WO2013175547A1 - 流量検出器 - Google Patents
流量検出器 Download PDFInfo
- Publication number
- WO2013175547A1 WO2013175547A1 PCT/JP2012/062912 JP2012062912W WO2013175547A1 WO 2013175547 A1 WO2013175547 A1 WO 2013175547A1 JP 2012062912 W JP2012062912 W JP 2012062912W WO 2013175547 A1 WO2013175547 A1 WO 2013175547A1
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- WO
- WIPO (PCT)
- Prior art keywords
- flow
- flow rate
- base
- rate detector
- groove
- Prior art date
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Classifications
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
- G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
- G01F1/56—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by using electric or magnetic effects
- G01F1/58—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by using electric or magnetic effects by electromagnetic flowmeters
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
- A61M1/1621—Constructional aspects thereof
- A61M1/1647—Constructional aspects thereof with flow rate measurement of the dialysis fluid, upstream and downstream of the dialyser
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
- G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
- G01F1/56—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by using electric or magnetic effects
- G01F1/58—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by using electric or magnetic effects by electromagnetic flowmeters
- G01F1/588—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by using electric or magnetic effects by electromagnetic flowmeters combined constructions of electrodes, coils or magnetic circuits, accessories therefor
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
- G01F15/00—Details of, or accessories for, apparatus of groups G01F1/00 - G01F13/00 insofar as such details or appliances are not adapted to particular types of such apparatus
- G01F15/02—Compensating or correcting for variations in pressure, density or temperature
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3317—Electromagnetic, inductive or dielectric measuring means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3324—PH measuring means
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3331—Pressure; Flow
- A61M2205/3334—Measuring or controlling the flow rate
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3368—Temperature
Definitions
- the present invention relates to a flow detector incorporated in a medical artificial dialysis device to detect the flow of dialysate.
- Patent Document 1 discloses a flow rate detector of this type.
- the flow rate detector disclosed in this document includes a synthetic resin base that is attached to and detached from the flow rate measuring device. A pair of flow paths are formed in the base for flowing dialysate. In the base, a detection terminal and an earth terminal are provided to detect the flow rate of the dialysate flowing in each flow path.
- each flow path is each arrange
- the pair of flow paths are formed in proximity to each other. For this reason, if the temperature of the fluid flowing in one of the pair of flow paths becomes high, the base may be deformed. As a result, the cross-sectional area of the other of the pair of flow paths changes, which may cause an error when measuring the flow rate of the dialysate.
- An object of the present invention is to prevent the temperature of the fluid flowing in one flow path from affecting the other flow paths, so that the cross-sectional area of each flow path can be properly maintained, and flow in each flow path
- An object of the present invention is to provide a flow rate detector capable of accurately measuring the flow rate of fluid.
- a base a plurality of flow paths formed in the base, and a detection unit for detecting the flow rate of fluid flowing in the plurality of flow paths
- a flow detector is provided between the plurality of flow paths.
- a blocking portion for blocking heat conduction between the flow paths is provided.
- the temperature of the fluid flowing in one flow passage may change. Even in such a case, the heat transfer from one flow path to another flow path is blocked by the blocking portion provided between the flow paths. Thus, the temperature of the fluid in one channel does not affect the other channels. For this reason, the cross-sectional area of each flow path can be maintained appropriately, and the flow rate of the fluid flowing through the flow path can be accurately measured.
- the blocking portion preferably comprises a groove formed in the base.
- the groove preferably penetrates from the front surface to the back surface of the base.
- the detection portion is preferably disposed at the central portion in the longitudinal direction of the groove.
- an orifice-like measurement flow generation unit is formed in the flow path, and the detection unit is disposed in the measurement flow generation unit.
- the sloped portions are formed at both ends in the fluid flow direction, and the sloped portions are formed such that the flow path narrows toward the measurement flow generation portion Is preferred.
- the detection unit preferably has terminals disposed at both ends in the width direction of the measurement flow generation unit, and the terminals preferably detect an electromotive force generated by fluid flow.
- the plurality of flow paths be a pair of flow paths, and each of the pair of flow paths be disposed on the same plane on both sides sandwiching the groove.
- the cross-sectional area of each flow passage can be appropriately maintained, and the flow flows in each flow passage.
- the flow rate of the fluid can be measured accurately.
