CN109142452A - It is declined the blood viscoelastic force measuring device and method of hanging bridge sensor based on pressure drag - Google Patents
It is declined the blood viscoelastic force measuring device and method of hanging bridge sensor based on pressure drag Download PDFInfo
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- CN109142452A CN109142452A CN201811261649.3A CN201811261649A CN109142452A CN 109142452 A CN109142452 A CN 109142452A CN 201811261649 A CN201811261649 A CN 201811261649A CN 109142452 A CN109142452 A CN 109142452A
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- pressure drag
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Abstract
The present invention provides a kind of to be declined the blood viscoelastic force measuring device and method of hanging bridge sensor based on pressure drag, including microfluidic device, the microfluidic device includes substrate, upper surface of base plate is carved with microchannel, microchannel input terminal is dual-port, output end is single port, pressure drag is installed to decline hanging bridge sensor in microchannel, liquid flows out after the micro- hanging bridge sensor of pressure resistance type from output end after two input terminals flow into and converge；Permanent magnet, the permanent magnet are placed in microfluidic device two sides, for providing stationary magnetic field for the pressure drag hanging bridge sensor that declines；Signal motivates detection circuit, and signal excitation detection circuit connection pressure drag declines hanging bridge sensor, for measuring the viscous force variation during blood coagulation.The present apparatus can fast and accurately measure the viscoelastic power of blood sample using less blood volume, meet the needs of clinical hemostasis examination analysis now.
Description
Technical field
The present invention relates to a kind of for quickly detecting the measuring technique of blood viscoelastic power, more particularly to one kind based on pressure resistance type
The viscoelastic force measuring device and method of the micro blood sample of micro- hanging bridge sensor.
Background technique
Blood coagulation is the process that the blood flowed becomes curdled appearance, and essence is exactly that the soluble fibrin in blood plasma is former
Become insoluble fibrinous process.The detection of coagulation function to the judgement of the prediction of postoperative blood loss risk, cause of bleeding,
Instruct haemostatic measures implement etc. it is all of crucial importance, especially amount of bleeding it is biggish operation as cardiovascular surgical procedure, obstetric operation,
Bone surgery etc. is particularly important.
At present the common method of hemostasis examination have platelet count, fibrinogen concentration, thrombelastogram instrument (TEG),
Rotate thrombus elasticity measuring method (ROTEM), the thrombus elastic force detection based on electromagnetic sensor etc..Platelet count, fibrin
Original content detection time is long, generally wants 45-60 minutes.Thrombelastogram instrument needs are not easy to keep straight when cup head is put into cup body
It is vertical, cause probe to be not easy to be aligned when being inserted into cup head, is unfavorable for upper cup operation.Above method sensitivity is low, and detection every time
The blood volume needed is on the high side, therefore, has been difficult to meet the needs of clinical hemostasis examination analysis now.
Summary of the invention
For the deficiency for solving current technology, the present invention combination prior art provides a kind of based on pressure from practical application
The blood viscoelastic force measuring device and method of the micro- hanging bridge sensor of resistive, can be using less blood volume to blood
The viscoelastic power of sample is fast and accurately measured, and meets the needs of clinical hemostasis examination analysis now.
Technical scheme is as follows:
It is declined the blood viscoelastic force measuring device of hanging bridge sensor based on pressure drag, comprising:
Microfluidic device, the microfluidic device include substrate, and upper surface of base plate is carved with microchannel, and microchannel input terminal is
Dual-port, output end are single port, and pressure drag is equipped in microchannel and is declined hanging bridge sensor, and liquid is flowed into through two input terminals
And it is flowed out after the micro- hanging bridge sensor of pressure resistance type from output end after converging；
Permanent magnet, the permanent magnet are placed in microfluidic device two sides, for providing perseverance for the pressure drag hanging bridge sensor that declines
Fixed-field；
Signal motivates detection circuit, and signal excitation detection circuit connection pressure drag declines hanging bridge sensor, for measuring
Viscous force variation during blood coagulation.
The pressure drag hanging bridge sensor that declines includes silicon base, and silicon base both ends are respectively provided with U-shaped of the opening towards outside
Pressure drag sensing and the electrified wire with autonomous channel, two ends, the two ends of electrified wire of pressure drag sensing are all connected with deposition
Pad on a silicon substrate.
