JP2023146439A - Hemostatic device - Google Patents

Abstract

To provide a hemostatic device capable of preventing a gas from remaining in a balloon when a liquid is injected into the balloon.SOLUTION: A hemostatic device 10 comprises a balloon 40, a belt 21 (equivalent to "a belt body"), and a discharge part 70. The balloon has a lumen 40a to inject a liquid therein, is configured to compress a puncture site P formed at a patient, and is expandable and contractable. The balloon is fixed to the wrist W with the belt. The discharge part is disposed at the balloon to discharge a gas in the balloon to the outside of the balloon with injection of the liquid into a lumen.SELECTED DRAWING: Figure 4

Description

The present invention relates to a hemostatic device for compressing a punctured site to stop bleeding.

In recent years, percutaneous treatment and testing has become popular, in which a blood vessel in an arm or leg is punctured, an introducer sheath is introduced into the puncture site, and a medical device such as a catheter is delivered to the affected area through the lumen of the introducer sheath. etc. are being carried out. When performing such treatment, examination, etc., the operator needs to stop the bleeding at the puncture site after removing the introducer sheath. In order to stop the bleeding, a band is used to wrap around limbs such as arms and legs, and a fixing means is connected to the band to fix the band while being wrapped around the limb. BACKGROUND ART A hemostatic device is known that includes a balloon that is an expansion member that expands and presses a puncture site.

In such a hemostasis device, if the expanded balloon continues to strongly compress the puncture site and the surrounding blood vessels and nerves for a long period of time, it may cause numbness or pain or occlude the blood vessel. To prevent blood vessel occlusion, doctors and nurses generally connect a special instrument such as a syringe to a hemostatic device after inflating the balloon, drain the fluid inside the balloon, and then close the balloon. By performing a pressure reduction operation to reduce the internal pressure, the compressive force acting on the puncture site is reduced over time.

On the other hand, the hemostasis device according to Patent Document 1 below involves inflating a balloon with a liquid (such as water) having ultrasonic properties and disposing a liquid (such as water) having ultrasonic properties in the balloon. is disclosed. For this reason, the structure is such that the ultrasonic waves emitted from the ultrasonic probe can propagate to the living tissue and allow the ultrasonic waves to pass through. This makes it possible to generate an ultrasound image of the blood vessel puncture site.

US Patent Application Publication No. 2019/0274692

The propagation of ultrasonic waves is greatly affected by the difference in acoustic impedance (density x speed of sound) between propagation media. When liquid is injected into the balloon, gas remains in the balloon. Because gas has a significantly different acoustic impedance than soft tissue within the body, most of the ultrasound waves are reflected at the interface and do not propagate beyond that. Therefore, there is a possibility that the ultrasound image of the blood vessel puncture site cannot be confirmed.

Patent Document 1 does not disclose a solution to the problem that occurs when a liquid is injected into a balloon.

The present invention has been made to solve the above problems, and an object of the present invention is to provide a hemostatic device that can prevent gas from remaining in a balloon when liquid is injected into the balloon.

A hemostatic device according to the present invention includes an inflatable and deflated balloon having a lumen into which a liquid is injected and configured to compress a puncture site formed in a patient; It has a band for fixing to a part, and a discharge part disposed on the balloon and discharges the gas inside the balloon to the outside of the balloon as the liquid is injected into the inner cavity.

According to the hemostasis device of the present invention, the balloon is fixed to a part of the patient's body by the band, and when liquid is injected into the inner cavity of the balloon, the expanded balloon presses the puncture site. As liquid is injected into the lumen of the balloon, gas within the balloon is discharged to the outside of the balloon by the discharge section. Therefore, when liquid is injected into the balloon, gas can be prevented from remaining inside the balloon. Since no gas remains within the balloon, for example, even if ultrasound is irradiated from an ultrasound probe toward a puncture site in order to confirm an ultrasound image, the propagating ultrasound is unlikely to be attenuated. Therefore, the ultrasonic image can be suitably confirmed, and the occlusion state of the blood vessel located at the puncture site can be accurately confirmed based on the obtained ultrasonic image.