- FIG. 5 is a cross-sectional view taken along line 4-4 of FIG. 3;
- FIG. 5 is a cross-sectional view taken along line 5-5 of FIG. 4;
- FIG. 6 is a cross-sectional view taken along line 6-6 of FIG. 3;
- FIG. 3 is a perspective view showing a detection terminal and a ground terminal of a flow rate detector.
- FIG. 7 is a plan view showing a flow rate detector according to a second embodiment of the present invention. Sectional drawing which shows the flow volume detector which concerns on 3rd Embodiment of this invention. The perspective view which shows the flow volume detector which concerns on 4th Embodiment of this invention. 13 is a cross-sectional view taken along line 13-13 of FIG. 12; The perspective view showing the flow rate detector concerning a 5th embodiment of the present invention. Sectional drawing which shows the flow volume detector which concerns on 6th Embodiment of this invention.
- the artificial dialysis device 21 includes a dialyzer 22.
- a dialyzer 22 By the operation of the pump 23, blood 24 containing waste 241 derived from the patient's body is introduced into the dialyzer 22 through the blood circulation path 25.
- the waste 241 in the blood is separated and taken into the dialysate 26 as a fluid.
- the filtered clean blood 24 is returned to the patient's body again.
- the artificial dialysis device 21 further includes a flow rate measuring device 27.
- the flow rate measuring device 27 is provided with a magnetic circuit 28 including an electromagnetic coil 281 and a pair of magnetic poles 282, and a signal processing circuit 29 for processing a measurement signal. An alternating current is supplied to the electromagnetic coil 281.
- the flow rate measuring device 27 is equipped with a disposable type flow rate detector 30 in order to measure the flow rate of the dialysate 26.
- the flow rate detector 30 is configured to be removable from the flow rate measuring device 27.
- the flow rate detector 30 is provided with a pair of flow paths 33 and 34.
- the flow paths 33 and 34 are respectively connected to the inflow path 31 and the return path 32 of the dialysate 26 to the dialyzer 22.
- the flow paths 33 and 34 are disposed between the magnetic poles 282 of the magnetic circuit 28 in a state where the flow rate detector 30 is mounted on the flow rate measuring device 27.
- the dialysate 26 flows from the supply tank 36 into the dialyzer 22 through the inflow path 31 and the flow path 33.
- the dialysate 26 containing the wastes 241 separated by the dialyzer 22 is returned to the drain tank 37 via the return path 32 and the flow path 34.
- the flow rate detector 30 measures the flow rate of the dialysate 26 flowing in the flow paths 33 and 34, respectively.
- the flow rate detector 30 includes a base 41 made of a transparent synthetic resin such as polypropylene resin.
- the base 41 is formed in a rectangular plate shape.
- a pair of connection pipes 42 and 43 respectively project from both end faces of the base 41.
- the connection pipes 42 and 43 are connected to the middle of the inflow path 31 and the return path 32, respectively.
- recesses 46 and 47 communicating with the passages 44 and 45 in the connection pipes 42 and 43 are respectively formed at both ends of the base 41.
- the passages 44 and 45 are respectively connected to the recesses 46 and 47 at a position slightly higher than the bottom surfaces of the recesses 46 and 47.
- Grooves 461 and 471 are formed at locations near the center of the base 41 in the recesses 46 and 47.
- the grooves 461 and 471 are provided at positions shallower than the recesses 46 and 47 and higher than the passages 44 and 45.
- a pair of lid plates 48 and 49 is adhered or welded to the upper surface of the base 41.
- the lids 48 and 49 are formed of a transparent synthetic resin such as polypropylene resin.
- Each lid plate 48, 49 is positioned at a predetermined position on the base 41 by a plurality of positioning pins 50.
- measurement groove portions 51 and 52 communicating with the concave portions 46 and 47 and the groove portions 461 and 471 are formed on the back surfaces of the lid plates 48 and 49, respectively.
- convex portions 511 and 521 are formed at the central portion in the longitudinal direction of each of the measurement groove portions 51 and 52.
- Inclined portions 512 and 522 are formed at both ends of the convex portions 511 and 521, respectively.
- a flow passage 34 is constituted by the passage 45 of the connection pipe 43, the concave portion 47, the groove portion 471 and the measurement groove portion 52 of the lid plate 49.