The silicon base is in I-shaped, silicon base both ends setting support base, silicon base top layer deposition silica.
The microchannel direction declines with pressure drag, and hanging bridge sensor hanging bridge direction is vertical, and permanent magnet magnetic line of force direction is hung down
Directly in microchannel direction.
The pressure drag hanging bridge size sensor range that declines is that micro- hanging bridge is long: 200~300 μm, wide: 20~30 μm, thick: 1
~5 μm, the decline silicon base support base height at hanging bridge sensor both ends of pressure drag is higher than intermediate silicon base thickness, and microchannel is in pressure drag
The hanging bridge sensor portion bit wide that declines is 200~300 μm, and 5~50 μm of depth, remaining position width is 1~200 μm, 5~50 μ of depth
M, a length of 1~10cm.
The signal excitation detection circuit includes signal generator, resistance bridge, difference amplifier, multiplier, low pass
Filter, analog-to-digital conversion, microcontroller are sent out wherein the microcontroller is connected with signal generator by microcontroller control signals
Raw device generates sinusoidal and cosine signal, and signal generator declines the sinusoidal excitation signal source access pressure drag of generation hanging bridge sensor
Pad corresponding to electrified wire.
The resistance bridge is declined two pressure drag sensing groups at hanging bridge sensor both ends by two fixed resistances and pressure drag
At resistance bridge two-arm output voltage access differential amplifier in, difference amplifier amplification factor is by non-essential resistance control
System, the output of difference amplifier access two multipliers, and sine, the cosine signal of signal generator output are respectively connected to two and multiply
Musical instruments used in a Buddhist or Taoist mass after two multiplier output signals are by low-pass filtering and analog-to-digital conversion, are sent into microcontroller and handled, obtain amplitude
And phase, and obtain the viscoelastic power during blood coagulation.
The substrate of the microfluidic device is divided into top substrate layer and underlying substrate, and underlying substrate is glass material, upper layer base
Plate is dimethyl silicone polymer material and is carved with microchannel, and top substrate layer is by splashing and closing one with underlying substrate after ion bombardment
It rises.
The input terminal and output end of the microchannel are the identical cylindrical hole in aperture, and are separately connected silica gel hose, two
The silica gel hose of a input terminal connects micro-sampling syringe, and the silica gel hose of output end connects waste liquid collection vessel.
It is a kind of using it is described based on pressure drag decline hanging bridge sensor blood viscoelastic force measuring device measurement method, including
Following steps:
Measuring device is put into temperature control box by step 1, is preheated to the temperature of temperature control box, and the temperature that detection needs is reached
Value；
Step 2, to blood sample and coagulation activation reagent carry out preheating reach test temperature after, be drawn into respectively it is micro into
In sample syringe, the amount of blood sample and coagulation activation reagent is 1~10ul；
Step 3 promotes micro-sampling syringe for blood sample and coagulation activation reagent with syringe pump while being injected into micro-
Channel, blood sample and coagulation activation reagent be advanced to pressure drag decline hanging bridge sensor position when syringe pump stop promote；
Step 4, the reagent that is activated with blood sample activation, blood viscoelastic power changes, and pressure drag declines hanging bridge sensing
Device resonance characteristic changes, and the voltage magnitude and phase for causing signal excitation detection circuit to detect change, and passes through survey
The voltage value and phase obtained, obtains the variation of blood viscoelastic power.
Beneficial effects of the present invention:
1, the present invention declines hanging bridge sensor as the main measurement surveyed element and carry out blood viscoelastic power, pressure resistance type using pressure drag
The manufacture of MEMS processing technology can be used in micro- hanging bridge sensor and microchannel template, and batch cost is cheap, while can make sensor
Very little, in microchannel realize detection when, it is only necessary to test can be completed in micro blood, at least only needs 1ul, can be extensive
Related fields for the detection of blood viscoelastic power.
2, it is preferable can to guarantee that sensor has when the pressure drag that the present invention uses declines hanging bridge sensor using MEMS processing
Consistency, ensure that detection accuracy, meanwhile, micro- hanging bridge structure ensure that the high sensitivity of detection.
3, in detection process of the present invention, micro setting time is short, is suitble to quickly detection.