FIG. 1 is a plan view of the hemostasis device according to the first embodiment, viewed from the inner surface side. 2A is a cross-sectional view for explaining the configuration of the balloon of the hemostatic device according to the first embodiment, FIG. 2(A) is a cross-sectional view showing a state before liquid is injected into the balloon, and FIG. 2(B) is FIG. 3 is a cross-sectional view showing a state when liquid is injected into the balloon. FIG. 2 is a perspective view showing a state in which the hemostasis device according to the first embodiment is worn on the wrist. 4 is a cross-sectional view showing the balloon of the hemostasis device according to the first embodiment in an expanded state, and is a cross-sectional view taken along line 4-4 in FIG. 3. FIG. FIG. 7 is a plan view of the hemostasis device according to the second embodiment, viewed from the inner surface side. 6(A) is a sectional view showing a state before liquid is injected into the balloon, FIG. 6(B) is a sectional view for explaining the configuration of a balloon of a hemostasis device according to a second embodiment; FIG. FIG. 3 is a cross-sectional view showing a state when liquid is injected into the balloon. It is a perspective view which shows the state where the hemostasis device based on 2nd Embodiment is attached to a wrist. 8 is a cross-sectional view showing a state in which the balloon of the hemostatic device according to the second embodiment is expanded, and is a cross-sectional view taken along line 8-8 in FIG. 7. FIG. FIG. 7 is a plan view of a balloon and a support plate of a hemostasis device according to a second embodiment, viewed from the outside. FIG. 7 is a plan view of the balloon and support plate of the hemostasis device according to Modification 1 of the second embodiment when viewed from the outside, showing a state in which the long axis of the ultrasound probe is pressed against the balloon along the longitudinal direction of the support plate. FIG. FIG. 7 is a plan view of the balloon and support plate of the hemostasis device according to Modification 1 of the second embodiment when viewed from the outside, showing a state in which the long axis of the ultrasound probe is pressed against the balloon along the width direction of the support plate. FIG. FIG. 7 is a plan view of the balloon and support plate of the hemostasis device according to Modification 2 of the second embodiment as viewed from the outside, showing a state in which the long axis of the ultrasound probe is pressed against the balloon along the longitudinal direction of the support plate. FIG. FIG. 7 is a plan view of the balloon and support plate of the hemostasis device according to Modification 2 of the second embodiment when viewed from the outside, showing a state in which the long axis of the ultrasound probe is pressed against the balloon along the width direction of the support plate. FIG. FIG. 7 is a plan view of a balloon and a support plate of a hemostasis device according to Modification 3 of the second embodiment, viewed from the outside. FIG. 7 is a plan view of a balloon and a support plate of a hemostasis device according to a fourth modification of the second embodiment, viewed from the outside. FIG. 7 is a cross-sectional view for explaining the configuration of a balloon of a hemostasis device according to modification 5 of the second embodiment, and is a cross-sectional view showing a state when liquid is injected into the balloon. 17 is a sectional view showing a hemostasis device according to modification 5 of the second embodiment, and is an enlarged sectional view of a main part of section A in FIG. 16. FIG. FIG. 7 is a plan view of a balloon and a support plate of a hemostasis device according to modification 5 of the second embodiment, viewed from the outside.

Embodiments of the present invention and modifications thereof will be described below with reference to the attached drawings. Note that the following description does not limit the technical scope or meaning of terms described in the claims. Further, the dimensional ratios in the drawings are exaggerated for convenience of explanation and may differ from the actual ratios.

<First embodiment>
A first embodiment of the present invention will be described with reference to FIGS. 1 to 4.

1 and 2 are diagrams for explaining the configuration of each part of the hemostasis device 10 according to the first embodiment. 3 and 4 are diagrams schematically showing an example of how the hemostasis device 10 is used.

As shown in FIGS. 3 and 4, the hemostasis device 10 according to the first embodiment is attached to the wrist W ("a part of the patient's body") for the purpose of inserting a catheter or the like for treatment, examination, etc. into a blood vessel. This is used to stop bleeding at the puncture site P after removing the introducer sheath that has been placed in the puncture site P formed in the radial artery R (equivalent). Furthermore, the hemostasis device 10 is configured to be able to obtain ultrasound images using the ultrasound probe 80 (see FIG. 4). Based on the obtained ultrasound image, the state of occlusion of the blood vessel located at the puncture site P (such as the diameter of the blood vessel) can be confirmed.

