WO2016109925A1 - 血压测量仪及其气路结构以及气路盒 - Google Patents

血压测量仪及其气路结构以及气路盒 Download PDF

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Publication number
WO2016109925A1
WO2016109925A1 PCT/CN2015/070129 CN2015070129W WO2016109925A1 WO 2016109925 A1 WO2016109925 A1 WO 2016109925A1 CN 2015070129 W CN2015070129 W CN 2015070129W WO 2016109925 A1 WO2016109925 A1 WO 2016109925A1
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WO
WIPO (PCT)
Prior art keywords
air
port
interface
housing
detecting sensor
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PCT/CN2015/070129
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English (en)
French (fr)
Inventor
卢艺
侯文君
Original Assignee
深圳迈瑞生物医疗电子股份有限公司
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 深圳迈瑞生物医疗电子股份有限公司 filed Critical 深圳迈瑞生物医疗电子股份有限公司
Priority to CN201580029325.5A priority Critical patent/CN106413535B/zh
Priority to PCT/CN2015/070129 priority patent/WO2016109925A1/zh
Publication of WO2016109925A1 publication Critical patent/WO2016109925A1/zh
Priority to US15/641,032 priority patent/US10932675B2/en

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/02141—Details of apparatus construction, e.g. pump units or housings therefor, cuff pressurising systems, arrangements of fluid conduits or circuits
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
    • A61B5/02208—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers using the Korotkoff method
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
    • A61B5/0225—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers the pressure being controlled by electric signals, e.g. derived from Korotkoff sounds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
    • A61B5/6813—Specially adapted to be attached to a specific body part
    • A61B5/6824—Arm or wrist
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/022—Measuring pressure in heart or blood vessels by applying pressure to close blood vessels, e.g. against the skin; Ophthalmodynamometers
    • A61B5/0235—Valves specially adapted therefor

Definitions

  • the invention relates to a medical device, in particular to a blood pressure measuring instrument and a pneumatic circuit structure thereof and a pneumatic circuit box.
  • Blood pressure meters such as the Non-invasive measurement of blood pressure (NIBP) typically include a cuff and an internal airway structure attached to the cuff.
  • the internal pneumatic circuit structure includes components such as an air pump, an electromagnetic bleed valve, and a pneumatic sensor connected to the air passage.
  • NIBP can automatically control the air pump to charge and deflate the sleeve, and collect and process the human body pressure transmitted by the sleeve through the internal air path structure.
  • the various components of the internal gas path structure are generally connected by a multi-stage gas pipe and a 2-way and 3-way joint, so that the internal gas path structure of the NIBP is relatively dispersed, the integration degree is poor, and the volume is large.
  • the internal gas path structure is made up of scattered gas pipes and joints, and the gas path connection points are many, so that the reliability is not high.
  • a pneumatic circuit structure for use in a blood pressure measuring instrument comprising:
  • the air circuit box includes a housing having a cavity formed therein, and the housing is formed with an inlet, an inflation port and an air inlet, and the inlet, the inflation port and the air inlet are connected to the cavity ;
  • An air pump comprising an inflation interface, the interface being directly connected to the inflation port;
  • venting valve disposed on the housing and directly communicating with the air inlet
  • the air pressure detecting sensor is formed with an interface, and an interface of the air pressure detecting sensor directly communicates with the cavity of the housing;
  • the air pump, the deflation valve and the air pressure detecting sensor realize air pressure transmission in the cavity of the housing.
  • the sleeve nozzle is formed with a plug end, the plug end is inserted into the inlet of the housing, and the inflation port is inserted and connected to the housing.
  • the housing is further formed with a first interface and a second interface that communicate with the cavity
  • the air path structure further includes an overvoltage detecting sensor
  • the overvoltage detecting sensor is formed with an interface. The interface of the overvoltage detecting sensor and the interface of the air pressure detecting sensor are respectively inserted and connected to the first interface and the second interface.
  • the air inlet includes a first air outlet and a second air outlet that are spaced apart
  • the air release valve includes a spaced-apart slow air release valve and a quick air release valve.
  • One end of the gas valve is provided with a connection port
  • the connection port is inserted into the first air connection port
  • one end of the quick release valve is provided with a connection port
  • the connection port of the quick release valve is inserted and connected In the second air inlet.
  • the gas path box is made of a hard plastic material, the inflation port of the air pump, the insertion end of the sleeve nozzle, the connection port of the slow release valve, and the quick release valve.
  • the interface of the connection port, the overvoltage detecting sensor and the interface of the air pressure detecting sensor are respectively interfitted with the corresponding inflation port, the inlet port, the first air inlet port, the second air port, the first interface and the second interface.
  • the inflation port, the inlet port, the first air port, the second air port, the first port, and the second port are all formed of a flexible material or are provided with a flexible material around the circumference thereof to respectively
  • one side of the housing is further formed with an opening, and is provided with a cover that closes the opening, the opening communicates with the cavity, and the housing surrounds the cavity
  • the first interface and the second interface form a blocking rib, and the blocking rib is provided with an air outlet, and the air outlet is away from the inlet, the first air inlet and the second air inlet of the housing.
  • the airway box further includes a support portion extending outwardly from one end of the housing, the support portion including a first support portion and a second support portion spaced apart, the slow speed
  • the air release valve and the quick release valve are respectively disposed on the first support portion and the second support portion, and an end of the housing adjacent to the support portion corresponds to the first support portion and the first
  • the second support portion is respectively formed with a first stop and a second stop, the first air connection is formed on the first stop, and the second air connection is formed on the second stop.
  • the first air inlet and the second air inlet respectively face the first support portion and The second support portion.
  • the two sides of the first support portion and the second support portion are respectively formed with a bent edge, and the first support portion and the second support portion are formed with a partitioning edge, a first receiving portion is formed between the bent edge of the first supporting portion and the separating edge, and a second receiving portion is formed between the second bending edge and the separating edge, the slow The quick release air valve is received in the first receiving portion, and the quick release valve is received in the second receiving portion.
  • the first support portion is bent away from an end of the housing to form a stop edge, and the stop edge is provided with a notch, so that the stop edge is divided into two stops.
  • the slow deflation valve is blocked on the two blocking ends and partially protrudes outside the notch.
  • a bent edge of the second support portion extends away from an end of the housing toward the first support portion to form a hook, and the second support portion is convex away from an end of the housing.
  • a stop end is formed, and a stop protrusion is formed at one end of the quick release valve away from the connection port, and the stop protrusion is formed with a locking opening, and the blocking protrusion blocks the stop On the end, the hook is snapped into the latching opening of the quick release valve.
  • a blood pressure measuring instrument includes a body and a sleeve connected to the body, wherein the body is provided with a gas path structure and a main control circuit board as described above, the main control circuit board and the air pump, The pressure detecting sensor, the air pressure detecting sensor and the air discharging valve are electrically connected, and the sleeve is connected to the air passage structure.
  • the main control circuit board is mounted on the air circuit box by a snap, a post hole interference or a fastener.
  • the overvoltage detecting sensor and the air pressure detecting sensor are respectively provided with soldering legs, and the soldering feet of the overvoltage detecting sensor and the air pressure detecting sensor are soldered and integrated in the main control circuit. On the board.
