are only for the purpose of describing specific embodiments, and are not intended to limit the present disclosure. The singular forms "a", "said" and "the" used in the embodiments of the present disclosure and the appended claims are also intended to include plural forms, unless the context clearly indicates other meanings, and "multiple" generally includes at least two.

[0034] It should be understood that the term "and / or" used in this article is only a description of the association relationship of associated objects, indicating that there can be three relationships. For example, A and / or B can represent: A exists alone, A and B exist at the same time, and B exists alone. In addition, the character " / " in this article generally indicates that the associated objects before and after are in an "or" relationship.

[0035] It should be understood that although the terms first, second, third, etc. may be used to describe structures in the disclosed embodiments, these structures should not be limited to these terms. These terms are only used to distinguish different structures. For example, without departing from the scope of the disclosed embodiments, a first component may also be referred to as a second component, and similarly, a second component may also be referred to as a first component.

[0036] As used herein, the words "if" and "if" may be interpreted as "at the time of" or "when" or "in response to determining" or "in response to detecting", depending on the context. Similarly, the phrases "if it is determined" or "if (stated condition or event) is detected" may be interpreted as "when it is determined" or "in response to determining" or "when detecting (stated condition or event)" or "in response to detecting (stated condition or event)", depending on the context.

[0037] It should also be noted that the term "includes", "comprising" or any other variation thereof is intended to cover non-exclusive inclusion, so that a commodity or device including a series of elements includes not only those elements, but also other elements not explicitly listed, or also includes elements inherent to such commodity or device. In the absence of more restrictions, the elements defined by the sentence "comprising a ..." do not exclude the existence of other identical elements in the commodity or device including the elements.

[0038] Figure 1 A schematic structural diagram of a field effect transistor assembly in the related art is shown.

[0039] like Figure 1As shown, in the related art, at the end of the transistor 900 used for biosensing detection, the thiol group of the probe 910 is connected to the nucleic acid chain end to end. At present, the FET surface is mainly modified with 3-aminopropyltriethoxysilane (APTES) by hydroxyl to form an amino end on the surface of the transistor 900, and the DNA probe 910 molecules are further assembled on the surface of the transistor 900 by silanization treatment and chemical bonding of the surface of the transistor 900. The hybridization of DNA and DNA is used to achieve ultra-sensitive, specific, label-free, and real-time detection and analysis of target DNA molecules. The Debye shielding effect has little effect on the detection of small molecule oligonucleotides (such as DNA or RNA). Under normal circumstances, the probe 910 molecule (such as an antibody) is fixed at a position about 10nm away from the FET surface, while the Debye length of whole blood or high ionic strength solution is about 0.7nm. Therefore, in a high ionic strength solution, the potential change caused by the probe 910 molecule and the binding target molecule is shielded, so that the sensor current cannot be changed, which poses a major challenge to the practical application of FET-based biosensors. The detection efficiency of FET biosensors for targets is affected by the distribution of charge groups in the target, the binding direction of the target, and the distance between the target and the FET biosensor channel. The binding rate with the sensitive layer of the TFT sensor is low in the Brownian motion mode.

[0040] In order to solve at least one of the technical problems mentioned above, the present disclosure provides a method for using a field effect transistor 200 component machine and a biosensor detection device, wherein the field effect transistor 200 component is used for biosensor detection, and the field effect transistor 200 component includes: a substrate 100, wherein the substrate 100 is configured to provide a substrate; a microfluidic chip 400, wherein the microfluidic chip 400 is disposed on one side of the substrate 100, and wherein the microfluidic chip 400 is configured to control a flow field; a transistor 200, wherein the transistor 200 is disposed on a side of the microfluidic chip 400 away from the substrate 100, and wherein the transistor 200 is configured to detect a target; wherein the transistor 200 includes: a probe 210, wherein the probe 210 is located at one end of the transistor 200, and wherein the thiol group 211 of the probe 210 is approximately located in the middle of a nucleic acid chain 212. The present invention mainly utilizes ultrasonic microfluidic technology to break through the Brownian motion mode of DNA, realize controlled motion, and improve the specific binding efficiency of DNA and the sensitive layer. At the same time, the high binding rate can capture most of the target DNA in a short time, thereby breaking through the limitation that conventional detection cannot change the liquid, and then replacing it with a low ion concentration liquid to increase the Debye length and weaken the Debye shielding effect; the sensitivity of the TFT sensor is improved from the two aspects of binding efficiency and Debye shielding.

