JP2016160901A - Tube pump and medical device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To appropriately control a maximum ultimate pressure in an outlet side flow passage of a tube pump when the outlet side flow passage is clogged.SOLUTION: A tube pump conveys liquid in a tube arranged along a guide member by moving a pressing member while squeezing the tube with the pressing member. The tube pump comprises: a biasing member that biases the guide member toward the side of the tube; and a biasing force adjustment part that adjusts the biasing force of the biasing member.SELECTED DRAWING: Figure 4

Description

  The present invention relates to a tube pump and a medical device.

  In recent years, various liquid supply apparatuses for supplying liquid to a water jet knife as a medical device have been proposed. The liquid supply device described in Patent Document 1 employs a plunger pump, and deforms a part of the flow path between the plunger pump and the water jet knife, thereby reducing the flow rate of the liquid supplied to the water jet knife. Fluctuation is suppressed.

JP 2014-95353 A

  In the prior art, there has been a desire to appropriately manage the maximum ultimate pressure in the flow path from the liquid container to the tip nozzle of the water jet knife, particularly in the flow path from the liquid supply device to the tip nozzle. .

  SUMMARY An advantage of some aspects of the invention is to solve at least a part of the problems described above, and the invention can be implemented as the following forms.

(1) One form of this invention is a tube pump which conveys the liquid in the said tube by moving the said press member, crushing the tube arrange | positioned along a guide member with a press member. The tube pump may include a biasing member that biases the guide member toward the tube, and a biasing force adjusting unit that adjusts a biasing force of the biasing member. According to the tube pump of this aspect, the urging force of the urging member that urges the guide member toward the tube is adjusted by the urging force adjusting unit, so that the maximum ultimate pressure in the flow path can be appropriately managed.

(2) In the tube pump of the said form, you may be for supplying a liquid to a medical liquid injection apparatus. According to the tube pump of this aspect, the maximum ultimate pressure in the liquid ejecting apparatus when the medical liquid ejecting apparatus is clogged can be appropriately managed.

(3) Another embodiment of the present invention is a medical device. The medical device moves the pressing member while squeezing the tube arranged along the guide member with the pressing member, and receives the supply of the liquid from the tube pump for conveying the liquid in the tube. A liquid ejecting apparatus. The tube pump may include an urging member that urges the guide member toward the tube, and an urging force adjusting unit that adjusts the urging force of the urging member. According to the medical device of this aspect, in the tube pump, the urging force of the urging member that urges the guide member toward the tube is adjusted by the urging force adjusting unit. The maximum ultimate pressure in the injection device can be appropriately managed.

(4) The medical device according to the aspect includes a flow rate setting unit that sets a flow rate of the liquid supplied to the liquid ejecting device, and a control unit that controls the biasing force adjusting unit based on the set flow rate. May be. According to this form of the medical device, since the urging force of the urging member is adjusted based on the flow rate set by the flow rate setting unit, the maximum ultimate pressure can be appropriately managed based on the set flow rate.

(5) In the medical device of the above aspect, the control unit may decrease the urging force as the set flow rate is smaller. According to this form of medical device, the smaller the set flow rate, the smaller the biasing force of the biasing member, so the maximum ultimate pressure can be managed more appropriately.

  The present invention can be realized in various forms. For example, a pump unit including a tube pump and a control device, a medical method using the tube pump, a surgical method using the tube pump, a program for realizing these methods, a storage medium storing these programs, etc. It can be realized in the form.

It is explanatory drawing which shows schematically the structure of the medical device as one Embodiment of this invention. It is explanatory drawing which shows notionally the structure of a tube pump. It is a perspective view of the tube pump of the state where the opening-and-closing part was opened. It is a fractured sectional view showing an internal configuration of an opening / closing part. It is a flowchart which shows a biasing force adjustment control process. It is explanatory drawing which shows table data. It is explanatory drawing which shows the liquid supply apparatus of an experiment example. It is a graph which shows the pressure change in each case of an experimental example. It is a graph which shows the relationship between the length of the spring in each case of an experiment example, and the maximum ultimate pressure.