- an orifice-like measurement flow generation unit 331 or 341 is formed between the convex portions 511 and 521 of the lid plates 48 and 49 and the upper surface of the base 41.
- Each measurement flow generation unit 331, 341 has a passage cross-sectional area suitable for generating a measurement flow of the dialysate 26 in each of the flow passages 33, 34.
- a pair of detection bus bars 53 and a pair of detection bus bars 54 are embedded in the base 41.
- a detection terminal 531 as a detection unit exposed in the measurement flow generation unit 331 is formed.
- a detection terminal 541 as a detection unit exposed in the measurement flow generation unit 341 is formed.
- the detection terminals 531 and 541 are disposed to face each other at the end portions in the width direction of the measurement flow generation units 331 and 341.
- connection terminals 532 exposed to the end face of the base 41 are formed at the second end of each detection bus bar 53.
- a connection terminal 542 exposed to the end face of the base 41 is formed at the second end of each detection bus bar 54.
- the connection terminals 532 and 542 are connected to the signal processing circuit 29 of the flow rate measuring device 27.
- ground bus bar 55 and the ground bus bar 56 are embedded. At first ends of the ground bus bars 55 and 56, ground terminals 551 and 561 exposed in the grooves 461 and 471, respectively are formed. At the second ends of the ground bus bars 55 and 56, connection terminals 552 and 562 exposed to the end face of the base 41 are formed. The connection terminals 552 and 562 are connected to the signal processing circuit 29.
- a blocking portion 57 is provided at the center of the base 41 between the flow paths 33 and 34.
- the blocking portion 57 blocks the conduction of heat from one of the flow paths 33 and 34 through the base 41 to the other flow path.
- the blocking portion 57 extends along the flow paths 33 and 34 between the flow paths 33 and 34. That is, the blocking portion 57 includes a through groove 58 penetrating from the front surface to the back surface of the base 41. Both flow paths 33 and 34 are disposed on the same plane on both sides sandwiching the through groove 58.
- the detection terminals 531 and 541 are disposed at the central portion in the longitudinal direction of the through groove 58.
- the flow rate detector 30 is attached to the flow rate measuring device 27 when the artificial dialysis device 21 is in use.
- the flow path 33 is connected to the middle of the inflow path 31, and the flow path 34 is connected to the middle of the return path 32.
- the measurement flow generation units 331 and 341 of the flow paths 33 and 34 illustrated in FIG. 4 are disposed between the pair of magnetic poles 282 of the magnetic circuit 28.
- the blood 24 drawn from the patient is introduced into the dialyzer 22 through the blood circulation path 25 by the operation of the pump 23. Further, the dialysate 26 in the supply tank 36 flows into the dialyzer 22 through the inflow path 31 and the flow path 33 by the operation of the pump 35. Therefore, the blood 24 is filtered by the dialyzer 22, and the waste 241 in the blood 24 is separated and transferred into the dialysate 26. The cleaned blood 24 is then returned to the patient again via the blood circulation path 25. Further, the dialysate 26 containing the wastes 241 is collected in the drain tank 37 via the return path 32 and the flow path 34.
- an alternating magnetic field is generated in the magnetic circuit 28 by the alternating current.
- the magnetic flux penetrates the measurement flow generation units 331 and 341 of the flow paths 33 and 34.
- an electromotive force corresponding to the flow rate of the dialysate 26 flowing to the measurement flow generation units 331 and 341 is generated.
- the electromotive force is output from the detection terminals 531 and 541 of the detection bus bars 53 and 54 to the signal processing circuit 29 as a detection signal.
- the detection signal is an output of a level set according to the ground potential from the ground bus bars 55 and 56.
- the flow rate per unit time of the dialysate 26 flowing in each of the flow paths 33 and 34 is measured based on the flow rate of the dialysate 26 and the cross-sectional area of the measurement flow generator 331 and 341.
- the amount of waste 241 separated from the blood 24 is calculated by the difference in the flow rate of the dialysate 26 flowing in both flow paths 33 and 34.
- the synthetic resin base 41 or lid plate 48 When measuring the flow rate of the dialysate 26, if the temperature of the dialysate 26 flowing in one of the channels 33, 34 changes, the synthetic resin base 41 or lid plate 48 may expand or contract. There is. For this reason, the cross-sectional area of the measurement flow generation part 331,341 of the other flow path among the flow paths 34,33 may change, and when measuring a flow volume, an error may arise.