4, the present invention can be used multiple pressure drags and decline hanging bridge sensor "+" microfluidic device " realize the detection of array, from
And can realize the synchronous detection of different reagents, further increase detection efficiency.
Detailed description of the invention
Attached drawing 1 is that pressure drag declines hanging bridge sensor schematic.
Attached drawing 2 is that pressure drag declines hanging bridge sensor normal section schematic diagram.
Attached drawing 3 is the viscoelastic force measuring device schematic diagram of hanging bridge sensor micro blood sample of being declined based on pressure drag.
Attached drawing 4 is that signal motivates detection circuit block diagram.
Attached drawing 5 is output voltage change curve in micro blood sample viscoelastic power test process.
Attached drawing 6 is output phase change curve in micro blood sample viscoelastic power test process.
Label shown in attached drawing:
1 sensor silica surface
2 sensor silicon bases
21,22 sensor silicon base support base
31,32 sensor electrified wire
41,42 U-shaped pressure drags sense
5 sensor hanging bridges
A1+, A1-, A2+, A2-, B1+, B1-, B2+, B2- pad
6 sensor electrified wire normal sections
7 pressure drags sense normal section
8 microfluidic devices
81 microchannels
82 pressure drags decline hanging bridge sensor
831,832 pressure drags decline hanging bridge sensor extraction wire
84 upper layer PDMS (dimethyl silicone polymer) substrates
85 lower layer's glass substrates
861,862 microchannels enter hole
Portal 863 microchannels
871,872,873 silica gel hose
881,882 injection pump
8810,8820 micro-sampling syringe
89 waste liquid collection vessels
9 permanent magnets
91 poles permanent magnet N
92 permanent magnet S poles
The magnetic line of force of 93 poles the permanent magnet N direction pole S
10 signals motivate detection circuit
Specific embodiment
With reference to the drawings and specific embodiments, the invention will be further described.It should be understood that these embodiments are merely to illustrate
The present invention rather than limit the scope of the invention.In addition, it should also be understood that, after reading the content taught by the present invention, this field
Technical staff can make various changes or modifications the present invention, and such equivalent forms equally fall within range defined herein.
As shown in Figure 1, 2, it declines 82 structural schematic diagram of hanging bridge sensor for pressure drag used in the present invention.
Wherein, the decline substrate of hanging bridge sensor 82 of pressure drag is I-shaped silicon base 2, is deposited with independence in silicon base 2
Electrified wire 31,32 and U-shaped the pressure drag sensing 41,42 in channel, the material of electrified wire 31,32 are aluminium (Al).In pressure resistance type
There are identical electrified wire 31 and 32, pressure drag sensing 41 and 42 in micro- 82 both ends of hanging bridge sensor respectively.Electrified wire 31, energization are led
Line 32 is connected with the aluminum pad A1+ of deposited on silicon substrates with A1-, A2+ with A2- respectively.U-shaped pressure drag sensing 41,42 respectively with
The aluminum pad B1+ of deposited on silicon substrates is connected with B1-, B2+ with B2-.Pressure drag decline 82 top layer of hanging bridge sensor deposition dioxy
SiClx 1.
Pressure drag declines hanging bridge sensor 82, and size range: micro- hanging bridge is long: 200~300 μm, wide: 20~30 μm, thick: 1
~5 μm.Pressure drag decline 82 both ends of hanging bridge sensor silicon base support base 21,22 height be higher than silicon base 2 thickness.
As shown in figure 3, being measuring device general structure schematic diagram of the invention.Pressure drag declines hanging bridge sensor blood viscoelastic
Force measuring device includes: microfluidic device 8, permanent magnet 9, signal excitation detection circuit 10.
Wherein microfluidic device 8 divides for top substrate layer 84 and underlying substrate 85, and underlying substrate 84 is glass material, upper layer base
Plate 85 is PDMS (dimethyl silicone polymer) material and is carved with microchannel 81, and top substrate layer 84 passes through after ion bombardment and lower layer's base
Plate 85, which splashes, to be combined.
Microchannel 81 is sandwiched between pressure drag and declines hanging bridge sensor 82, and microchannel 81 declines hanging bridge sensor 82 in pressure drag
Bit wide be 200~300 μm, 5~50 μm of depth, remaining position width be 1~200 μm, 5~50 μm of depth, a length of 1~10cm.