As shown in FIGS. 1 and 2, the hemostasis device 10 includes a balloon 40, a belt 21 (corresponding to a "band"), and a discharge section 70. The balloon 40 has a lumen 40a into which a liquid is injected, is configured to compress a puncture site P formed in a patient, and is expandable and deflated. Balloon 40 is fixed to wrist W by belt 21. The discharge part 70 is disposed in the balloon 40 and discharges the gas inside the balloon 40 to the outside of the balloon 40 as liquid is injected into the lumen 40a.

The hemostasis device 10 further includes a hook-and-loop fastener 30 for fixing the belt 21 around the wrist W, a marker 40c for aligning the balloon 40 with the puncture site P, and an injection part 60 capable of injecting liquid into the balloon 40. It has .

In this specification, when the belt 21 is wrapped around the wrist W, the surface of the wrist W that faces the body surface (wearing surface) is referred to as the "inner surface", and the surface opposite thereto is referred to as the "outer surface". It is called. Furthermore, when the belt 21 is wound around the wrist W, the circumferential direction of the wrist W is referred to as the "longitudinal direction", and the direction intersecting the longitudinal direction is referred to as the "width direction".

As shown in FIGS. 1 and 4, the belt 21 includes a first belt 23 connected to one longitudinal end of the balloon 40 (the left end in FIG. 1), and a first belt 23 connected to the other longitudinal end of the balloon 40 (the left end in FIG. 1). The second belt 24 is connected to the right end (in FIG. 1). Unless the first belt 23 and the second belt 24 are separately described, the first belt 23 and the second belt 24 will be collectively referred to as the belt 21.

The belt 21 is made of a flexible band-shaped member. The belt 21 is connected to the balloon 40 and wrapped around the outer circumference of the wrist W, as shown in FIGS. 1, 3, and 4. The inner surface of the end of the belt 21 is joined to the end of the balloon 40 by a method such as fusion (thermal fusion, high frequency fusion, ultrasonic fusion, etc.) or adhesive (adhesion using an adhesive or solvent).

A male side (or female side) 31 of the hook-and-loop fastener 30 is arranged on the outer surface side of a portion of the first belt 23 near the left end in FIG. 1, and a portion of the second belt 24 near the right end in FIG. A female side (or male side) 32 of the hook-and-loop fastener 30 is arranged on the inner surface side of the hook-and-loop fastener 30 . The hook and loop fastener 30 is, for example, a hook and loop fastener known as a common product such as VELCRO (registered trademark) or Velcro tape (registered trademark) in Japan. As shown in FIG. 4, the belt 21 is attached to the wrist W by wrapping the belt 21 around the wrist W and joining the male side 31 and the female side 32. Note that the means for fixing the belt 21 in a state where it is wrapped around the wrist W is not limited to the hook-and-loop fastener 30; for example, a fixing member such as a snap, a button, a clip, or a frame member through which the end of the belt 21 is passed may be used. good.

The belt 21 is made of a material with lower elasticity than the balloon 40. Further, as shown in FIG. 1, the belt 21 is connected to the balloon 40 at a position that does not overlap with at least a part of the area in the surface direction of the balloon 40. The discharge section 70 is arranged in a region of the balloon 40 where the belt 21 does not overlap.

Since the elasticity of the belt 21 is lower than that of the balloon 40, the balloon 40 can be pressed against the outer periphery of the wrist W without creating a gap. Therefore, an air layer is less likely to be formed between the balloon 40 and the outer periphery of the wrist W, and attenuation of the ultrasonic waves emitted from the ultrasonic probe 80 is less likely to occur when generating an ultrasonic image. Further, in the balloon 40, there is no other member covering the outer surface of the balloon 40 at a position where it does not overlap with the belt 21. Therefore, the ultrasonic probe 80 can be directly pressed against the outer surface of the balloon 40, and the ultrasonic waves emitted from the ultrasonic probe 80 are less likely to be attenuated. The outer surface of the discharge section 70 is not covered by the belt 21. Therefore, the gas within the balloon 40 is discharged to the outside of the balloon 40 through the discharge section 70 without remaining within the balloon 40. Therefore, with the above configuration, ultrasonic waves are less likely to be attenuated due to the presence of air or the presence of boundaries with other members. Therefore, the occlusion state of the blood vessel located at the puncture site P can be confirmed more accurately based on the obtained ultrasound image.