  • a casing is formed at one end of the air passage box, and the inlet is formed on the protrusion and extends along a length direction of the air passage box, and the air inlet is adjacent to the air inlet
  • the protrusion is formed on the housing, and the protrusion is provided with a positioning post, and the two sides of the end of the housing adjacent to the protrusion are respectively formed with a buckle and a fixing post, and the main control circuit board a positioning hole is formed at one end thereof, and a locking notch is formed on one side and a locking position is formed on the other side, and a positioning post of the housing is inserted into the positioning hole of the main control circuit board,
  • the buckle is fastened to the locking position, and the fixing post is fixed to the locking gap And thereby fixing the main control circuit board to the air path box.
  • the blood pressure measuring instrument is an electronic non-invasive blood pressure measuring instrument.
  • a gas path box comprising:
  • a housing having a cavity formed therein, wherein the housing is formed with an inflation port and a communication port, and the inflation port and the communication port are both formed of a flexible material and communicate with the cavity, the inflation port and The communication port is configured to directly and airtightly cooperate with the corresponding pneumatic device, so that each pneumatic device realizes air pressure transmission or gas exchange in the cavity of the housing, and the inflation port is used to realize the orientation of the pneumatic circuit box
  • the inner inflation function is used to realize an outward exhaust or air pressure detecting function of the air path box.
  • the inflation port is for communicating with an air pump of the air pump, and the communication port is configured to directly communicate with the air pressure detecting sensor to implement a gas pressure detecting function of the air circuit box, and the housing is further An air inlet is further formed, and the air inlet is spaced apart from the air inlet and the communication port, and the air inlet is composed of a flexible material and communicates with the cavity, and the air inlet is used for the air outlet valve Direct airtight fit to achieve the outward exhaust function of the air circuit box.
  • the air pump, the cuff nozzle, the air pressure detecting sensor and the deflation valve are directly connected to the air path box, the integration degree is high, and the gas path structure is small in volume, and the direct connection mode is not
  • the air pipe is required to connect the above components, which reduces the possibility of air leakage and improves the connection reliability.
  • FIG. 1 is a perspective view of a blood pressure measuring instrument according to an embodiment
  • Figure 2 is a front elevational view showing the gas path structure of the blood pressure measuring instrument shown in Figure 1;
  • FIG. 3 is a perspective exploded view of the gas path structure shown in FIG. 2;
  • Figure 4 is a perspective view of the gas path box of the gas path structure shown in Figure 2;
  • Figure 5 is a perspective exploded view of another perspective view of the gas path structure shown in Figure 2;
  • Figure 6 is a perspective view of the air pump structure of the air pump structure of Figure 2 and the sleeve valve;
  • Figure 7 is a perspective view of the overpressure detecting sensor of the gas path structure shown in Figure 2;
  • Figure 8 is a perspective view of the air pressure detecting sensor of the pneumatic circuit structure shown in Figure 2;
  • Figure 9 is a perspective view of the slow bleed valve of the gas path structure shown in Figure 2;
  • Figure 10 is a perspective view of the quick release valve of the gas path structure shown in Figure 2;
  • Figure 11 is a perspective view of the main control circuit board of the gas path structure shown in Figure 2;
  • Fig. 12 is a perspective view showing the main control circuit board of the air passage structure of another embodiment.
  • the blood pressure measuring instrument 300 of the embodiment includes a body 180 and a sleeve 200 coupled to the body 180 .
  • the body 180 is provided with an air passage structure 100 connected to the sleeve 200 and a main control circuit board 80 electrically connected to the air passage structure 100 (please refer to FIG. 11).
  • the air passage structure 100 includes a pneumatic circuit box 10 and an air pump 20 connected to the air path box 10, a cuff nozzle 30, an overpressure detecting sensor 40, a gas pressure detecting sensor 50, a slow deflation valve 60, and a quick bleed valve 70.
  • the blood pressure measuring instrument 300 is an NIBP blood pressure measuring instrument.
  • the pneumatic circuit box 10 is substantially rectangular and is a closed air box made of a hard material such as a hard plastic.
  • the air circuit box 10 includes a housing 11 and a first support portion 13 and a second support portion 15 which are formed to extend side by side from the end of the housing 11.
  • the housing 11 is substantially in the shape of a square body, and a cavity 111 is formed therein (see Fig. 5).
  • a protrusion 112 is formed at one end of the housing 11 away from the first support portion 13 and an inflation port 113 is formed on a side adjacent to the protrusion 112.
  • the housing 11 is further formed with a buckle 114 and a fixing post 115 respectively on two sides of one end of the protrusion 112 , and a first interface 116 and a second interface 117 are formed between the buckle 114 and the fixing post 115 .
  • a first stopper 118 and a second stopper 119 are protruded from the first end of the first support portion 13 and the second support portion 15 , and the housing 11 is formed away from the side of the first interface 116 and the second interface 117 .
  • the housing 11 forms a ring of barrier ribs 1103 around the first interface 116 and the second interface 117 in the cavity 111.
  • a positioning post 1121 is protruded from the protrusion 112 and an inlet 1125 is formed in communication with the cavity 111.
  • the inlet 1125 extends along the length of the air path box 10.
  • the inflation port 113 communicates with the cavity 111.
  • the fixing column 115 is a rubber column.
  • the center connection of the first interface 116 and the second interface 117 is oblique to the longitudinal direction of the air path box 10.
  • the first stopper 118 and the second stopper 119 are located at an end of the housing 11 adjacent to the first support portion 13 and the second support portion 15.
  • a support post 1181 is convexly disposed on the first stopper 118, and a first air inlet 1183 facing the first support portion 13 is formed.
  • the top of the support post 1181 is flush with the top of the fixed post 115.
  • the second stopper 119 is formed with a second air inlet 1191 toward the second support portion 15.
  • the first air inlet 1183 and the second air inlet 1191 are both in communication with the cavity 111.
  • the opening 110 communicates with the cavity 111 and the outside, and a stepped stop surface 1102 is formed around the circumference of the cavity 111.
  • the barrier ribs 1103 respectively define an inner ring 1111 and an outer ring 1113, and an air outlet 1104 is further disposed on the blocking rib 1103 to communicate the inner ring 1111 and the outer ring 1113.
  • the air outlet 1104 is away from the inlet 11125 of the housing 11.
  • the air inlet 1183 and the second air inlet 1191 reduce the airflow disturbance generated by the air pump 20, the slow air release valve 60 and the quick air release valve 70 in the outer ring 1113 of the cavity 111 to the inner ring 1111.
  • the direct influence of the overpressure detecting sensor 40 and the air pressure detecting sensor 50 are examples of the overpressure detecting sensor 40 and the air pressure detecting sensor 50.
  • a sealing surface 1105 is formed on one side of the cover 1101, and the blocking surface 1102 is fitted through the sealing surface 1105 to close the opening 110.
  • the cover 1101 is sealed to the opening 110 by gluing or ultrasonic welding.
  • the inflation port 113, the inlet 1125, the first interface 116, the second interface 117, the first air inlet 1183, and the second air port 1191 on the housing 11 are all made of a flexible material or surround the periphery thereof.
  • a flexible material is provided to achieve the seal.
  • the flexible material may be a flexible plastic or silicone material or a silicone gel material.
  • the first support portion 13 and the second support portion 15 are both plate-shaped, and the two sides of the first support portion 13 and the second support portion 15 are separated from each other to form vertically extending bent edges 131 and 151, and the first support portion
  • a partitioning edge 132 is formed between the 13 and the second support portion 15.
  • the bent sides 131, 151 and the dividing edge 132 are both on the side away from the opening 110.