Next, an embodiment of the present invention will be described.
A. overall structure:
FIG. 1 is an explanatory diagram schematically showing the configuration of a medical device 10 as an embodiment of the present invention. The medical device 10 is used in a medical institution, and has a function of incising or excising an affected part by ejecting a liquid to the affected part. The medical device 10 includes a handpiece 20, a liquid supply unit 50, and a control unit 80.

  The liquid supply unit 50 is a unit for supplying a liquid to the handpiece 20, and includes a water supply bag 51, a spike needle 52, first to fifth connectors 53a to 53e, and a first channel in which a flow path is formed. 1st-4th water supply tube 54a-54d, the pump tube 55, the obstruction | occlusion detection mechanism 56, and the filter 57 are provided.

  The water supply bag 51 is made of a transparent synthetic resin, and is filled with a liquid (specifically, physiological saline). The spike needle 52 is connected to the first water supply tube 54a via the first connector 53a. When the spike needle 52 is stabbed into the water supply bag 51, the liquid filled in the water supply bag 51 can be supplied to the first water supply tube 54a. The liquid may be another liquid that is not harmful even if it is sprayed onto a living tissue, such as pure water or a chemical solution, instead of physiological saline.

  The first water supply tube 54a is connected to the tube pump 60 via the second connector 53b. The tube pump 60 is connected to the second water supply tube 54b via the third connector 53c.

  The tube pump 60 sends the liquid in the pump tube 55 from the first water supply tube 54a side to the second water supply tube 54b side. The tube pump 60 is driven by the drive signal received from the control unit 80 via the pump cable 91. The detailed configuration of the tube pump 60 will be described later.

  The blockage detection mechanism 56 detects the blockages in the second to fourth water supply tubes 54b to 54d by measuring the pressure in the second water supply tube 54b.

  The second water supply tube 54b is connected to the third water supply tube 54c via the fourth connector 53d. A filter 57 is connected to the third water supply tube 54c. The filter 57 collects foreign matters contained in the liquid.

  The third water supply tube 54c is connected to the fourth water supply tube 54d through the fifth connector 53e. The fourth water supply tube 54 d is connected to the handpiece 20. The first to fourth water supply tubes 54a to 54d are tubes made of polyvinyl chloride and have elasticity. Note that the first to fourth water supply tubes 54a to 54d may be made of silicon or a thermoplastic elastomer.

  The handpiece 20 is an instrument that an operator holds and operates, and is a liquid ejecting apparatus that includes a liquid ejecting tube 22, a pulsation generating unit 24, and a housing 26. The pulsation generating unit 24 is supplied with liquid from the liquid supply unit 50 via the fourth water supply tube 54d. When a driving voltage is applied from the control unit 80 via the actuator cable 92, the pulsation generation unit 24 imparts pulsation to the supplied liquid. The liquid to which the pulsation is applied is ejected at high speed from the opening 22 a at the tip of the liquid ejecting tube 22. The surgeon performs treatment such as incision or excision of the affected area by applying the pulsating liquid sprayed from the handpiece 20 to the living tissue that is the affected area of the patient. Hereinafter, the liquid to which pulsation is imparted is also referred to as a pulsating flow or a pulsed flow. The liquid to which pulsation is imparted means that the liquid is in a state where the flow rate or flow velocity is fluctuated. The fluctuation referred to here includes intermittent injection in which the flow rate or flow velocity becomes zero and repeats the injection and repeats the injection. However, since the flow rate or flow velocity of the liquid only needs to fluctuate, it does not necessarily need to be intermittent injection.

  In the present embodiment, the pulsation generator 24 is a well-known one that includes a piezoelectric element and a diaphragm. The piezoelectric element is operated by the drive voltage applied from the control unit 80 to increase or decrease the volume of the liquid chamber partitioned by the diaphragm, thereby changing the pressure of the liquid in the liquid chamber and imparting pulsation to the liquid.