The constituent material of the belt 21 is not particularly limited as long as it is a flexible material. Such materials include, for example, polyvinyl chloride, polyethylene, polypropylene, polybutadiene, polyolefins such as ethylene-vinyl acetate copolymer (EVA), polyesters such as polyethylene terephthalate (PET), polybutylene terephthalate (PBT), etc. , polyvinylidene chloride, silicone, polyurethane, polyamide elastomer, polyurethane elastomer, polyester elastomer, and other thermoplastic elastomers, or arbitrary combinations of these (blended resins, polymer alloys, laminates, etc.).

The balloon 40 has a function of expanding by injecting liquid and applying pressure to the puncture site P. The balloon 40 is further provided with a discharge part 70 for discharging the gas inside the balloon 40 to the outside of the balloon 40 as liquid is injected into the lumen 40a. The liquid injected into the balloon 40 is not particularly limited as long as the balloon 40 can be expanded, and for example, water, physiological saline, etc. can be used.

The temperature of the liquid injected into balloon 40 can be relatively cold. By doing so, the pain near the puncture site P can be alleviated.

As shown in FIGS. 1, 2(A), 2(B), and 4, the balloon 40 is made by overlapping two approximately rectangular sheets and bonding or heat-sealing (using ultrasonic or laser) the periphery. It is composed of a bag-shaped member. As a result, an inner cavity 40a is formed between the two sheets. The sheet shown on the upper side in FIGS. 2A and 2B and located on the outer surface side of the balloon 40 is referred to as a first sheet 47. The sheet shown on the lower side in FIGS. 2A and 2B and located on the inner surface of the balloon 40 is referred to as a second sheet 48. In FIGS. 2(A) and 2(B), reference numeral 49 indicates a joint where the first sheet 47 and the second sheet 48 are joined. In FIG. 2(B), reference numeral 51 indicates air bubbles contained in the liquid within the lumen 40a of the balloon 40, and reference numeral 52 indicates gas discharged to the outside of the balloon 40 by the discharge portion 70.

The discharge part 70 is a porous member 71 that constitutes at least part of one surface (the "inner surface") of the balloon 40 located on the side that contacts the body and the other surface (the "outer surface") located on the opposite side. It is configured. The porous member 71 is made of a member that allows passage of gas (for example, air) and restricts passage of liquid.

As liquid is injected into the lumen 40a of the balloon 40, the gas within the balloon 40 passes through the porous member 71 and is discharged to the outside of the balloon 40. Furthermore, the liquid within the balloon 40 is restricted from passing through the porous member 71. Therefore, the pressure force applied to the puncture site P by the balloon 40 does not decrease, and gas can be prevented from remaining in the balloon 40. Therefore, the occlusion state of the blood vessel located at the puncture site P can be confirmed more accurately based on the obtained ultrasound image without reducing the hemostasis function.

In the first embodiment, the first sheet 47 is entirely composed of the porous member 71. The joint portion 49 of the first sheet 47 has lost its function of allowing gas to pass through due to the processing (adhesion, heat fusion, etc.) that forms the joint portion 49 . The balloon 40 is connected to the belt 21 at the end where the joint 49 is formed. Therefore, as shown in FIGS. 1 and 4, the outer surface of the discharge section 70 is not covered by the belt 21.

The constituent material of the porous member 71 is, for example, polyethylene, polyester, fluororesin (PTFE), or the like.

The constituent material of the second sheet 48 in the balloon 40 is not particularly limited as long as it is a flexible material, and for example, the same material as the constituent material of the belt 21, such as polyvinyl chloride, can be used. Polyvinyl chloride is a material that has an acoustic impedance relatively close to that of living tissue, so it is suitable for use as a constituent material of the second sheet 48.

It is preferable that at least a portion of the other portions of the balloon 40 other than the portion made of the porous member 71 be made of a material having lower elasticity than the porous member 71.