  • a first accommodating portion 133 is formed between the bent side 131 and the partitioning edge 132
  • a second accommodating portion 153 is formed between the bent side 151 and the partitioning edge 132 .
  • the bent side 151 extends away from the end of the housing 11 toward the bent side 131 to form a hook 155.
  • the first support portion 13 is bent away from an end of the housing 11 to form a stop edge 135.
  • a notch 1351 is defined in the middle of the stop edge 135 such that the stop edge 135 is divided into two first stop ends 1353.
  • a second stopping end 157 protrudes from an end of the second supporting portion 15 away from the housing 11 .
  • the second stop end 157 is on the side of the second support portion 15 adjacent to the first support portion 13 and extends toward the bent side 131.
  • the second stop end 157 and the partition edge 132 are spaced apart from each other.
  • the air pump 20 is disposed at one side of the housing 11 and directly connected to the housing 11.
  • the air pump 20 is formed with an inflation interface 21, and the inflation interface 21 is detachably inserted into the inflation port 113 of the housing 11.
  • the flexible sealing material on the inflation port 113 allows the inflation interface 21 to achieve an interference sealing fit with the inflation port 113.
  • the inflation port 113 can correspondingly inflate the outer ring 1113 of the cavity 111.
  • the cuff nozzle 30 is directly connected to one end of the housing 11.
  • the sleeve nozzle 30 is formed with a plug end 31, and the plug end 31 is detachably inserted into the inlet 1125 of the housing 11 to connect the sleeve nozzle 30 and the air box 10.
  • the flexible sealing material in the access port 1125 allows the plug end 31 to achieve an interference sealing fit with the access port 1125.
  • the overpressure detecting sensor 40 is disposed side by side with the air pressure detecting sensor 50 on the casing 11 and directly connected to the casing 11.
  • An interface 41 is formed on the overvoltage detecting sensor 40, and soldering legs 43 are formed on both sides.
  • the interface 41 of the overvoltage detecting sensor 40 is detachably inserted into the first interface 116 of the housing 11 to directly connect with the cavity 111.
  • the flexible sealing material of the first interface 116 causes the overvoltage detecting sensor 40 and the first interface 116 interference seal fit.
  • the soldering feet 43 are soldered to the main control board 80.
  • the air pressure detecting sensor 50 is formed with an interface 51, and soldering legs 53 are formed on both sides.
  • the interface 51 of the air pressure detecting sensor 50 is detachably inserted into the second interface 117 of the housing 11 to be directly connected to the cavity 111.
  • the flexible sealing material of the second interface 117 causes the air pressure detecting sensor 50 and the second interface 117 to pass. Surround seal fit.
  • the soldering feet 53 are soldered to the main control board 80.
  • the interface 41 of the overvoltage detecting sensor 40 is located in the inner cavity 1111 of the cavity 111 corresponding to the interface 51 of the air pressure detecting sensor 50.
  • the slow release valve 60 is received in the first receiving portion 133 and directly connected to the housing 11 .
  • the slow release valve 60 is provided with a connection port 61 at one end and a stopper projection 63 at the periphery of the other end.
  • the connecting port 61 is detachably inserted into the first air inlet 1183.
  • the flexible sealing material of the first air port 1183 allows the slow air venting valve 60 to have an interference sealing fit with the air box 10.
  • the other end portion of the slow deflation valve 60 protrudes beyond the notch 1351 of the housing 11, and the blocking projection 63 is blocked by the two first stopper ends 1353.
  • the quick release valve 70 is received in the second receiving portion 153 and directly connected to the housing 11 .
  • One end of the quick release valve 70 is provided with a connection port 71, and a stopper projection 73 is formed on each of the other ends, and a locking port 75 is formed on the stopper projection 73.
  • the connecting port 71 is detachably inserted into the second air inlet 1191, and the flexible sealing material of the second air port 1191 causes the quick air release valve 70 to have an interference sealing fit with the air box 10.
  • the second stop end 157 blocks a stop projection 73 of the quick bleed valve 70. Card of the second support portion 15
  • the hook 155 snaps into the locking opening 75 of the other stopper projection 73.
  • the connection port 61 of the slow release valve 60 and the connection port 71 of the quick release valve 70 may correspond to the gas in the outer ring 1113 of the discharge chamber 111.
  • the main control circuit board 80 is covered on the air path box 10.
  • the main control circuit board 80 can be mounted on the air circuit box 10 by means of a snap or interference hole post or fastener.
  • the main control circuit board 80 includes a circuit module 81, and a positioning hole 83 is formed in a corner portion of the main control circuit board 80, and a locking notch 85 is formed on one side.
  • the main control board 80 also has a locking position 87 on a side away from the locking notch 85.
  • the circuit module 81 is electrically connected to the air pump 20, the overpressure detecting sensor 40, the air pressure detecting sensor 50, the slow deflation valve 60, and the fast deflation valve 70 to collect data of the overpressure detecting sensor 40 and the air pressure detecting sensor 50.
  • the air pump 20, the slow deflation valve 60 and the quick deflation valve 70 are electrically controlled.
  • the positioning post 1121 of the housing 11 is inserted into the positioning hole 83 of the main control circuit board 80, the buckle 114 is fastened to the locking position 87, and the fixing post 115 is fixed to the periphery of the locking notch 85 by screws, so that the main control The circuit board 80 is fixed to the air circuit box 10 while the support post 1181 of the first stop 118 abuts against the main control circuit board 80.
  • the air pump 20 When the blood pressure measuring instrument 300 is assembled, the air pump 20 is inserted into the inlet 113 of the casing 11 such that the air pump 20 is disposed at one side of the air path casing 10.
  • the cuff nozzle 30 is inserted into the inlet 1125 of the housing 11 such that the cuff nozzle 30 is located at one end of the manifold.
  • the overvoltage detecting sensor 40 and the air pressure detecting sensor 50 are respectively inserted into the first interface 116 and the second interface 117.
  • the slow bleed valve 60 and the quick bleed valve 70 are respectively inserted and connected to the first air inlet 1183 and the second air port 1191.
  • the main control circuit board 80 is clamped on the air circuit box 10, and the circuit module 81 and the air pump 20, the overpressure detecting sensor 40, the air pressure detecting sensor 50, the slow deflation valve 60, and the quick deflation valve 70 are electrically connected. connection.
  • the air passage structure 200 is disposed in the body 180, and the sleeve 200 is coupled to the cuff nozzle 30.
  • the main control circuit board 80 controls the air pump 20 to inflate the air circuit box 10, and inflates the cuff cover 30 to the cuff 200, so that the cuff 200 is filled with gas and is inflated to fit the person. Arm.
  • the pressure within the cuff 200 rises rapidly in a short period of time and blocks arterial blood flow, during which the overpressure detecting sensor 40 can detect an overpressure in the cuff 200.
  • the main control circuit board 80 controls the slow deflation valve 60 to start deflation and decompression.
  • the pressure in the cuff 200 is reduced to the arterial blood pressure, the blood can pass through the arterial blood vessel and generate an oscillating wave, and the oscillating wave propagates through Air pressure detecting sensor 50.
  • the air pressure detecting sensor 50 detects the pressure and the fluctuation in the cuff 200 in real time, and the pressure in the cuff 200 corresponding to the maximum amplitude of the oscillation wave corresponds to the average arterial blood pressure, and the detection ends. Then, the main control board 80 controls the quick deflation valve 70 to deflate to make the sleeve Set 200 slack.