  The control unit 80 is a device that controls the overall operation of the medical device 10 and is connected to a foot switch 94 that is operated by a surgeon with a foot. The controller 80 particularly controls the tube pump 60 and the pulsation generator 24. Specifically, the control unit 80 transmits a drive signal via the pump cable 91 and the actuator cable 92 while the foot switch 94 is stepped on. The drive signal transmitted via the pump cable 91 drives the tube pump 60. When the tube pump 60 is driven, the liquid is supplied to the handpiece 20. The drive signal transmitted via the actuator cable 92 drives the pulsation generator 24. When the pulsation generator 24 is driven, pulsation is imparted to the liquid. Therefore, the pulse flow is ejected while the surgeon is stepping on the foot switch 94, and the pulse flow is stopped while the surgeon is not stepping on the foot switch 94.

  The control unit 80 is connected to an ejection condition setting unit 96 for the user to set the liquid ejection conditions. The injection condition setting unit 96 includes a flow rate setting dial 97 and an applied voltage setting dial 98.

  The flow rate setting dial 97 is a dial type operation unit for an operator (or a user other than the operator) to set the flow rate Q (ml / min) of the liquid supplied from the liquid supply unit 50 to the handpiece 20. . The applied voltage setting dial 98 is a dial type operation unit for setting an applied voltage E (V) of a drive signal to be transmitted to the pulsation generating unit 24 by an operator (a user other than the operator is also allowed).

  The user adjusts the combination of the value of the flow rate Q and the value of the applied voltage E to adjust various combinations of the liquid ejected from the handpiece 20 such as the discharge pressure, flow rate, and droplet shape of the liquid ejected from the handpiece 20. The injection conditions can be set. The injection condition setting unit 96 is not limited to the flow rate setting dial 97 and the applied voltage setting dial 98, and may include other operation units. For example, an operation unit for setting various injection conditions, such as a frequency setting unit for the user to set the frequency of the applied voltage and a waveform setting unit for the user to set the waveform of the drive signal. The setting unit 96 may be provided.

  The control unit 80 stores table data TBL. The table data TBL will be described in detail later.

B. Tube pump configuration:
FIG. 2 is an explanatory diagram conceptually showing the structure of the tube pump 60. As illustrated, the tube pump 60 includes a rotor 61 including a roller (pressing member) 62 and a stator (guide member) 65.

  The stator 65 has a shape having an arcuate recess 65a. The pump tube 55 described in FIG. 1 is disposed along the wall surface of the recess 65a. The pump tube (hereinafter, also simply referred to as “tube”) 55 is made of silicon, fluororubber, elastic resin, or the like, and has elasticity.

  Four rollers 62 are arranged on the outer periphery of the rotor 61 at equal intervals. The rotor 61 is rotated about the rotation shaft 63 by a drive motor (not shown). This drive motor is driven by the drive signal received via the pump cable 91 (FIG. 1). Each roller 62 is an idler wheel. The position of the rotor 61 with respect to the stator 65 is determined so that each roller 62 presses the tube 55. As the rotor 61 rotates in the R direction, the position of each roller 62 also rotates. As a result, the tube 55 is sequentially squeezed while being crushed by the rollers 62. As a result, the liquid in the tube 55 is conveyed. Note that the number of rollers 62 is not limited to four, and may be other numbers (one or more) such as three, two, one, five, and the like.

  FIG. 3 is a perspective view of the tube pump 60 with the opening / closing part 70 opened. As illustrated, the opening / closing part 70 is provided with a stator 65. The tube 55 is loaded into the tube pump 60 by spanning the tube 55 from the in-side loading groove 71 through the roller 62 to the out-side loading groove 72 with the opening / closing portion 70 opened.

  FIG. 4 is a cutaway sectional view showing the internal configuration of the opening / closing part 70. As shown in the figure, the opening / closing part 70 is formed with a storage part 73 for storing the stator 65 in a state in which the recess 65a protrudes.