In the first embodiment, the second sheet 48 in the balloon 40 is made of a material with lower elasticity than the porous member 71, such as polyvinyl chloride. In the balloon 40, the elongation of the discharge part 70 made of the porous member 71 is suppressed by other parts. Therefore, deterioration in the function of the porous member 71 due to elongation can be suppressed.

The exhaust section 70 can be configured to exhaust gas from the maximum expansion section 72 of the balloon 40 located at the farthest position from the patient's body when the balloon 40 is expanded.

Here, "the maximum expansion part 72 disposed at the position farthest from the patient's body" means the part that becomes the apex of the balloon 40 when the balloon 40 is expanded. With this configuration, since the gas remaining in the balloon 40 is accumulated in the maximum expansion part 72, the discharge part 70 can discharge the gas in the balloon 40 from the maximum expansion part 72 to the outside of the balloon 40. Note that when using the hemostasis device 10, depending on how the wrist W is tilted, the maximum expansion portion 72 may not coincide with the apex of the balloon 40 in its current posture. However, the wrist W still moves to some extent even when the bleeding is stopped. Furthermore, when checking the ultrasound image, the ultrasound probe 80 is moved. Therefore, the gas remaining in the balloon 40 accumulates in the maximum expansion part 72 due to the movement of the wrist W or the operation of the ultrasound probe 80, and the gas in the balloon 40 can be discharged to the outside of the balloon 40.

The outer shape of the balloon 40 is not particularly limited. For example, the balloon 40 may have an external shape such as a circle, an ellipse, or a polygon when viewed from above in an unexpanded state.

The balloon 40 is preferably substantially transparent, but is not limited to being transparent, and may be translucent or colored transparent. Thereby, the puncture site P can be visually recognized from the outside surface side, and a marker 40c, which will be described later, can be easily aligned with the puncture site P.

The marker 40c is provided approximately at the center of the outer surface of the balloon 40, as shown in FIG. By providing such a marker 40c on the balloon 40, the balloon 40 can be easily aligned with the puncture site P, so that misalignment of the balloon 40 is suppressed. Note that the marker 40c may be provided on the side of the balloon 40 facing the wrist W. At this time, the marker 40c is preferably provided on the inner surface of the balloon 40 so as not to come into direct contact with the puncture site P.

The shape of the marker 40c is not particularly limited, and examples thereof include a circle, a triangle, and a quadrangle. In this embodiment, the shape is a quadrangle.

The size of the marker 40c is not particularly limited, but for example, when the marker 40c has a rectangular shape, it is preferable that the length of one side of the marker 40c is in the range of 1 to 4 mm. If the length of one side is 5 mm or more, the size of the marker 40c becomes larger than the size of the puncture site P, making it difficult to align the center of the balloon 40 with the puncture site P.

The material of the marker 40c is not particularly limited, and examples thereof include oil-based colorants such as ink, resins kneaded with pigments, and the like.

The color of the marker 40c is not particularly limited as long as it allows the balloon 40 to be aligned with the puncture site P, but a greenish color is preferable. By using a greenish color, the marker 40c can be easily seen on blood or skin, so that it becomes easier to align the balloon 40 with the puncture site P.

Moreover, it is preferable that the marker 40c is semitransparent or colored and transparent. Thereby, the puncture site P can be visually recognized from the outer surface side of the marker 40c.

The method of providing the marker 40c on the balloon 40 is not particularly limited, but examples include a method of printing the marker 40c on the balloon 40, a method of fusing the marker 40c to the balloon 40, a method of applying an adhesive to one side of the marker 40c, and a method of attaching the marker 40c to the balloon 40. Examples include a method of pasting it on the .

The injection part 60 is a part for injecting liquid into the balloon 40, and is connected to the balloon 40 as shown in FIG.

The injection part 60 can be connected to a flexible tube 61 that communicates with the inner lumen 40a of the balloon 40, a tubular connector 63 that is connected to the tube 61 and has a built-in check valve (not shown), and the connector 63. syringe 64. The syringe 64 is filled with liquid to be injected into the balloon 40. The position where the tube 61 is connected in the balloon 40 is not particularly limited as long as the tube 61 communicates with the lumen 40a of the balloon 40.