[0041] The optional embodiments of the present disclosure are described in detail below with reference to the accompanying drawings.

[0042] Figure 2 A schematic structural diagram of a field effect transistor 200 assembly according to an embodiment of the present disclosure is shown. Figure 3 FIG. 4 is a schematic diagram showing the structure of a transistor 200 and a microfluidic chip 400 according to an embodiment of the present disclosure. Figure 5 FIG. 2 shows a schematic diagram of the structure of a probe 210 according to an embodiment of the present disclosure. Figure 2 , Figure 3 and Figure 5 As shown, according to a specific embodiment of the present disclosure, on the one hand, a field effect transistor 200 component is provided, and the field effect transistor 200 component is used for biosensing detection, and the field effect transistor 200 component includes: a substrate 100, and the substrate 100 is configured to provide a substrate; a transistor 200, and the transistor 200 is arranged on one side of the substrate 100, and the transistor 200 is configured to detect a target; a piezoelectric transducer 300, and the piezoelectric transducer 300 is arranged on the substrate 100, and the piezoelectric transducer 300 is configured to generate a flow field; a microfluidic chip 400, and the microfluidic chip 400 is arranged on one side of the transistor 200, and the microfluidic chip 400 is configured to control the flow field; wherein, the transistor 200 includes: a probe 210, and the probe 210 is located at one end of the transistor 200, and the thiol group 211 of the probe 210 is approximately located in the middle of the nucleic acid chain 212. The present disclosure uses a microfluidic chip 400 to control the flow field, realizes fluid regularity disturbance control through the flow field, and reduces and eliminates the Brownian motion of the target to be detected. In addition, by setting the thiol group 211 of the probe 210 in the middle position of the nucleic acid chain 212, the distance between the target to be detected and the surface of the transistor 200 is greatly shortened after the functionalized transistor 200 surface is combined with the target to be detected, and the improved transistor 200 probe 210 can effectively improve the intensity of the detection signal and improve the sensitivity. It should be noted that the field effect transistor 200 component disclosed in the present disclosure uses the COMSOL analysis platform before use to perform flow field simulation analysis on the tip structure, bubble structure and tip coupling bubble structure under ultrasonic excitation. The pressure acoustics, thermoviscous acoustics, and laminar flow modules are used to analyze the influence of microstructures on the acoustic field and flow field in the microfluidic cavity. Then, according to the results of the simulation exploration and flow field simulation analysis and the optimization of the device structure, key dimensions and process parameters, an ultrasonic enhanced field effect transistor 200 sensor chip is designed. The component consists of two layers, the upper layer is a PDMS ultrasonic microfluidic chip 400 (i.e., the microfluidic chip 400), which is used for ultrasonic liquid (i.e., the flow field) manipulation, and the lower layer is a field effect transistor 200 array. The entire device and the piezoelectric transducer 300 are adhered to a glass sheet, and the piezoelectric transducer 300 is used to generate ultrasound to achieve vibration.

[0043] In some embodiments, there are a plurality of transistors 200 , and a plurality of transistors 200 are heterogeneously integrated in an array.

[0044] In some embodiments, the transistor 200 is a field effect transistor 200. The Id parameter of the field effect transistor 200 sensor increases with the increase of the drain voltage, and has a good linear relationship. It means that a curve with a consistent linear change trend can be obtained when different gate voltages are applied, indicating that the field effect transistor 200 sensor of the embodiment of the present disclosure can be effectively regulated by the gate voltage.

[0045] Figure 4 FIG. 2 shows a schematic diagram of the structure of the bubble body 213 according to an embodiment of the present disclosure. Figure 4 As shown, in some embodiments, one end of the plurality of transistors 200 is coupled in series through a bubble body 213. The core of the upper microfluidic chip 400 is a PDMS flexible tip. Under the action of ultrasound, the oscillation of the microstructure induces a strong microflow, and two symmetrical vortex flows rotate in opposite directions. Comparing the flow field simulation results of the tip, bubble, and tip-coupled bubble structure, the structure of the coupled bubble body 213 and the tip cantilever oscillation mechanism will produce mutually enhanced and amplified acoustic disturbance effects, thereby causing vortex microflows with higher flow speeds.