  Inside the accommodating portion 73, a pressing motor 75, a connecting member 76, a pressing member 77, and two springs 78 and 79 are provided. The connecting member 76 constitutes a ball screw structure that engages with the screw shaft 75a of the pressing motor 75 to change the rotation of the screw shaft 75a into a linear motion in the Y direction. A pressing member 77 is connected below the connecting member 76 (+ side in the Y direction). The pressing member 77 is juxtaposed with a surface (referred to as a rear surface) 65b on the opposite side (the negative side in the Y direction) 65b of the stator 65 with a gap. Two springs 78 and 79 are disposed in the gap. Each spring 78, 79 is a so-called coil spring.

  In an initial state, a predetermined distance is provided between the pressing member 77 and the rear surface 65b of the stator 65. The predetermined distance is sized according to the length of each spring 78, 79, and the biasing force of each spring 78, 79 in the initial state is a predetermined value P0. When the pressing motor 75 is rotated forward, the connecting member 76 moves the pressing member 77 to the + side in the Y direction, and the urging forces of the springs 78 and 79 can be made larger than the value P0. As a result, an urging force (which can also be referred to as a pressing force to press) the stator 65 toward the tube 55 increases. The increase in the urging force is proportional to the amount of forward rotation of the pressing motor 75. The pressing motor 75 is driven by a drive signal received from the control unit 80 (FIG. 1) via the urging force adjusting cable 99 (FIG. 1).

  In the present embodiment, the two springs 78 and 79 correspond to the subordinate concept of the “biasing member” according to an embodiment of the present invention. The pressing motor 75, the connecting member 76, and the pressing member 77 correspond to the subordinate concept of the “biasing force adjusting unit” in one embodiment of the present invention. The control unit 80 in FIG. 1 executes an urging force adjustment control process for controlling a drive signal for driving the pressing motor 75. This urging force adjustment control process will be described next.

C. Configuration of urging force adjustment control processing:
FIG. 5 is a flowchart showing the urging force adjustment control process. The urging force adjustment control process is started when the flow rate setting dial 97 is operated by the user after the power supply (not shown) of the medical device 10 is turned on.

  When the process is started, the control unit 80 operates the flow rate setting dial 97 and acquires the liquid flow rate Q set by the ejection condition setting unit 96 (step S110). Next, the control unit 80 calculates the rotation amount VR of the pressing motor 75 based on the acquired flow rate Q (step S120). This calculation is performed using the table data TBL (FIG. 1) stored in the control unit 80.

  FIG. 6 is an explanatory diagram showing the table data TBL. As shown in the figure, the table data TBL has two items of a flow rate Q and a rotation amount VR of the pressing motor 75, and is tabular data indicating the rotation amount VR of the pressing motor 75 corresponding to the flow rate Q. It is.

  The relationship between the flow rate Q and the rotation amount VR is obtained as follows. First, the urging force of the springs 78 and 79 required according to the flow rate Q is obtained experimentally or by simulation. Next, the displacement in the Y direction of the pressing member 77 (FIG. 4) necessary to obtain the obtained urging force is obtained experimentally or by simulation. Thereafter, the rotation amount VR of the pressing motor 75 necessary to obtain the obtained displacement of the pressing member 77 is obtained experimentally or by simulation. The rotation amount VR corresponding to the flow rate Q thus obtained is recorded in the table data TBL.

  As shown in FIG. 6, for example, when the flow rate Q set by the user is less than 4 ml / min, the rotation amount VR of the pressing motor 75 becomes 0 rotation (does not rotate). When the flow rate Q is 4 ml / min or more and less than 6 ml / min, the rotation amount VR is 1 rotation, and when the flow rate Q is 6 ml / min or more and less than 8 ml / min, the rotation amount VR is 2 rotations. When the flow rate Q is 10 ml / min or more and less than 12 ml / min, the rotation amount VR is 4 rotations. Thus, the table data TBL is determined such that the rotation amount VR increases as the flow rate Q increases.