  • the NIBP pneumatic circuit structure 100 is directly connected to and houses the fixed air pump 20, the cuff nozzle 30, the overpressure detecting sensor 40, the air pressure detecting sensor 50, the slow deflation valve 60, and the quick deflation valve. 70, the above components are concentrated in the cavity 111 of the air path box 10 to achieve air pressure transmission, and thus the degree of integration is high. Moreover, a gas path box 10 is used to bring together the gas path connections of the components, thereby eliminating the connection points required for the gas path connection between the previously dispersed components, effectively simplifying the gas path, reducing the complexity of the gas path, and reducing the volume of the gas path. It reduces the possibility of gas leakage in the gas path and improves the reliability of its connection.
  • the gas path box 10 is made of hard plastic material, and does not have abnormalities such as gas path distortion, deformation, assembly interference and pressure blockage which are often used in the past, which can simplify the assembly requirements and improve the product yield. .
  • each inlet of the gas path box 10 is provided with a flexible sealing material, and is connected with each functional component without other sealing parts, and the assembly is convenient, the links are reduced, and the components can be reliably and effectively connected.
  • Each inlet port is connected to each component through a flexible sealing material to achieve an interference connection, which is compatible with the dimensional tolerance range of each component inlet to ensure airtightness.
  • the integrated system of the NIBP pneumatic circuit structure 100 can realize a compact gas path structure and bring about a small size for the whole machine.
  • the integrated gas path structure with the gas path box 10 as the core has been modularized, and it is very convenient to transplant in each product, which accelerates the development speed of the product.
  • the overvoltage detecting sensor 40' and the air pressure detecting sensor 50' are integrated on the main control board 80' and electrically connected to the circuit module 81'.
  • the overvoltage detecting sensor 40' and the air pressure detecting sensor 50' may be previously disposed on the main control board 80' by surface mounting such as soldering.
  • the last deflation of the cuff 200 can be achieved with only one slow deflation valve 60, at which time the quick deflation valve 70 can be omitted, the second stop 119 and the second of the housing 11
  • the support arm 15 can be omitted.
  • the measurement of the cuff pressure may be accomplished with only one air pressure detecting sensor 50, in which case the overpressure detecting sensor 40 may be omitted.
  • the air pressure measurement of the pneumatic system can be performed by only one air pressure detecting sensor 50, and when the measured air pressure reaches the upper limit of the working air pressure, it stops. The inflation is continued, and the program operation of the blood pressure measurement is started, that is, the air pressure detecting sensor 50 simultaneously performs the functions of the air pressure measurement and the measurement of the maximum protection air pressure, and at this time, the first interface 116 on the housing 11 can be omitted.
  • a support portion connected to the casing 11 may be added to the air passage box 10 to achieve accommodation and fixing of the air pump 20. It can be understood that when the slow release valve 60 and the quick release valve 70 are stably fixed to the housing 11, the first support portion 13 and the second support portion 15 can be omitted.
  • an interface tube can be formed on the casing 11 of the pneumatic circuit box 10 instead of the cuff nozzle 30.
  • the pneumatic circuit box 10 and the components are integrally designed, and the components can be designed to be different in other positions, and then the structural shape of the pneumatic circuit box 10 is adjusted to adaptively connect the components.
  • various components such as air pumps, bleed valves, sensors, air nozzles, etc., may be of other types or types, such as other front compression seal sensors, or other components that need to be involved in the pneumatic system. Either changing the number of components or reducing the access of some components to achieve configuration differentiation, while assisting other conventional forms such as silicone gas pipe forms, connecting components that are not directly connected to the gas path cartridge 10.
  • the gas path box 10 can be divided into multiple parts according to the specific layout requirements of the product, and each part is connected with two or more parts, and the gas path box 10 is connected by a conventional method such as a silicone gas pipe.
  • the splitting of the pneumatic circuit box 10 can reduce the connection of the local air path, and can also appropriately reduce the air path node.
  • the inlet of the pneumatic circuit box 10 can also be made entirely of a flexible material, not just a self-contained flexible sealing material.
  • the gas path box 10 and its inlet can also be made of a hard material such as a hard plastic, and the inlet is directly connected to the inlet of each component.
  • the gas path box 10 can also be made of a hard material such as plastic, and a flexible material such as an O-ring is used at the inlet to assist the sealing connection between the gas path box 10 and the component inlet.
  • the upper surface can be equivalent to the combination of the pneumatic rubber box 10 hard rubber soft glue.
  • the air path box 10 can be adjusted as a combination of a box body and a plurality of covers, or a combination of a plurality of boxes and a plurality of covers as needed, and at the same time, the access ports of the components can be designed in the box as needed.
  • the gas path box 10 can be divided into a structural fixing function part and a gas path connecting function part, the number is two parts or more parts, and the fixed part of the fixed pump, the valve, the sensor and the like are integrated by the structural fixing part, and the form is a single gas volume multi-trache tube.
  • the gas path components of the outlet are connected to each other.
  • the gas path box 10 in the variation scheme is connected with various components such as a pump, a valve and a sensor to form a gas path system, and the gas path box 10 forms a preliminary hole-axis connection relationship with each component at the interface, and does not achieve complete freedom degree constraint, and the gas path
  • the fixing of the components and the pneumatic circuit box 10 in the system is accomplished by adding additional components or upper and lower casings of the product to complete the final fixing.
  • the air passage box 10 can also be provided only with the inflation port 113 and the first air connection port 1183, or only The inflation port 113 is connected to the first interface 116 (for detecting air pressure).
  • the first air inlet 1183 and the first interface 116 are communication ports corresponding to respective functions.
  • a plurality of communication ports (ie, function interfaces) of other functions may be disposed on the air path box 10.