By pressure drag decline hanging bridge sensor pads A1+, A1-, B1+, B1- by extraction wire 831 draw microfluidic device 8
In addition, other than pressure drag being declined hanging bridge sensor pads A2+, A2-, B2+ and B2- by the extraction microfluidic device 8 of conducting wire 832,
The direction of microchannel 81 is vertical with 2 direction of sensor hanging bridge.
81 input terminal of microchannel is dual-port, and respectively input terminal 861, input terminal 862, output end are single port, is defeated
Outlet 863.Liquid flows into and converges through input terminal 861 and input terminal 862, from output after pressure drag declines hanging bridge sensor 82
863 outflow of end.Microchannel input terminal 861, input terminal 862, microchannel output end 863 are the identical cylindrical hole in aperture, and
It is separately connected silica gel hose 871,872,873.The silica gel hose 871,872,873 drawn from microchannel 81 is respectively and micro-sampling
Syringe 8810, micro-sampling syringe 8820, waste liquid collection vessel 89 are connected, micro-sampling syringe 8810, micro-sampling
Syringe 8820 is separately fixed at syringe pump 881, on syringe pump 882.
As it is shown in the figures, permanent magnet 9 is placed in 8 both ends of microfluidic device, permanent magnet S pole 92 is directed toward in the pole permanent magnet N 91
The magnetic line of force 93 perpendicular to microchannel 81 direction, permanent magnet 9 generate magnetic field be stationary magnetic field.
As shown in figure 4, signal excitation detection circuit 10 includes signal generator S1, resistance bridge B, difference amplifier
IC1, multiplier M1 and M2, low pass filter LPF1 and LPF2, analog-to-digital conversion (A/D), microcontroller (MCU).
MCU is connected with signal generator S1, generates sinusoidal and cosine signal by MCU control signal generator S1.Signal hair
Raw device S1 declines the sinusoidal excitation signal source access pressure drag of generation pad A1+, A2 corresponding to hanging bridge sensor electrified wire
+, A1-, A2- are connected with power ground.
Resistance bridge B by two fixed resistances R1, R2 and pressure drag decline hanging bridge sensor both ends pressure drag sensing 41, pressure
42 composition of resistance sensing, the corresponding resistance in the both ends pad B1+ and B1- is Rsen1, the corresponding resistance in the both ends pad B2+ and B2- is
Rsen2.R1 mono- termination power+VS1, another termination Rsen1, Rsen2 mono- termination power+VS1, another termination R2, Rsen1 and R2
The other end connect power ground simultaneously.
Resistance bridge B two-arm output voltage V1 and V2 access differential amplifier IC1 input terminal.Difference amplifier IC1 is put
Big multiple is controlled by resistance Rg.Output access multiplier M1, M2 of difference amplifier IC1, the sine of signal generator S1 output,
Cosine signal is respectively connected to multiplier M1, M2.Multiplier M1, M2 output signal accesses low-pass filter LPF1, LPF2, after filtering
Output signal access A/D analog-to-digital conversion after, be sent into MCU and handled, obtain amplitude and phase, and obtain blood coagulation process
In viscoelastic power.
The present invention is used to measure the viscoelastic force measuring method of micro blood sample, includes the following steps:
1. setting measuring device is put into temperature control box, the temperature of temperature control box is preheated, reaches the temperature value that detection needs.
2. pair blood sample and prothrombin time (PT) detection reagent carry out preheating reach test temperature after, suck respectively
Into micro-sampling syringe 8810,8820, the amount of blood sample and PT detection reagent is 1~10ul.
3. micro-sampling syringe 8810,8820 is promoted respectively with syringe pump 881,882, by blood sample and PT detection examination
Agent is injected into microchannel 81 simultaneously, blood sample and PT detection reagent be advanced to pressure drag decline hanging bridge 82 position of sensor when
Syringe pump 881,882 stops promoting.
4. blood viscoelastic power changes as blood sample is activated by PT detection reagent, pressure drag declines hanging bridge sensor
82 resonance characteristics change, and the voltage magnitude and phase for causing signal excitation detection circuit 10 to detect change.Pass through
The voltage value and phase measured, obtains the variation of blood viscoelastic power.