  In step S120 of FIG. 5, the control unit 80 inputs the liquid flow rate Q acquired in step S110 to the table data TBL, and acquires the rotation amount VR corresponding to the flow rate Q from the table data TBL. Subsequently, the control unit 80 drives the pressing motor 75 based on the rotation amount VR obtained in step S120. Thereafter, the process returns to “return” and the urging force adjustment control process is terminated.

  According to the urging force adjustment control process configured as described above, in the tube pump 60, the urging force of the springs 78 and 79 that urge the stator 65 toward the tube 55 is set by the injection condition setting unit 96. It can be adjusted according to the flow rate Q of the liquid. As described above, the table data TBL is determined so that the rotation amount VR increases as the liquid flow rate Q increases. Therefore, as the set flow rate Q increases, the pressing member 77 and the stator are increased. The distance to 65 becomes narrow, and the urging force of the springs 78 and 79 can be increased. In other words, the smaller the liquid flow rate Q, the wider the distance between the pressing member 77 and the stator 65, and the urging force of the springs 78, 79 can be reduced.

D. Effects of the embodiment:
According to the medical device 10 of the present embodiment configured as described above, in the tube pump 60, the urging forces of the springs 78 and 79 that urge the stator 65 toward the tube 55 are applied to the pressing motor 75 and the connecting member. 76 and the pressing member 77, the maximum ultimate pressure in the liquid ejection pipe 22 when the liquid ejection pipe 22 of the handpiece 20 is clogged in the flow path downstream from the tube pump 60 is appropriately managed. it can. Management is possible because there is a correlation between the biasing force of the springs 78 and 79 and the maximum ultimate pressure. This correlation is a new finding obtained by the inventor of the present invention, and is proved from the following experiment.

  FIG. 7 is an explanatory view showing a liquid supply apparatus of an experimental example. The liquid supply apparatus 100 of the experimental example includes a liquid container 110, a tube pump 120, first and second connectors 130a and 130b, a water supply channel 140, a drain channel 150, an opening / closing valve 160, and a pressure gauge 170. With. The tube pump 120 drains the liquid sucked from the liquid container 110 through the water absorption channel 140 to the outside through the drain channel 150. An opening / closing valve 160 is provided at the end of the drainage channel 150 opposite to the tube pump 120, and a pressure gauge 170 is connected to the drainage channel 150 in the middle.

  The tube pump 120 is of a type that can bias the stator toward the tube by a spring, but the biasing force of the spring is constant and cannot be varied. That is, the tube pump 120 has a configuration that does not include an urging force adjusting unit that adjusts the urging force of the spring. In this experimental example, the tube pump 120 was disassembled, and the spring itself was replaced with a spring having a different length (which means natural length, hereinafter referred to as “spring length”). Specifically, the spring length was changed to three types of springs of 12.4 mm, 13.5 mm, and 15 mm. These springs differ only in spring length, and the dimensions and materials that determine the spring characteristics other than the spring length are the same. Since the gap to which the spring is attached is constant, the urging force of the spring increases as the spring length increases. That is, among the three types of springs, a spring having a spring length of 12.4 mm has the smallest biasing force, and a spring having a spring length of 15 mm has the largest biasing force. A spring having a spring length of 13.5 mm is an intermediate urging force.

  An experiment was conducted for each case to which the above 12.4 mm, 13.5 mm, and 15 mm springs were attached. For details of the experiment, the open / close valve 160 is opened and the tube pump 120 is operated, then the open / close valve 160 is fully closed and the drainage flow path 150 is closed. Then, the pressure change in the drainage channel 150 from the start of the blockage is measured by the pressure gauge 170.