[0046] In some embodiments, the field effect transistor 200 component further includes: a piezoelectric transducer 300, wherein the piezoelectric transducer 300 is disposed on the substrate 100 and connected to the microfluidic chip 400, and the piezoelectric transducer 300 is configured to generate ultrasonic waves to achieve vibration.

[0047] In some embodiments, the microfluidic chip 400 is configured as a flow field ultrasonic bubble flow field.

[0048] In some embodiments, the preparation process of the field effect transistor 200 component is as follows: the upper PDMS ultrasonic microfluidic device is prepared by the standard "photolithography-inverting" process, first preparing a silicon wafer master on a silicon wafer by SU8 photoresist, and then by the PDMS inverting process. After the PMDS microfluidic device is prepared, it is heterogeneously integrated with the field effect field effect transistor 200 array to make an ultrasonic enhanced field effect transistor 200 field effect sensor chip, and after integration, the PDMS tip area is aligned with the field effect field effect transistor 200 sensitive area. The entire device is then bonded to a glass substrate, and ultrasonic disturbances are generated by a piezoelectric transducer 300.

[0049] Specifically, the surface functionalization of the field effect transistor array 200 includes the following steps:

[0050] S10. Use anhydrous ethanol and (3-aminopropyl) triethoxysilane (APTES) to prepare a 5% solution by volume, and place the FET in it for soaking. Then put it in a shaker and incubate it at 25°C at a speed of 180r / min for 1h. Since the surface of the sensing area of ​​FET contains hydroxyl groups, silanization will occur after soaking with APTES solution, so that the hydroxyl groups on the surface of the sensing area are converted into amino groups.

[0051] S20. Rinse the surface of the FET sensor with anhydrous ethanol to first wash away the high-concentration solution residue; then quickly immerse it in anhydrous ethanol and rinse it repeatedly. Since anhydrous ethanol is highly volatile, it is necessary to try not to let the device out of the liquid environment during the entire process. After rinsing, use nitrogen to quickly blow dry to prevent the anhydrous ethanol from evaporating and leaving APTES on the surface of the device to form white crystals, which will affect the sensitivity of the device and the detection results.

[0052] S30, placing the blow-dried device in an oven at 110° C. and baking for 30 minutes to perform surface silanization, which can make the amino groups just grown on the surface of the FET sensing area more solid.

[0053] S40. Use 10mM (pH 7.4) PBS solution to prepare 4-(N-maleimidomethyl)cyclohexane-1-carboxylic acid sulfosuccinimide sodium salt (sulfo-SMCC) into a 1mg / mL solution. Since sulfo-SMCC is difficult to dissolve, the solution can be placed in an ultrasonic machine and the temperature can be set to 50°C. Ultrasonication can be performed for about 20 minutes. During this period, the solution can be paused and shaken to help it dissolve as quickly as possible. Immerse the device in the prepared solution and incubate it in a shaker at a speed of 180r / mim for 2h. Since a relatively stable amino group has been formed in the sensing area of ​​the device before, a stable amide bond can be formed when reacting with sulfo-SMCC, allowing it to establish a stable connection with the sensing area of ​​the device.

[0054] S50. After taking out the device, rinse it with 10 mM (pH 7.4) PBS solution and blow dry it with nitrogen gas.

[0055] S60. Use 10 mM (pH 7.4) PBS to dissolve tri-(2-formylethyl)phosphine hydrochloride particles, prepare a 10 mM solution to dissolve the DNA probe 210 powder, and incubate in a shaker for 1 hour.

[0056] S70, drop the DNA probe 210 solution into the sensing area of ​​the device and incubate at 4°C for 12 hours. Since the sensing area of ​​FET is small, about 3 μL of solution is used each time when the probe 210 is incubated, which is very easy to volatilize after 12 hours and affects the modification effect. Therefore, we put the FET to be incubated into a wet box, which can effectively prevent the volatilization of the DNA probe 210 solution while ensuring good sealing and preventing the external DNA enzyme from decomposing the probe 210. Then, the thiol 211 at the 5' end of the DNA probe 210 can form a stable thioether bond with sulfo-SMCC to ensure that the DNA probe 210 is stably connected to the sulfo-SMCC, thereby firmly connecting the DNA probe 210 to the sensing area of ​​the device.