Fig. 5, Fig. 6 test curve are referred to as the general data of the present embodiment.
As shown in figure 5, this figure is output voltage change curve in micro blood sample viscoelastic power test process.
0~2 second period was that blood sample and PT detection reagent stage are not added, and pressure drag declines hanging bridge sensor in air
Middle resonance.
2~8 second period was that addition blood sample and PT detection reagent stage, pressure drag decline hanging bridge sensor from air
Resonance switchs to resonant process in a liquid, and in lasting input, voltage fluctuates this process liquids.
8~20 second period was that blood sample is activated by PT detection reagent, and blood sample starts to condense, and pressure drag declines hanging bridge
Sensor is influenced by blood clotting, and resonance damping becomes larger, and resonance amplitude becomes smaller, and voltage declines.
20~28 second period, blood sample condensation accelerate, and resonance amplitude becomes smaller rapidly, and dramatic decrease occurs in voltage.
28~32 second period, condensation is completed in most of blood sample, therefore rate of set weakens.
Period after 32 seconds, blood sample are basically completed condensation, and the pressure drag hanging bridge sensor resonant frequency that declines tends to
Gently, it is meant that detection is completed.
As shown in fig. 6, this figure is output phase change curve in micro blood sample viscoelastic power test process.
0~2 second period was that blood sample and PT detection reagent stage are not added, and pressure drag declines hanging bridge sensor in air
Middle resonance, phase is without significant change.
2~8 second period was that addition blood sample and PT detection reagent stage, pressure drag decline hanging bridge sensor from air
Resonance switchs to resonant process in a liquid, and in lasting input, phase fluctuates this process liquids.
8~20 second period was that blood sample is activated by PT detection reagent, and blood sample starts to condense, and pressure drag declines hanging bridge
Sensor is influenced by blood clotting, and resonance damping becomes larger, and resonance amplitude becomes smaller, and phase starts to reduce.
20~28 second period, blood sample condensation accelerate, and resonance amplitude becomes smaller rapidly, and dramatic decrease occurs in phase.
28~32 second period, condensation is completed in most of blood sample, therefore rate of set weakens.
Period after 32 seconds, blood sample are basically completed condensation, and the pressure drag hanging bridge sensor resonant frequency that declines tends to
Gently, it is meant that detection is completed.
Claims (10)
1. being declined the blood viscoelastic force measuring device of hanging bridge sensor based on pressure drag, it is characterised in that: including microfluidic device, institute
Stating microfluidic device includes substrate, and upper surface of base plate is carved with microchannel, and microchannel input terminal is dual-port, output end is single-ended
Mouthful, pressure drag is installed in microchannel and is declined hanging bridge sensor, liquid is after two input terminals flow into and converge by pressure resistance type
It is flowed out after micro- hanging bridge sensor from output end；
Permanent magnet, the permanent magnet are placed in microfluidic device two sides, for providing constant magnetic for the pressure drag hanging bridge sensor that declines
?；
Signal motivates detection circuit, and signal excitation detection circuit connection pressure drag declines hanging bridge sensor, for measuring blood
Viscous force variation in coagulation process.
2. being declined the blood viscoelastic force measuring device of hanging bridge sensor based on pressure drag as described in claim 1, it is characterised in that:
The pressure drag hanging bridge sensor that declines includes silicon base, and the U-shaped pressure drag that silicon base both ends are respectively provided with opening towards outside senses
With the electrified wire with autonomous channel, two ends, the two ends of electrified wire of pressure drag sensing are all connected with and are deposited on silicon base
On pad.
3. being declined the blood viscoelastic force measuring device of hanging bridge sensor based on pressure drag as claimed in claim 2, it is characterised in that:
The silicon base is in I-shaped, silicon base both ends setting support base, silicon base top layer deposition silica.
4. being declined the blood viscoelastic force measuring device of hanging bridge sensor based on pressure drag as claimed in claim 3, it is characterised in that:
The microchannel direction declines with pressure drag, and hanging bridge sensor hanging bridge direction is vertical, and permanent magnet magnetic line of force direction is perpendicular to micro- logical
Road direction.