  FIG. 8 is a graph showing the pressure change in each case. As can be seen from the graph, the rate of pressure increase from the start of occlusion hardly changes in any spring. The pressure from the start of closing increases and settles to a constant pressure (maximum ultimate pressure). This maximum ultimate pressure varies depending on the type of spring. A spring having a spring length of 12.4 mm has the lowest maximum ultimate pressure, and a spring having a spring length of 15 mm has the highest maximum ultimate pressure. A spring having a spring length of 13.5 mm has an intermediate maximum ultimate pressure.

  FIG. 9 is a graph showing the relationship between the spring length and the maximum ultimate pressure in each case. As can be seen from this graph, the shorter the spring length, the lower the maximum ultimate pressure. From these facts, it was found that the smaller the urging force of the spring, the lower the maximum ultimate pressure.

  In the case of a general tube pump, as can be seen from FIG. 8, the pressure rise in the drainage flow channel after the start of the blockage is steep. For this reason, when a general tube pump is adopted as a liquid supply apparatus that supplies liquid to a medical liquid ejecting apparatus, the following problems occur. If foreign matter is mixed in the liquid jet tube of the liquid supply device, the liquid jet tube is clogged and it becomes impossible to eject the liquid. However, there is a possibility that the obstruction is removed from the clogged state for some reason. When the obstruction is removed, there is a possibility that a very strong jet may temporarily occur at the moment of removal.

  In the medical device 10 of this embodiment, the maximum ultimate pressure at the time of obstruction | occlusion can be lowered | hung by making the setting of the flow volume Q of the liquid by the injection condition setting part 96 low. Generally, in a site where low invasiveness is important (for example, the brain), the setting of the liquid flow rate Q is lowered. In such a case, the medical device 10 has a lower maximum ultimate pressure. Such a problem that strong injection occurs at the moment when the obstruction is removed can be prevented.

E. Variations:
The present invention is not limited to the above-described embodiment and its modifications, and can be carried out in various modes without departing from the gist thereof. For example, the following modifications are possible.

・ Modification 1:
In the embodiment, the coil spring is used as the biasing member, but other types of springs such as a plate spring and an air spring may be used instead. Further, the spring may be made of metal or resin. Further, as the biasing member, an elastic resin, a rubber material, or the like in which the material itself having no spring shape has an elastic force may be used.

Modification 2
In the above-described embodiment, the urging force adjusting unit is configured by the pressing motor 75, the connecting member 76, and the pressing member 77, but the urging force adjusting unit is not necessarily limited to this configuration. For example, it is good also as a structure which transmits the driving force of a motor to an urging | biasing member using the power transmission mechanism of another structure. Moreover, it is good also as a structure which adjusts the urging | biasing force of an urging | biasing member by human power, without using a motor. For example, the pressing member can be moved by a slide lever operated by the user.

・ Modification 3:
In the above embodiment, the urging force adjusting unit is controlled based on the flow rate Q set by the injection condition setting unit 96, but instead, based on an adjustment instruction from a dedicated button for urging force adjustment. The urging force adjusting unit may be controlled. Furthermore, it is good also as a structure which controls an urging | biasing force adjustment part based on parameters other than the set flow volume and an adjustment instruction | indication. For example, the urging member may be a shape memory alloy spring, and the urging force of the spring may be changed based on the ambient temperature.

-Modification 4:
In the above-described embodiment, the pulsation generating unit 24 provided in the handpiece 20 is configured to include a volume adjusting unit including a piezoelectric element and a diaphragm. However, instead of this, the volume of the liquid chamber is increased by a driving source other than the piezoelectric element. It is good also as a structure which adjusts. Further, a bubble generating unit that generates bubbles in the liquid in the liquid chamber may be provided to change the pressure of the liquid in the liquid chamber. The bubble generation unit may be configured to irradiate an optical maser, laser light, resistor heater, ceramic heater, microwave, or the like.

Modification 5:
The purpose of use of the medical device of the present invention may not be human therapy. For example, animals other than humans may be treated, or human tissue may be excised for research or education. Moreover, the tube pump of the present invention may be used in a cleaning device that removes dirt with the ejected liquid, or may be used in a drawing device that draws a line or the like with the ejected liquid.