[0057] S80. After the probe 210 is incubated, the device is taken out, and the unbound probe 210 is rinsed with a 10 mM (pH 7.4) PBS solution, and blown dry with nitrogen. At this point, the surface functionalization is completed, and the DNA probe 210 has been firmly connected to the surface of the sensing area through a stable chemical bond, and the sample can be dropped into it for detection.

[0058] According to a specific embodiment of the present disclosure, on the other hand, a method for using a field effect transistor 200 component is provided, and the method for using the field effect transistor 200 component is used for biosensing detection, and the method for using the field effect transistor 200 component includes: using a low ion concentration liquid as a solvent for the target to be detected; achieving flow field law disturbance control for the target to be detected; contacting the target to be detected with the transistor 200, and detecting the target to be detected after being captured by the probe 210.

[0059] Figure 6 FIG. 2 is a flow chart showing a method for using a field effect transistor 200 assembly according to an embodiment of the present disclosure. Figure 6 Specifically, the method for using the field effect transistor 200 assembly includes at least the following steps:

[0060] S100, using a liquid with a low ion concentration as a solvent for the target to be detected.

[0061] S200, realizing flow field law disturbance control on the target to be detected.

[0062] S300 , the target to be detected is brought into contact with the transistor 200 , and the target to be detected is captured by the probe 210 and then detected.

[0063] Among them, in step S100, the original sample solution is replaced with a low ion concentration liquid by a cleaning and liquid replacement method. Since most of the targets to be detected have been captured by the probe 210, the liquid replacement will hardly affect the concentration of the target to be detected, and the low concentration liquid can effectively reduce the influence of Debye interference, thereby improving the sensitivity of the system to detect the target to be detected.

[0064] Among them, in step S200, ultrasonic bubbles are used to realize regular disturbance control of the fluid, and the sample to be tested is added into PDMS. In the absence of ultrasound, the sample to be tested is in Brownian motion in the liquid and randomly contacts the functionalized probe 210 in the sensor detection area of ​​the field effect transistor 200, and the probability of being captured by the probe 210 is small.

[0065] Among them, in step S300, under the disturbance of ultrasound, the Brownian motion mode is broken and a controlled motion mode is formed, the contact probability between the target to be measured and the functionalized probe 210 is increased, and the efficiency of the probe 210 in capturing the target to be measured is improved; in the high binding rate mode, the high concentration probe 210 can capture most of the targets to be measured in a short time.

[0066] In some embodiments, in step S200, ultrasonic bubbles are used to achieve fluid regular disturbance control. In an optional embodiment, flow field simulation analysis is performed on the tip structure, bubble structure, and tip-coupled bubble structure under flow field excitation. The influence of the acoustic field and flow field in the microfluidic cavity is explored by simulation; based on the results of the simulation exploration and the flow field simulation analysis, the flow field is controlled.

[0067] In some embodiments, the achieving flow field regularity disturbance control on the target to be detected includes: achieving fluid regularity disturbance control using ultrasonic bubbles.

[0068] In some embodiments, the method for using the field effect transistor 200 assembly further includes: performing flow field simulation analysis on the tip structure, the bubble structure, and the tip-coupled bubble structure under flow field excitation.

[0069] In some embodiments, the method of using the field effect transistor 200 assembly further includes: using simulation to explore the impact on the acoustic field and flow field in the microfluidic cavity; and controlling the flow field based on the results of the simulation exploration and the flow field simulation analysis.

[0070] According to a specific embodiment of the present disclosure, on another aspect, a biosensor detection device is provided, and the biosensor detection device includes: a field effect transistor 200 component as described in any one of the above embodiments.