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Abstract

一种血压测量仪(300)及其气路结构(100)，以及气路盒(10)。所述气路结构(100)包括气路盒(10)、充气泵(20)、袖套气嘴(30)、放气阀(60,70)及气压检测传感器(50)。所述气路盒(10)包括内部形成有腔体(111)的壳体(11)，所述壳体(11)上还间隔形成有接入口(1125)、充气口(113)及接气口(1183,1191)，所述接入口(1125)、充气口(113)以及所述接气口(1183,1191)均与所述腔体(111)连通。所述充气泵(20)包括充气接口(21)，所述接口(21)直接连通于所述充气口(113)。所述袖套气嘴(30)与所述接入口(1125)直接连通，所述放气阀(70)设置于所述壳体(11)上并直接连通所述接气口(1183,1191)。所述气压检测传感器(50)直接连通所述壳体(11)的腔体(111)。所述气路结构(100)使得所述血压测量仪(300)体积较小且可靠性较高。

Description

血压测量仪及其气路结构以及气路盒 【技术领域】
本发明涉及一种医疗器械，尤其涉及一种血压测量仪及其气路结构以及气路盒。
【背景技术】
血压测量仪，如电子无创血压测量仪(NIBP，Non-invasive measurement of blood pressure)一般包括袖套及连接至袖套上的内部气路结构。内部气路结构包括连接至气路上的充气泵、电磁放气阀、气压传感器等部件。NIBP可自动控制充气泵对袖套进行充、放气，并通过内部气路结构对袖套传递过来的人体压力进行采集处理。
然而，内部气路结构的各部件之间一般是使用多段气管以及2通、3通接头连接，使得NIBP的内部气路结构较为分散，集成度差且体积较大。另外，该内部气路结构由零散的气管及接头搭接而成，气路接驳点多，使得其可靠性不高。
【发明内容】
基于此，有必要提供一种体积较小且可靠性较高的气路结构及采用该气路结构的血压测量仪，以及气路盒。
一种气路结构，应用于血压测量仪中，包括：
气路盒，包括内部形成有腔体的壳体，所述壳体上间隔形成有接入口、充气口及接气口，所述接入口、充气口以及所述接气口均与所述腔体连通；
充气泵，包括充气接口，所述接口直接连通于所述充气口；
袖套气嘴，与所述接入口直接连通；
放气阀，设置于所述壳体上并直接连通所述接气口；以及
气压检测传感器，形成有接口，所述气压检测传感器的接口直接连通所述壳体的腔体；
其中，所述充气泵、放气阀及气压检测传感器于所述壳体的腔体内实现气压传递。
在其中一个实施例中，所述袖套气嘴上形成有插接端，所述插接端插设连接于所述壳体的接入口中，所述充气接口插设连接于所述壳体的充气口中，所述壳体上还形成有与所述腔体连通的第一接口与第二接口，所述气路结构还包括过压检测传感器，所述过压检测传感器形成有接口，所述过压检测传感器的接口及所述气压检测传感器的接口分别插设连接于所述第一接口与所述第二接口中。
在其中一个实施例中，所述接气口包括间隔设置的第一接气口与第二接气口，所述放气阀包括间隔设置的慢速放气阀和快速放气阀，所述慢速放气阀的一端设有连接口，所述连接口插设连接于所述第一接气口中，所述快速放气阀的一端设有连接口，所述快速放气阀的连接口插设连接于所述第二接气口中。
在其中一个实施例中，所述气路盒由硬塑胶材料制成，所述充气泵的充气接口、袖套气嘴的插接端、慢速放气阀的连接口、快速放气阀的连接口、过压检测传感器的接口及气压检测传感器的接口分别过盈配合于对应的充气口、接入口、第一接气口、第二接气口、第一接口及第二接口中。
在其中一个实施例中，所述充气口、接入口、第一接气口、第二接气口、第一接口及第二接口均由柔性材料构成或环绕自身周缘设有柔性材料，以分别与所述充气泵的充气接口、袖套气嘴的插接端、慢速放气阀的连接口、快速放气阀的连接口、过压检测传感器的接口及气压检测传感器的接口密封连接。
在其中一个实施例中，所述壳体的一侧还形成有开口，并设有封闭所述开口的封盖，所述开口连通所述腔体，所述壳体于所述腔体内环绕所述第一接口与所述第二接口形成阻挡筋，所述阻挡筋上开设有出气口，所述出气口远离所述壳体的接入口、第一接气口及第二接气口。
在其中一个实施例中，所述气路盒还包括由所述壳体一端向外延伸形成的支撑部，所述支撑部包括间隔设置的第一支撑部与第二支撑部，所述慢速放气阀和所述快速放气阀分别设置于所述第一支撑部与所述第二支撑部上，所述壳体邻近所述支撑部的一端对应所述第一支撑部及所述第二支撑部分别凸设有第一挡块与第二挡块，所述第一接气口形成于所述第一挡块上，所述第二接气口形成于所述第二挡块上，所述第一接气口与第二接气口分别朝向所述第一支撑部与 所述第二支撑部。
在其中一个实施例中，所述第一支撑部与所述第二支撑部相互远离的两侧分别形成有弯折边，且所述第一支撑部与所述第二支撑部之间形成有分隔边，所述第一支撑部的弯折边与所述分隔边之间形成第一收容部，所述第二弯折边与所述分隔边之间形成有第二收容部，所述慢速放气阀收容于所述第一收容部中，所述快速放气阀收容于所述第二收容部中。
在其中一个实施例中，所述第一支撑部远离所述壳体的一端弯折形成挡止边，所述挡止边上开设有缺口，从而使得所述挡止边分隔成两个挡止端，所述慢速放气阀挡止于所述两个挡止端上并部分凸伸于所述缺口外。
在其中一个实施例中，所述第二支撑部的弯折边远离所述壳体的一端朝所述第一支撑部延伸形成卡钩，所述第二支撑部远离所述壳体的一端凸伸有挡止端，所述快速放气阀远离其连接口的一端形成有挡止凸块，所述挡止凸块上形成有卡止口，所述挡止凸块挡止于所述挡止端上，所述卡钩卡入所述快速放气阀的卡止口中。
一种血压测量仪，包括本体及连接于所述本体上的袖套，所述本体内设有如上所述的气路结构及主控电路板，所述主控电路板与所述充气泵、压检测传感器、气压检测传感器及所述放气阀电性连接，所述袖套连接于所述气路结构上。
在其中一个实施例中，所述主控电路板通过卡扣、柱孔过盈或者紧固件装设于所述气路盒上。
在其中一个实施例中，所述过压检测传感器及所述气压检测传感器上均设置有焊接脚，所述过压检测传感器与所述气压检测传感器的焊接脚均焊接集成于所述主控电路板上。
在其中一个实施例中，所述气路盒的壳体一端形成有凸起，所述接入口形成于所述凸起上并沿所述气路盒的长度方向延伸，所述充气口邻近所述凸起形成于所述壳体上，所述凸起上设有定位柱，所述壳体邻近所述凸起的一端的两侧分别形成有卡扣和固定柱，所述主控电路板的一端开设有定位孔，并于一侧开设有卡止缺口且于另一侧形成有卡止位，所述壳体的定位柱插设于所述主控电路板的定位孔中，所述卡扣扣合于所述卡止位，所述固定柱固定于所述卡止缺口 中，从而将所述主控电路板固定于所述气路盒上。
在其中一个实施例中，所述血压测量仪为电子无创血压测量仪。
一种气路盒，包括：
壳体，内部形成有腔体，所述壳体上间隔形成有充气口与连通口，所述充气口与所述连通口均由柔性材料构成并与所述腔体连通，所述充气口及连通口用于与对应的气路器件直接气密配合，以使各气路器件于所述壳体的腔体内实现气压传递或气体交换，所述充气口用于实现所述气路盒的向内充气功能，所述连通口用于实现所述气路盒的向外排气或者气压检测功能。