Modification 6:
In the embodiment, the urging force of the springs 78 and 79 is adjusted by the pressing motor 75, the connecting member 76, and the pressing member 77. According to this configuration, since the tube is formed of an elastic material, the position of the stator 65 approaches or moves away from the rotation trajectory of the roller 62. On the other hand, as a modification, the pressing motor 75, the connecting member 76, and the pressing member 77 may be omitted to adjust the distance between the wall surface of the recess of the stator and the track of the rotor. If the distance can be adjusted, the stator side may be moved, or a rotor having a roller may be moved. This movement may be moved by the power of the motor or by human power.

Modification 7:
In the above embodiment, the urging force for urging the stator 65 toward the tube 55 is adjusted by adjusting the urging force of the springs 78 and 79. However, instead of this, a roller 62 is disposed. The entire stator 65 may be configured to be biased by a biasing member in a direction in which the tube 55 is biased toward the stator 65, and the biasing force of the biasing member may be adjusted. Also with this configuration, similarly to the first embodiment, the maximum ultimate pressure in the liquid ejecting apparatus when the liquid ejecting apparatus is clogged can be appropriately managed.

  The present invention is not limited to the above-described embodiments, examples, and modifications, and can be realized with various configurations without departing from the spirit of the present invention. For example, the technical features in the embodiments, examples, and modifications corresponding to the technical features in each embodiment described in the summary section of the invention are to solve some or all of the above-described problems, or In order to achieve part or all of the above-described effects, replacement or combination can be performed as appropriate. Further, if the technical feature is not described as essential in the present specification, it can be deleted as appropriate.

DESCRIPTION OF SYMBOLS 10 ... Medical device 20 ... Handpiece 22 ... Liquid injection pipe 22a ... Opening part 24 ... Pulsation generation | occurrence | production part 26 ... Housing | casing 50 ... Liquid supply part 51 ... Water supply bag 52 ... Spike needle 53a-53e ... 1st-5th connector 54a -54d ... 1st-4th water supply tube 55 ... Pump tube (tube)
56 ... Blockage detection mechanism 57 ... Filter 60 ... Tube pump 61 ... Rotor 62 ... Roller 63 ... Rotating shaft 65 ... Stator 70 ... Opening / closing part 71, 72 ... Loading groove 73 ... Storage part 75 ... Motor for pressing 75a ... Screw shaft 76 ... Connecting member 77 ... Pressing member 78, 79 ... Spring 80 ... Control unit 91 ... Pump cable 92 ... Actuator cable 94 ... Foot switch 96 ... Injection condition setting unit 97 ... Flow rate setting dial 98 ... Applied voltage setting dial 99 ... Biasing force Adjustment cable TBL ... Table data Q ... Flow rate VR ... Rotation amount

Claims (5)

A tube pump that conveys the liquid in the tube by moving the pressing member while crushing the tube arranged along the guide member with the pressing member,
A biasing member that biases the guide member toward the tube;
An urging force adjusting unit for adjusting the urging force of the urging member;
A tube pump comprising:   The tube pump according to claim 1 for supplying a liquid to a medical liquid ejecting apparatus. A medical device,
A tube pump for transporting the liquid in the tube by moving the pressing member while crushing the tube arranged along the guide member with the pressing member;
A liquid ejecting apparatus that receives a supply of liquid from the tube pump;
With
The tube pump is
A biasing member that biases the guide member toward the tube;
An urging force adjusting unit for adjusting the urging force of the urging member;
A medical device comprising: The medical device according to claim 3,
A flow rate setting unit for setting a flow rate of the liquid supplied to the liquid ejecting apparatus;
A control unit for controlling the biasing force adjusting unit based on the set flow rate;
A medical device comprising: The medical device according to claim 4,
The said control part is a medical device which makes the said energizing force small, so that the said set flow volume is small.

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