- the through groove 58 is formed between the flow paths 33 and 34 on the base 41 as the blocking portion 57 for substantially blocking the heat conduction. Therefore, even if the temperature of the dialysate 26 flowing in one of the flow paths 33 and 34 changes, the penetration groove 58 hardly affects the other flow path.
- a blocking portion 57 is provided between the flow paths 33 and 34 in order to block heat conduction between the flow paths 33 and 34. Therefore, even if the temperature of the dialysate 26 flowing in one of the flow paths 33 and 34 changes, the heat transfer from the one flow path to the other flow path is blocked by the blocking portion 57. . Therefore, the temperature of the dialysate 26 flowing in one of the flow paths 33 and 34 hardly affects the other flow path. Therefore, the cross-sectional area of each flow path 33, 34 can be maintained appropriately, and the flow rate of the dialysate 26 flowing in the flow paths 33, 34 can be accurately measured.
- the blocking portion 57 includes the through groove 58 formed in the base 41. According to this configuration, the structure of the blocking portion 57 is simple, and heat conduction between the flow paths 33 and 34 can be effectively blocked.
- the through groove 58 penetrates from the front surface to the back surface of the base 41. For this reason, the heat conduction between the flow paths 33 and 34 can be interrupted at a high level, and a high interruption rate can be maintained.
- Inclined portions 512 and 522 are formed at both ends of the convex portions 511 and 521 which form the measurement flow generation portions 331 and 341, respectively. According to this configuration, the flow of the dialysate 26 is unlikely to be disturbed even when the cross-sectional areas of the flow paths are different between the convex portions 511 and 521 and both sides of the convex portions 511 and 521. For this reason, the flow rate of the dialysate 26 can be accurately detected.
- Recesses 46 and 47 and grooves 461 and 471 are formed between the passages 44 and 45 of the connection pipes 42 and 43 and the measurement grooves 51 and 52 of the lid plates 48 and 49, respectively. According to this configuration, the dialysate 26 is temporarily stored in the recesses 46 and 47 and the grooves 461 and 471. Thereby, the flow of the dialysate 26 is less likely to be disturbed. For this reason, the flow rate of the dialysate 26 can be accurately detected.
- the detection terminals 531 and 541 of the detection bus bars 53 and 54 are disposed at the center of the through groove 58 in the longitudinal direction. In this case, the detection terminals 531 and 541 are disposed at positions which are less susceptible to the influence of heat from a flow path different from the flow path in which the detection terminals are arranged. Thereby, the flow rate of the dialysate 26 can be accurately detected.
- the flow channels 33 and 34 are disposed on the same plane on both sides of the through groove 58. Therefore, the flow rate detector 30 can be made flat and compact.
- the through groove 58 as the blocking portion 57 is divided into two in the longitudinal direction.
- the blocking portion 57 is formed of a recessed groove 59 formed on the upper surface of the base 41.
- the recessed groove 59 has a bottom wall.
- the recessed groove 59 is provided between the flow paths 33 and 34 and extends along the flow paths 33 and 34.
- the recessed groove 59 has a bottom wall, so that deformation of the entire base 41 can be suppressed and the reinforcing action of the base 41 can be obtained.
- a pair of flow channels 33 and 34 are formed to be spaced apart and overlapped in the thickness direction of the base 41.
- a through groove 58 as the blocking portion 57 is provided between the flow paths 33 and 34. The through groove 58 penetrates from one end of the base 41 to the other.
- the flow channels 33 and 34 are arranged so as to overlap in the thickness direction of the base 41 on both sides sandwiching the through groove 58. According to this configuration, the width of the base 41 can be narrowed to make the entire base 41 compact. In addition, since the refrigerant can also flow in the through groove 58, the temperature control of the flow rate detector 30 is facilitated.
- a single lid plate 60 is employed in place of the pair of lid plates 48 and 49 in the above-described embodiments.
- a through groove 61 is formed as a blocking portion penetrating from the front surface to the rear surface of the cover plate 60.
- the through groove 61 is formed at a position corresponding to the through groove 58 of the base 41.
- the through groove 61 has substantially the same width and length as the through groove 58.
- one cover plate of the pair of cover plates 48 and 49 is attached to the surface of the base 41 opposite to the other cover plate. Therefore, also for the pair of flow paths 33 and 34 and the detection bus bars 53 and 54, one flow path and the detection bus bar are provided on the surface of the base 41 opposite to the other flow path and the detection bus bar.