在其中一个实施例中，所述充气口用于与充气泵气路连通，所述连通口用于与气压检测传感器直接连通以实现所述气路盒的气压检测功能，所述壳体还上还形成有接气口，所述接气口与所述充气口及所述连通口间隔设置，所述接气口均由柔性材料构成并与所述腔体连通，所述接气口用于与放气阀直接气密配合，以实现所述气路盒的向外排气功能。
由于充气泵、袖套气嘴、气压检测传感器及放气阀均直接连接于气路盒上，使得其集成度较高，进而使得该气路结构体积较小，而且这种直接连接方式，不再需要气管来连接上述各部件，减少了气路的漏气可能性，提高了其连接可靠性。
【附图说明】
通过附图中所示的本发明的优选实施例的更具体说明，本发明的上述及其它目的、特征和优势将变得更加清晰。在全部附图中相同的附图标记指示相同的部分，且并未刻意按实际尺寸等比例缩放绘制附图，重点在于示出本发明的主旨。
图1为一实施例的血压测量仪的立体示意图；
图2为图1所示血压测量仪的气路结构的主视图；
图3为图2所示气路结构的立体分解示意图；
图4为图2所示气路结构的气路盒的立体示意图；
图5为图2所示气路结构的另一视角的立体分解示意图；
图6为图2所示气路结构的充气泵与袖套气嘴的立体示意图；
图7为图2所示气路结构的过压检测传感器的立体示意图；
图8为图2所示气路结构的气压检测传感器的立体示意图；
图9为图2所示气路结构的慢速放气阀的立体示意图；
图10为图2所示气路结构的快速放气阀的立体示意图；
图11为图2所示气路结构的主控电路板的立体示意图；
图12为另一实施例的气路结构的主控电路板的立体示意图。
【具体实施方式】
为使本发明的上述目的、特征和优点能够更加明显易懂，下面结合附图对本发明的具体实施方式做详细的说明。在下面的描述中阐述了很多具体细节以便于充分理解本发明。但是本发明能够以很多不同于在此描述的其它方式来实施，本领域技术人员可以在不违背本发明内涵的情况下做类似改进，因此本发明不受下面公开的具体实施的限制。
请参阅图1及图2，一实施例的血压测量仪300包括本体180及连接于本体180上的袖套200。本体180内设有连接于袖套200上的气路结构100以及与气路结构100电性连接的主控电路板80(请参见图11)。气路结构100包括气路盒10以及连接于气路盒10上的充气泵20、袖套气嘴30、过压检测传感器40、气压检测传感器50、慢速放气阀60以及快速放气阀70。在本实施例中，所述血压测量仪300为NIBP血压测量仪。
请参阅图3至图5，气路盒10大致呈矩形状，为一个由硬性材料如硬塑胶制成的封闭气盒。气路盒10包括壳体11及从壳体11一端并列向外延伸形成的第一支撑部13及第二支撑部15。
壳体11大致呈方体状，并于其内形成有腔体111(参见图5)。壳体11远离第一支撑部13的一端形成有凸起112并邻近凸起112的一侧形成有充气口113。壳体11还于邻近凸起112的一端的两侧分别形成有卡扣114和固定柱115，且于卡扣114和固定柱115之间形成有第一接口116与第二接口117。壳体11邻近第一支撑部13与第二支撑部15的一端凸设有第一挡块118与第二挡块119，且壳体11背离第一接口116与第二接口117的一侧形成有开口110，并设有封闭开口110的封盖1101。壳体11于腔体111内环绕第一接口116与第二接口117形成一圈阻挡筋1103。
凸起112上凸设有定位柱1121并形成有与腔体111连通的接入口1125，接入口1125沿气路盒10的长度方向延伸。充气口113与腔体111相通。固定柱115为胶柱。第一接口116与第二接口117的中心连线与气路盒10的长度方向斜交。第一挡块118与第二挡块119位于壳体11邻近第一支撑部13与第二支撑部15的端部。第一挡块118上凸设有支撑柱1181，并形成有朝向第一支撑部13的第一接气口1183。支撑柱1181的顶部与固定柱115的顶部平齐。第二挡块119朝向第二支撑部15形成有第二接气口1191。第一接气口1183及第二接气口1191均与腔体111连通。
开口110连通腔体111与外界，并环绕腔体111的周缘形成有台阶状的挡止面1102。阻挡筋1103将腔体111分别为内圈1111及外圈1113，阻挡筋1103上还开设有出气口1104以连通内圈1111与外圈1113，出气口1104远离壳体11的接入口1125、第一接气口1183及第二接气口1191，从而减少充气泵20、慢速放气阀60及快速放气阀70在腔体111的外圈1113充放气产生的气流扰动对内圈1111中的过压检测传感器40与气压检测传感器50的直接影响。封盖1101一侧形成有密封面1105，并通过密封面1105贴合挡止面1102以封闭开口110。在本实施方式中，封盖1101通过涂胶或超声波焊接与封闭于开口110上。在本实施方式中，壳体11上的充气口113、接入口1125、第一接口116、第二接口117、第一接气口1183及第二接气口1191均由柔性材料制成或者环绕自身周缘设置有柔性材料，以实现密封。所述柔性材料可以为柔性塑胶或者硅胶材料或者硅凝胶材料。
第一支撑部13与第二支撑部15均为板状，第一支撑部13与第二支撑部15相互远离的两侧分别形成有垂直延伸的弯折边131、151，且第一支撑部13与第二支撑部15之间形成有分隔边132。弯折边131、151与分隔边132均处于背离开口110的一侧。弯折边131与分隔边132之间形成第一收容部133，弯折边151与分隔边132之间形成有第二收容部153。弯折边151远离壳体11的一端朝弯折边131延伸形成卡钩155。第一支撑部13远离壳体11的一端弯折形成挡止边135。挡止边135中部开设有缺口1351，从而使得挡止边135分隔成两个第一挡止端1353。第二支撑部15远离壳体11的一端凸伸有第二挡止端157。第二挡止端157处于第二支撑部15邻近第一支撑部13的侧边上且朝弯折边131延伸。第二挡止端157与分隔边132相互间隔设置。
请一并参阅图6，充气泵20设置于壳体11的一侧并与壳体11直接连接。充气泵20上形成有充气接口21，充气接口21可拆卸地插设连接于壳体11的充气口113中，充气口113上的柔性密封材料使得充气接口21与充气口113实现过盈密封配合。充气口113可对应向腔体111的外圈1113进行充气。
袖套气嘴30直接连接于壳体11的一端。袖套气嘴30上形成有插接端31，插接端31可拆卸地插设连接于壳体11的接入口1125中，以连接袖套气嘴30与气路盒10。接入口1125中的柔性密封材料使得插接端31与接入口1125实现过盈密封配合。
请参阅图7，过压检测传感器40与气压检测传感器50并排设置于壳体11上并与壳体11直接连接。过压检测传感器40上形成有接口41，并于两侧分别形成有焊接脚43。过压检测传感器40的接口41可拆卸地插设连接于壳体11的第一接口116中以与腔体111直接连接，第一接口116的柔性密封材料使得过压检测传感器40与第一接口116过盈密封配合。焊接脚43焊接于主控电路板80上。
请参阅图8，气压检测传感器50形成有接口51，并于两侧分别形成有焊接脚53。气压检测传感器50的接口51可拆卸地插设连接于壳体11的第二接口117中以与腔体111直接连接，第二接口117的柔性密封材料使得气压检测传感器50与第二接口117过盈密封配合。焊接脚53焊接于主控电路板80上。过压检测传感器40的接口41与气压检测传感器50的接口51对应位于腔体111的内腔1111。