5. being declined the blood viscoelastic force measuring device of hanging bridge sensor based on pressure drag as claimed in claim 4, it is characterised in that:
The pressure drag hanging bridge size sensor range that declines is that micro- hanging bridge is long: 200~300 μm, wide: it is 20~30 μm, thick: 1~5 μm, pressure
The silicon base support base height at resistive micro- hanging bridge sensor both ends is higher than intermediate silicon base thickness, and microchannel declines hanging bridge in pressure drag
Sensor portion bit wide be 200~300 μm, 5~50 μm of depth, remaining position width be 1~200 μm, 5~50 μm of depth, a length of 1~
10cm。
6. being declined the blood viscoelastic force measuring device of hanging bridge sensor based on pressure drag as claimed in claim 2, it is characterised in that:
The signal excitation detection circuit includes signal generator, resistance bridge, difference amplifier, multiplier, low pass filter, modulus
Conversion, microcontroller are generated just wherein the microcontroller is connected with signal generator by microcontroller control signals generator
String and cosine signal, signal generator decline the sinusoidal excitation signal source of generation access pressure drag hanging bridge sensor electrified wire institute
Corresponding pad.
7. being declined the blood viscoelastic force measuring device of hanging bridge sensor based on pressure drag as claimed in claim 6, it is characterised in that:
The resistance bridge by two fixed resistances and pressure drag decline hanging bridge sensor both ends two pressure drags sensing form, Hui Sidun
Electric bridge two-arm output voltage access differential amplifier in, difference amplifier amplification factor are controlled by non-essential resistance, and difference is put
The output of big device accesses two multipliers, and sine, the cosine signal of signal generator output are respectively connected to two multipliers, and two
It after multiplier output signal is by low-pass filtering and analog-to-digital conversion, is sent into microcontroller and is handled, obtain amplitude and phase, and
Obtain the viscoelastic power during blood coagulation.
8. being declined the blood viscoelastic force measuring device of hanging bridge sensor based on pressure drag as described in claim 1, it is characterised in that:
The substrate of the microfluidic device is divided into top substrate layer and underlying substrate, and underlying substrate is glass material, and top substrate layer is poly- two
Methylsiloxane material is simultaneously carved with microchannel, and top substrate layer is by splashing and being combined with underlying substrate after ion bombardment.
9. being declined the blood viscoelastic force measuring device of hanging bridge sensor based on pressure drag as described in claim 1, it is characterised in that:
The input terminal and output end of the microchannel are the identical cylindrical hole in aperture, and are separately connected silica gel hose, two input terminals
Silica gel hose connect micro-sampling syringe, the silica gel hose of output end connects waste liquid collection vessel.
10. it is a kind of using described in any one of claim 1~9 based on pressure drag decline hanging bridge sensor blood glue elastic force measurement fill
The measurement method set, which comprises the steps of:
Measuring device is put into temperature control box by step 1, is preheated to the temperature of temperature control box, and the temperature value that detection needs is reached；
Step 2, to blood sample and coagulation activation reagent carry out preheating reach test temperature after, be drawn into respectively micro-sampling note
In emitter, the amount of blood sample and coagulation activation reagent is 1~10ul；
Step 3 promotes micro-sampling syringe that blood sample and coagulation activation reagent are injected into microchannel simultaneously with syringe pump,
Blood sample and coagulation activation reagent be advanced to pressure drag decline hanging bridge sensor position when syringe pump stop promote；
Step 4, the reagent that is activated with blood sample activation, blood viscoelastic power changes, and the pressure drag hanging bridge sensor that declines is humorous
Vibration characteristic changes, and the voltage magnitude and phase for causing signal excitation detection circuit to detect change, and passes through what is measured
Voltage value and phase obtain the variation of blood viscoelastic power.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811261649.3A CN109142452B (en) | 2018-10-26 | 2018-10-26 | Blood viscoelastic force measuring device and method based on piezoresistive micro-suspension bridge sensor |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811261649.3A CN109142452B (en) | 2018-10-26 | 2018-10-26 | Blood viscoelastic force measuring device and method based on piezoresistive micro-suspension bridge sensor |
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| CN109142452B CN109142452B (en) | 2021-03-26 |
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| CN109142452B (en) | 2021-03-26 |
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