- One of the flow paths of the pair of flow paths 33 and 34 is provided on the surface of the base 41 opposite to the other flow path. According to this configuration, since the distance between the flow paths 33 and 34 is increased, it is possible to further suppress that the temperature of the fluid flowing in one flow path of the pair of flow paths 33 and 34 affects the other flow paths. can do.
- a heat insulating material such as expanded polystyrene may be filled in the through groove 58 or the recessed groove 59. That is, the blocking portion 57 may be configured by the through groove 58 or the recessed groove 59 and the heat insulating material.
- a plurality of small holes may be linearly and continuously formed to constitute the blocking portion 57.
- the flow detector of the present invention may be used in other fields besides artificial dialysis.
- 21 artificial dialysis device
- 22 dialyzer
- 24 blood
- 241 waste
- 26 dialysis fluid as fluid
- 27 flow detector measuring device
- 28 magnetic circuit
- 30 flow detector
- 33, 34 Flow path: 331, 341: measurement flow generation part, 512, 522: inclined part, 41: base, 53, 54: detection bus bar 431, 541: detection terminal as detection part, 57: blocking part, 58, 61: penetrating Groove, 59 ... recessed groove.
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Abstract
Description
以下、本発明の流量検出器を具体化した第1実施形態について図1~図9に従って説明する。
次に、本発明の流量検出器30を具体化した第2実施形態について図10を参照して説明する。第2実施形態以降の各実施形態及び変更例は、第1実施形態と異なる部分を中心に説明する。
次に、本発明の流量検出器30を具体化した第3実施形態について図11を参照して説明する。
次に、本発明の流量検出器30を具体化した第4実施形態について図12及び図13を参照して説明する。
次に、本発明の流量検出器30を具体化した第5実施形態について図14を参照して説明する。
次に、本発明の流量検出器30を具体化した第6実施形態について図15を参照して説明する。
Claims (8)
- ベースと、前記ベースに形成された複数の流路と、前記複数の流路に流れる流体の流量を検出する検出部とを備えた流量検出器において、
前記複数の流路間には、前記流路間の熱伝導を遮断するための遮断部が設けられていることを特徴とする流量検出器。 - 前記遮断部は、前記ベースに形成された溝からなることを特徴とする請求項1に記載の流量検出器。
- 前記溝は、前記ベースの表面から裏面にかけて貫通していることを特徴とする請求項2に記載の流量検出器。
- 前記検出部は、前記溝の長手方向の中央部に配置されていることを特徴とする請求項2又は3に記載の流量検出器。
- 前記流路には、オリフィス状の計測流生成部が形成され、前記検出部は、前記計測流生成部に配置されていることを特徴とする請求項2~4のうちのいずれか一項に記載の流量検出器。
- 前記計測流生成部において、流体が流れる方向の両端部には傾斜部が形成され、前記傾斜部は、前記計測流生成部に向かうに従い前記流路が狭くなるように形成されていることを特徴とする請求項5に記載の流量検出器。
- 前記検出部は、前記計測流生成部の幅方向両側の端部に配置される端子を有し、前記端子は、流体が流れることによって生じる起電力を検出することを特徴とする請求項5又は6に記載の流量検出器。
- 前記複数の流路は、一対の流路からなり、前記一対の流路のそれぞれは、前記溝を挟む両側において同一面上に配置されていることを特徴とする請求項2~7のうちのいずれか一項に記載の流量検出器。
Priority Applications (6)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2014516532A JP6081454B2 (ja) | 2012-05-21 | 2012-05-21 | 流量検出器 |
EP12877098.9A EP2853864A4 (en) | 2012-05-21 | 2012-05-21 | FLOW VOLUME DETECTOR |
PCT/JP2012/062912 WO2013175547A1 (ja) | 2012-05-21 | 2012-05-21 | 流量検出器 |
CN201280073265.3A CN104303022B (zh) | 2012-05-21 | 2012-05-21 | 流量检测器 |
US14/400,730 US9752906B2 (en) | 2012-05-21 | 2012-05-21 | Flow volume detector |
HK15102912.4A HK1202615A1 (en) | 2012-05-21 | 2015-03-23 | Flow volume detector |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
PCT/JP2012/062912 WO2013175547A1 (ja) | 2012-05-21 | 2012-05-21 | 流量検出器 |
Publications (1)
Publication Number | Publication Date |