请参阅图9，慢速放气阀60收容于第一收容部133中且与壳体11直接连接。慢速放气阀60的一端设有连接口61，并于另一端的周缘形成有挡止凸块63。连接口61可拆卸地插设连接于第一接气口1183中，第一接气口1183的柔性密封材料使得慢速放气阀60与气路盒10过盈密封配合。慢速放气阀60的另一端部分凸伸于壳体11的缺口1351外，而挡止凸块63挡止于两个第一挡止端1353上。
请参阅图10，快速放气阀70收容于第二收容部153中且与壳体11直接连接。快速放气阀70的一端设有连接口71，并于另一端的两侧分别形成有挡止凸块73，挡止凸块73上形成有卡止口75。连接口71可拆卸地插设连接于第二接气口1191中，第二接气口1191的柔性密封材料使得快速放气阀70与气路盒10过盈密封配合。第二挡止端157挡止快速放气阀70的一个挡止凸块73上。第二支撑部15的卡 钩155卡入另一个挡止凸块73的卡止口75中。慢速放气阀60的连接口61及快速放气阀70的连接口71可对应排出腔体111的外圈1113内的气体。
请参阅图11，主控电路板80盖设于气路盒10上。主控电路板80可通过卡扣或者过盈孔柱或者紧固件装设于气路盒10上。在本实施方式中，主控电路板80包括电路模块81，且主控电路板80的角部上开设有定位孔83，并于一侧边开设有卡止缺口85。主控电路板80还于远离卡止缺口85的一侧开设有卡止位87。电路模块81与充气泵20、过压检测传感器40、气压检测传感器50、慢速放气阀60及快速速放气阀70电性连接，以采集过压检测传感器40及气压检测传感器50的数据并对充气泵20、慢速放气阀60及快速放气阀70进行电性控制。壳体11的定位柱1121插设于主控电路板80的定位孔83中，卡扣114卡扣于卡止位87上，固定柱115通过螺钉固定于卡止缺口85周缘，从而将主控电路板80固定于气路盒10上，同时第一挡块118的支撑柱1181抵持于主控电路板80上。
组装血压测量仪300时，将充气泵20插设连接于壳体11的接入口113中，以使充气泵20设置于气路盒10的一侧。将袖套气嘴30插设连接于壳体11的接入口1125中，以使袖套气嘴30位于气路盒10的一端。将过压检测传感器40与气压检测传感器50分别插设连接于第一接口116及第二接口117中。将慢速放气阀60及快速放气阀70分别插设连接于第一接气口1183及第二接气口1191上。将主控电路板80卡设于气路盒10上，并使电路模块81与充气泵20、过压检测传感器40、气压检测传感器50、慢速放气阀60及快速放气阀70电性连接。将气路结构200设置于本体180内，将袖套200连接于袖套气嘴30上。
血压测量仪300工作时，主控电路板80控制充气泵20对气路盒10充气，并使袖套气嘴30对袖套200进行充气，使袖套200充满气体并胀紧以贴紧人的胳膊。袖套200内的压力在短时间迅速上升并阻断动脉血流，在此过程中，过压检测传感器40能检测袖套200内是否过压。主控电路板80控制慢速放气阀60开始放气减压，当袖套200内的压力减小到动脉血压大小时，血液能通过动脉血管并随之产生振荡波，振荡波通过传播到气压检测传感器50。气压检测传感器50实时检测袖套200内的压力及波动，振荡波幅度最大点对应的袖套200内压力相当于平均动脉血压，此时检测结束。然后，主控电路板80控制快速放气阀70放气，以使袖 套200松弛。
NIBP气路结构100以气路盒10为核心，直接连接并收容固定充气泵20、袖套气嘴30、过压检测传感器40、气压检测传感器50、慢速放气阀60及快速放气阀70，使得上述各部件集中于气路盒10的腔体111内实现气压传递，因而其集成度较高。而且采用一个气路盒10把各部件的气路连接集合在一起，消除了以往分散部件间气路连接所需的连接点，有效地简化了气路，减少气路复杂程度，缩小气路体积，减少气路本身漏气可能性，提高了其连接可靠性。
气路盒10由硬塑胶材料制成，在使用中不会出现以往弹性连接气管常有的气路扭曲、变形、装配过盈受压堵塞等异常不良，可明显简化装配要求，提高产品良率。而且气路盒10的各接入口自带柔性密封材料，与各功能部件连接无需其它密封零件，装配方便，环节减少，同时能可靠有效连接各部件。各接入口通过柔性密封材料与各部件接入口实现过盈连接，能够兼容各部件接入口的尺寸公差范围，保证气密性。
NIBP气路结构100的一体化系统，可以实现气路结构紧凑化，为整机做小尺寸带来可能。同时以气路盒10为核心的一体化气路结构，已经实现模块化，在各产品中移植非常方便，加快了产品的开发速度。
请参阅图12，在另一实施例中，过压检测传感器40'与气压检测传感器50'集成于主控电路板80'上并与电路模块81’电性连接。可以通过表面贴装，如焊接等技术将过压检测传感器40'与气压检测传感器50'预先设置于主控电路板80'上。
可以理解，在其他实施例中，可以仅用一个慢速放气阀60实现袖套200最后的放气，此时快速放气阀70可以省略，壳体11的第二挡块119与第二支撑臂15可以省略。
可以理解，在其他实施例中，可以仅用一个气压检测传感器50实现对袖套气压的测量，此时过压检测传感器40可以省略。具体而言，当血压测量仪300的统可靠性足够高或有其它保护措施时，可以仅用一个气压检测传感器50进行气路系统的气压测量，当测得气压触及工作气压上限时，即停止继续充气，启动血压测量的程序操作，即气压检测传感器50同时承担气压测量和最大保护气压的测量的功能，此时，壳体11上的第一接口116可以省略。
可以理解，在其他实施例中，可与气路盒10上增设一个连接于壳体11上的支撑部，以实现对充气泵20的收容固定。可以理解，当慢速放气阀60及快速放气阀70可稳固定安装于壳体11上时，第一支撑部13及第二支撑部15可以省略。
可以理解，气路盒10的壳体11上可以形成一个接口圆管代替袖套气嘴30。在其他实施方式中，气路盒10及各部件是整体设计，各部件可以设计为不一样的其它摆放位置，然后调整气路盒10的结构形状，适应性地固定连接各部件。可以理解，各部件如充气泵、放气阀、传感器、气嘴等也可以为其他的类型或种类，如其它正面压紧密封的传感器，或其它需要参与到气路系统中的部件。或者改变部件的数量或减少部分部件的接入来实现配置差异化，而辅助其它传统形式如硅胶气管形式，连接未与气路盒10直接连接的部件。
可以理解，可以根据产品具体布局需要，将气路盒10分为多部分，每部分与二个或以上的部件连接，气路盒10之间用传统方式如硅胶气管连接。气路盒10的拆分使用可减少局部气路的连接，也能适当减少气路节点。
可以理解，气路盒10的接入口也可以整体由柔性材料制成，而不仅仅是自带柔性密封材料。气路盒10及其接入口也可以全部采用硬性材料如硬塑料制成，接入口处直接与各部件接入口过盈密封连接。气路盒10也可以全部采用硬性材料如塑料等制成，而接入口处采用其它柔性塑胶或硅胶等柔性材料，例如O型圈，来辅助气路盒10与部件接入口的密封连接，功能上可等同于气路盒10硬胶软胶一体结合的效果。
可以理解，气路盒10可根据需要调整为一个盒体与多个封盖的组合，或多个盒体与多个封盖的组合，同时，可根据需要把各部件的接入口设计在盒体上或封盖上。可以把气路盒10分为结构固定功能部分和气路连接功能部分，数量为二部分或更多部分，以结构固定部分集成固定泵、阀、传感器等各部件，以形式为单气容多气管出口的气路部件，就近连接各部件。变化方案中的气路盒10连接泵、阀、传感器等各部件形成气路系统，气路盒10在接口处与各部件形成初步的孔轴连接关系，未实现完全自由度的约束，气路系统中各部件及气路盒10的固定，是以增加的其它零件或产品的上下壳来完成最后的固定。