When expanding (inflating) the balloon 40, insert the front barrel part of the syringe 64 into the connector 63, open the check valve, push the pusher of the syringe 64, and inject the liquid in the syringe 64 through the injection part 60. and inject into the balloon 40. After injecting the liquid into the balloon 40, when the front barrel portion of the syringe 64 is removed from the connector 63, a check valve built into the connector 63 closes to prevent leakage of the liquid.

Next, a method of using the hemostasis device 10 according to this embodiment will be explained.

Before the hemostatic device 10 is attached to the wrist W, the balloon 40 is in an unexpanded state (see FIG. 2(A)). Echo jelly, gel, or the like that can transmit ultrasonic waves is applied between the inner surface of the balloon 40 and the wrist W. As shown in FIGS. 3 and 4, when puncturing the radial artery R of the wrist W of the right hand, the puncture site P is at a position biased toward the thumb side. Usually, an introducer sheath is placed in the puncture site P. Wrap the belt 21 around the wrist W with the introducer sheath still in place, align the balloon 40 and the belt 21 so that the marker 40c provided on the balloon 40 overlaps the puncture site P, and attach the hook-and-loop fastener. The male side 31 and female side 32 of 30 are brought into contact and joined, and the belt 21 is attached to the wrist W.

At this time, the hemostasis device 10 is attached to the wrist W so that the injection part 60 faces the downstream side (palm side) of the blood flow of the radial artery R. Thereby, the injection part 60 can be operated without interfering with the procedure upstream of the wrist W or with instruments located upstream (for example, a blood pressure monitor, etc.). Furthermore, by attaching the hemostasis device 10 to the wrist W of the right hand so that the injection part 60 faces downstream, the balloon 40 is located in the radial artery R, which is biased towards the thumb side of the wrist W. Note that in the case of an artery, the upstream side of the blood vessel refers to the direction of the blood vessel approaching the heart. Further, the downstream side of the blood vessel refers to the direction of the blood vessel away from the heart.

Note that the hemostasis device 10 may be used when puncturing the radial artery R of the wrist W of the left hand. In this case, the injection part 60 is attached to the wrist W of the left hand so as to face upstream of the blood flow of the radial artery R.

After the hemostasis device 10 is attached to the wrist W, the syringe 64 is connected to the connector 63 of the injection part 60, and the liquid is injected into the balloon 40 as described above to inflate the balloon 40.

As shown in FIGS. 2A and 2B, the discharge section 70 discharges the gas inside the balloon 40 to the outside of the balloon 40 as the liquid is injected into the lumen 40a of the balloon 40. The gas in the lumen 40a becomes bubbles 51 and rises in the liquid. The porous member 71 constituting the discharge section 70 has the function of allowing gas to pass through and restricting the passage of liquid. The gas in the inner cavity 40a passes through the porous member 71 and is discharged to the outside. The gas 52 discharged to the outside diffuses into the atmosphere. Therefore, the lumen 40a of the balloon 40 is filled with liquid without the presence of air.

Echo jelly, gel, or the like that can transmit ultrasonic waves is applied to the outer surface of the balloon 40 and the ultrasonic probe 80. As shown in FIG. 4, the ultrasonic probe 80 is pressed against the outer surface of the balloon 40, and ultrasonic waves are emitted from the ultrasonic probe 80 toward the puncture site P.

The ultrasonic probe 80 is in close contact with the first sheet 47 of the balloon 40, the inner cavity 40a of the balloon 40 is free of air, and the second sheet 48 of the balloon 40 is in close contact with the wrist W. Therefore, the ultrasonic waves emitted from the ultrasonic probe 80 propagate through the first sheet 47, the liquid in the balloon 40, the second sheet 48, and the living tissue. The acoustic impedance difference between propagation media is greatly involved in the propagation of ultrasonic waves. Since the hemostatic device 10 reduces the boundary surface of the propagation medium as much as possible, attenuation of the propagating ultrasonic waves is unlikely to occur. Therefore, the ultrasonic image can be suitably confirmed, and the occlusion state of the blood vessel located at the puncture site P can be accurately confirmed based on the obtained ultrasonic image.

Since the occlusion state of the blood vessel can be accurately confirmed based on the ultrasound image, the degree of expansion of the balloon 40, that is, the compression force acting on the puncture site P, can be easily and accurately adjusted depending on the case. For example, if too much liquid is injected into the balloon 40 and the balloon 40 is over-inflated, the syringe 64 may be used to discharge the excess liquid from within the balloon 40.