[0071] The present disclosure aims to protect a method for using a field effect transistor 200 component machine and a biosensor detection device, wherein the field effect transistor 200 component is used for biosensor detection, and the field effect transistor 200 component comprises: a substrate 100, wherein the substrate 100 is configured to provide a substrate; a transistor 200, wherein the transistor 200 is disposed on one side of the substrate 100, and wherein the transistor 200 is configured to detect a target; a piezoelectric transducer 300, wherein the piezoelectric transducer 300 is disposed on the substrate 100, and wherein the piezoelectric transducer 300 is configured to generate a flow field; a microfluidic chip 400, wherein the microfluidic chip 400 is disposed on one side of the transistor 200, and wherein the microfluidic chip 400 is configured to control the flow field; wherein the transistor 200 comprises: a probe 210, wherein the probe 210 is located at one end of the transistor 200, and wherein the thiol group 211 of the probe 210 is approximately located in the middle of a nucleic acid chain 212. The present disclosure mainly breaks through the DNA Brownian motion mode by utilizing ultrasonic microfluidics technology, realizes controlled motion, and improves the specific binding efficiency of DNA and sensitive layer. At the same time, the high binding rate can realize the capture of most of the target DNA in a short time, thereby breaking through the limitation that conventional detection cannot change liquid, and then replacing low ion concentration liquid to increase Debye length and weaken Debye shielding effect; improve the sensitivity of TFT sensor from two aspects of binding efficiency and Debye shielding. The present disclosure uses microfluidic chip 400 to control the flow field, realizes fluid regular disturbance control through the flow field, reduces and eliminates the Brownian motion of the target to be detected. In addition, by arranging the thiol group 211 of the probe 210 in the middle position of the nucleic acid chain 212, after the functionalized transistor 200 surface is combined with the target to be detected, the distance between the target to be detected and the surface of the transistor 200 is greatly shortened, and the improved transistor 200 probe 210 can effectively improve the intensity of the detection signal and improve the sensitivity.

[0072] Finally, it should be noted that the various embodiments in this specification are described in a progressive manner, and each embodiment focuses on the differences from other embodiments. The same or similar parts between the various embodiments can be referred to each other. For the system or device disclosed in the embodiment, since it corresponds to the method disclosed in the embodiment, the description is relatively simple, and the relevant parts can be referred to the method part description.

[0073] The above embodiments are only used to illustrate the technical solutions of the present disclosure, rather than to limit them. Although the present disclosure has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some of the technical features therein. However, these modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the embodiments of the present disclosure.

Claims

1. A field effect transistor component for biosensing detection, characterized in that: include: a substrate configured to provide a substrate; A transistor, the transistor being disposed on one side of the substrate, the transistor being configured to detect a target object; a piezoelectric transducer, the piezoelectric transducer being disposed on the substrate, the piezoelectric transducer being configured to generate a flow field; A microfluidic chip, the microfluidic chip being disposed on one side of the transistor and configured to control a flow field; Wherein, the transistor comprises: a probe, wherein the probe is located at one end of the transistor, and the thiol group of the probe is approximately located in the middle of the nucleic acid chain.

2. The field effect transistor assembly according to claim 1, characterized in that: There are a plurality of transistors, and the plurality of transistor arrays are heterogeneously integrated.

3. The field effect transistor assembly according to claim 2, characterized in that: One ends of the plurality of transistors are connected in series through bubble coupling.

4. The field effect transistor assembly according to claim 1, characterized in that: The piezoelectric transducer is arranged on the substrate and connected to the microfluidic chip, and the piezoelectric transducer is configured to generate ultrasonic waves to realize vibration.

5. The field effect transistor assembly according to claim 4, characterized in that: The microfluidic chip is configured as a flow field ultrasonic bubble flow field.

6. A method for using a field effect transistor assembly for biosensing detection, characterized in that: include: Using a low ion concentration liquid as a solvent for the target to be detected; Implementing flow field law disturbance control on the target to be detected; The target to be detected is brought into contact with a transistor, and the target to be detected is detected after being captured by a probe.

7. The method for using the field effect transistor assembly according to claim 6, characterized in that: The control of flow field law disturbance on the target to be detected comprises: Use ultrasonic bubbles to achieve regular fluid disturbance control.

8. The method for using the field effect transistor assembly according to claim 6, characterized in that: Also includes: The flow field simulation analysis of the tip structure, bubble structure and tip-coupled bubble structure is carried out under flow field excitation.

9. The method for using the field effect transistor assembly according to claim 8, characterized in that: Also includes: Use simulation to explore the impact on the acoustic and flow fields within a microfluidic cavity; Based on the results of the simulation exploration and the flow field simulation analysis, the flow field is controlled.

10. A biosensor detection device, characterized in that: include: A field effect transistor assembly as claimed in any one of claims 1 to 5.

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