可以理解，气路盒10上也可仅设有充气口113及第一接气口1183，或者仅设置 充气口113与第一接口116(用于检测气压)。第一接气口1183与第一接口116为对应实现各自功能的连通口。当然，气路盒10上还可设置其他功能的多个连通口(即功能接口)。
以上所述实施例仅表达了本发明的几种实施方式，其描述较为具体和详细，但并不能因此而理解为对本发明专利范围的限制。应当指出的是，对于本领域的普通技术人员来说，在不脱离本发明构思的前提下，还可以做出若干变形和改进，这些都属于本发明的保护范围。因此，本发明专利的保护范围应以所附权利要求为准。

Claims (17)

  1. 一种气路结构，应用于血压测量仪中，其特征在于，包括：
    气路盒，包括内部形成有腔体的壳体，所述壳体上间隔形成有接入口、充气口及接气口，所述接入口、充气口以及所述接气口均与所述腔体连通；
    充气泵，包括充气接口，所述充气接口直接连通于所述充气口；袖套气嘴，与所述接入口直接连通；
    放气阀，设置于所述壳体上并直接连通所述接气口；以及
    气压检测传感器，形成有接口，所述气压检测传感器的接口直接连通所述壳体的腔体；
    其中，所述充气泵、放气阀及气压检测传感器于所述壳体的腔体内实现气压传递。
  2. 如权利要求1所述的气路结构，其特征在于，所述袖套气嘴上形成有插接端，所述插接端插设连接于所述壳体的接入口中，所述充气接口插设连接于所述壳体的充气口中，所述壳体上还形成有与所述腔体连通的第一接口与第二接口，所述气路结构还包括过压检测传感器，所述过压检测传感器形成有接口，所述过压检测传感器的接口及所述气压检测传感器的接口分别插设连接于所述第一接口与所述第二接口中。
  3. 如权利要求2所述的气路结构，其特征在于，所述接气口包括间隔设置的第一接气口与第二接气口，所述放气阀包括间隔设置的慢速放气阀和快速放气阀，所述慢速放气阀的一端设有连接口，所述连接口插设连接于所述第一接气口中，所述快速放气阀的一端设有连接口，所述快速放气阀的连接口插设连接于所述第二接气口中。
  4. 如权利要求3所述的气路结构，其特征在于，所述气路盒由硬塑胶材料制成，所述充气泵的充气接口、袖套气嘴的插接端、慢速放气阀的连接口、快速放气阀的连接口、过压检测传感器的接口及 气压检测传感器的接口分别过盈配合于对应的充气口、接入口、第一接气口、第二接气口、第一接口及第二接口中。
  5. 如权利要求4所述的气路结构，其特征在于，所述充气口、接入口、第一接气口、第二接气口、第一接口及第二接口均由柔性材料构成或环绕自身周缘设有柔性材料，以分别与所述充气泵的充气接口、袖套气嘴的插接端、慢速放气阀的连接口、快速放气阀的连接口、过压检测传感器的接口及气压检测传感器的接口密封连接。
  6. 如权利要求3所述的气路结构，其特征在于，所述壳体的一侧还形成有开口，并设有封闭所述开口的封盖，所述开口连通所述腔体，所述壳体于所述腔体内环绕所述第一接口与所述第二接口形成阻挡筋，所述阻挡筋上开设有出气口，所述出气口远离所述壳体的接入口、第一接气口及第二接气口。
  7. 如权利要求3所述的气路结构，其特征在于，所述气路盒还包括由所述壳体一端向外延伸形成的支撑部，所述支撑部包括间隔设置的第一支撑部与第二支撑部，所述慢速放气阀和所述快速放气阀分别设置于所述第一支撑部与所述第二支撑部上，所述壳体邻近所述支撑部的一端对应所述第一支撑部及所述第二支撑部分别凸设有第一挡块与第二挡块，所述第一接气口形成于所述第一挡块上，所述第二接气口形成于所述第二挡块上，所述第一接气口与第二接气口分别朝向所述第一支撑部与所述第二支撑部。
  8. 如权利要求7所述的气路结构，其特征在于，所述第一支撑部与所述第二支撑部相互远离的两侧分别形成有弯折边，且所述第一支撑部与所述第二支撑部之间形成有分隔边，所述第一支撑部的弯折边与所述分隔边之间形成第一收容部，所述第二弯折边与所述分隔边之间形成有第二收容部，所述慢速放气阀收容于所述第一收容部中，所述快速放气阀收容于所述第二收容部中。
  9. 如权利要求7所述的气路结构，其特征在于，所述第一支撑部远离 所述壳体的一端弯折形成挡止边，所述挡止边上开设有缺口，从而使得所述挡止边分隔成两个挡止端，所述慢速放气阀挡止于所述两个挡止端上并部分凸伸于所述缺口外。
  10. 如权利要求7所述的气路结构，其特征在于，所述第二支撑部的弯折边远离所述壳体的一端朝所述第一支撑部延伸形成卡钩，所述第二支撑部远离所述壳体的一端凸伸有挡止端，所述快速放气阀远离其连接口的一端形成有挡止凸块，所述挡止凸块上形成有卡止口，所述挡止凸块挡止于所述挡止端上，所述卡钩卡入所述快速放气阀的卡止口中。
  11. 一种血压测量仪，其特征在于，包括本体及连接于所述本体上的袖套，所述本体内设有如权利要求1所述的气路结构及主控电路板，所述主控电路板与所述充气泵、压检测传感器、气压检测传感器及所述放气阀电性连接，所述袖套连接于所述气路结构上。
  12. 如权利要求11所述的血压测量仪，其特征在于，所述主控电路板通过卡扣、柱孔过盈或者紧固件装设于所述气路盒上。
  13. 如权利要求12所述的血压测量仪，其特征在于，所述过压检测传感器及所述气压检测传感器上均设置有焊接脚，所述过压检测传感器与所述气压检测传感器的焊接脚均焊接集成于所述主控电路板上。
  14. 如权利要求12所述的血压测量仪，其特征在于，所述气路盒的壳体一端形成有凸起，所述接入口形成于所述凸起上并沿所述气路盒的长度方向延伸，所述充气口邻近所述凸起形成于所述壳体上，所述凸起上设有定位柱，所述壳体邻近所述凸起的一端的两侧分别形成有卡扣和固定柱，所述主控电路板的一端开设有定位孔，并于一侧开设有卡止缺口且于另一侧形成有卡止位，所述壳体的定位柱插设于所述主控电路板的定位孔中，所述卡扣扣合于所述卡止位，所述固定柱固定于所述卡止缺口中，从而将所述主控电路板固定于所述气路盒上。
  15. 如权利要求11～14中任一项所述的血压测量仪，其特征在于，所述血压测量仪为电子无创血压测量仪。
  16. 一种气路盒，其特征在于，包括：
    壳体，内部形成有腔体，所述壳体上间隔形成有充气口与连通口，所述充气口与所述连通口均由柔性材料构成并与所述腔体连通，所述充气口及连通口用于与对应的气路器件直接气密配合，以使各气路器件于所述壳体的腔体内实现气压传递或气体交换，所述充气口用于实现所述气路盒的向内充气功能，所述连通口用于实现所述气路盒的向外排气或者气压检测功能。
  17. 如权利要求16所述的气路盒，其特征在于，所述充气口用于与充气泵气路连通，所述连通口用于与气压检测传感器直接连通以实现所述气路盒的气压检测功能，所述壳体还上还形成有接气口，所述接气口与所述充气口及所述连通口间隔设置，所述接气口均由柔性材料构成并与所述腔体连通，所述接气口用于与放气阀直接气密配合，以实现所述气路盒的向外排气功能。
PCT/CN2015/070129 2015-01-05 2015-01-05 血压测量仪及其气路结构以及气路盒 WO2016109925A1 (zh)

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