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WO2013175547A1 true WO2013175547A1 (ja) | 2013-11-28 |
Family
ID=49623280
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/JP2012/062912 WO2013175547A1 (ja) | 2012-05-21 | 2012-05-21 | 流量検出器 |
Country Status (6)
Country | Link |
---|---|
US (1) | US9752906B2 (ja) |
EP (1) | EP2853864A4 (ja) |
JP (1) | JP6081454B2 (ja) |
CN (1) | CN104303022B (ja) |
HK (1) | HK1202615A1 (ja) |
WO (1) | WO2013175547A1 (ja) |
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2015197424A1 (de) * | 2014-06-25 | 2015-12-30 | Fresenius Medical Care Deutschland Gmbh | Flussmesser und kassettenmodul für einen flussmesser |
JP2016095192A (ja) * | 2014-11-13 | 2016-05-26 | 愛知時計電機株式会社 | 流量計測器及び電磁流量計 |
EP3193959A4 (en) * | 2014-09-12 | 2018-03-21 | Easydial, Inc. | Portable hemodialysis machine and disposable cartridge with flow sensor |
US11406745B2 (en) | 2015-03-24 | 2022-08-09 | Fresenius Medical Care Deutschland Gmbh | Balancing method and balancing unit being independent of temperature disturbance |
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DE102015001406B3 (de) * | 2015-02-04 | 2016-07-14 | Fresenius Medical Care Deutschland Gmbh | Kassettenmodul für einen Differenzflussmesser und Differenzflussmesser |
CN109707932B (zh) * | 2018-12-27 | 2020-09-04 | 宁波安创电子科技有限公司 | 高效高精度流量检测设备 |
DE102020102485A1 (de) * | 2020-01-31 | 2021-08-05 | Fresenius Medical Care Deutschland Gmbh | Flusssensor und Verfahren zum Messen eines Flusses |
CN112197823A (zh) * | 2020-08-21 | 2021-01-08 | 蚌埠恒远传感器科技有限公司 | 智能电磁流量传感器 |
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Cited By (8)
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WO2015197424A1 (de) * | 2014-06-25 | 2015-12-30 | Fresenius Medical Care Deutschland Gmbh | Flussmesser und kassettenmodul für einen flussmesser |
CN106461432A (zh) * | 2014-06-25 | 2017-02-22 | 弗雷森纽斯医疗护理德国有限责任公司 | 流量测量器和用于流量测量器的盒模块 |
JP2017520752A (ja) * | 2014-06-25 | 2017-07-27 | フレゼニウス メディカル ケア ドイッチェランド ゲゼルシャフト ミット ベシュレンクテル ハフツング | 流量計及び流量計のためのカセットモジュール |
US10620029B2 (en) | 2014-06-25 | 2020-04-14 | Fresenius Medical Care Deutschland Gmbh | Flowmeter and cassette module for a flowmeter |
EP3193959A4 (en) * | 2014-09-12 | 2018-03-21 | Easydial, Inc. | Portable hemodialysis machine and disposable cartridge with flow sensor |
JP2016095192A (ja) * | 2014-11-13 | 2016-05-26 | 愛知時計電機株式会社 | 流量計測器及び電磁流量計 |
US11406745B2 (en) | 2015-03-24 | 2022-08-09 | Fresenius Medical Care Deutschland Gmbh | Balancing method and balancing unit being independent of temperature disturbance |
EP3274014B1 (de) * | 2015-03-24 | 2024-04-24 | Fresenius Medical Care Deutschland GmbH | Temperaturstörungsunabhängige bilanzierungseinrichtung |
Also Published As
Publication number | Publication date |
---|---|
EP2853864A4 (en) | 2016-07-20 |
JP6081454B2 (ja) | 2017-02-15 |
US20150135848A1 (en) | 2015-05-21 |
EP2853864A1 (en) | 2015-04-01 |
CN104303022B (zh) | 2017-07-11 |
HK1202615A1 (en) | 2015-10-02 |
JPWO2013175547A1 (ja) | 2016-01-12 |
CN104303022A (zh) | 2015-01-21 |
US9752906B2 (en) | 2017-09-05 |
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