After the balloon 40 is expanded, the syringe 64 is removed from the connector 63. Then, the introducer sheath is removed from the puncture site P.

At an appropriate timing, the vascular condition based on the above ultrasound image is confirmed. Based on the blood vessel condition based on the ultrasound image, for example, if hemostasis has not been sufficiently achieved, liquid is injected into the balloon 40 to increase the internal pressure of the balloon 40.

When a predetermined period of time has elapsed and bleeding at the puncture site P has been stopped, the hemostasis device 10 is removed from the wrist W. The hemostatic device 10 is removed from the wrist W by peeling off the male side 31 and female side 32 of the hook and loop fastener 30.

(effect)
As described above, the hemostasis device 10 of the first embodiment includes the balloon 40, the belt 21, and the discharge section 70. The balloon 40 has a lumen 40a into which a liquid is injected, is configured to compress a puncture site P formed in a patient, and is expandable and deflated. Belt 21 secures balloon 40 to a portion of the patient's body. The discharge part 70 is disposed in the balloon 40 and discharges the gas inside the balloon 40 to the outside of the balloon 40 as liquid is injected into the lumen 40a.

According to the hemostatic device 10 configured as described above, when the balloon 40 is fixed to a part of the patient's body by the belt 21 and a liquid is injected into the inner cavity 40a of the balloon 40, the expanded balloon 40 hits the puncture site P. Press. As the liquid is injected into the lumen 40a of the balloon 40, the gas inside the balloon 40 is discharged to the outside of the balloon 40 by the discharge section 70. Therefore, when liquid is injected into the balloon 40, gas can be prevented from remaining inside the balloon 40. Since no gas remains in the balloon 40, even if ultrasound is irradiated from the ultrasound probe 80 toward the puncture site P in order to confirm an ultrasound image, the propagating ultrasound is unlikely to be attenuated. Therefore, the ultrasonic image can be suitably confirmed, and the occlusion state of the blood vessel located at the puncture site P can be accurately confirmed based on the obtained ultrasonic image.

Further, the belt 21 is made of a material with lower elasticity than the balloon 40. Furthermore, it is connected to the balloon 40 at a position that does not overlap with at least a part of the area in the plane direction of the balloon 40. The discharge section 70 is arranged in a region of the balloon 40 where the belt 21 does not overlap. With this configuration, since the stretchability of the belt 21 is lower than the stretchability of the balloon 40, the balloon 40 can be pressed against the outer periphery of the wrist W without creating a gap. Further, in the balloon 40, there is no other member covering the outer surface of the balloon 40 at a position where it does not overlap with the belt 21. The outer surface of the discharge section 70 is not covered by the belt 21. Therefore, ultrasonic waves are less likely to be attenuated due to the presence of air or the presence of boundaries with other members. Therefore, the occlusion state of the blood vessel located at the puncture site P can be confirmed more accurately based on the obtained ultrasound image.

Further, the discharge section 70 is composed of a porous member 71 that constitutes at least part of one surface of the balloon 40 located on the side that contacts the body and the other surface located on the opposite side. The porous member 71 is made of a member that allows the passage of gas and restricts the passage of liquid. With this configuration, as liquid is injected into the lumen 40a of the balloon 40, the gas within the balloon 40 is discharged to the outside of the balloon 40 by passing through the porous member 71. Furthermore, the liquid within the balloon 40 is restricted from passing through the porous member 71. Therefore, the pressure force applied to the puncture site P by the balloon 40 does not decrease, and gas can be prevented from remaining in the balloon 40. Therefore, the occlusion state of the blood vessel located at the puncture site P can be confirmed more accurately based on the obtained ultrasound image without reducing the hemostasis function.

Further, at least a portion of the balloon 40 other than the portion made of the porous member 71 is made of a material having lower elasticity than the porous member 71. With this configuration, in the balloon 40, the expansion of the discharge part 70 made of the porous member 71 is suppressed by other parts. Therefore, deterioration in the function of the porous member 71 due to elongation can be suppressed.

Further, the discharge section 70 is configured to discharge gas from the maximum expansion section 72 located in the balloon 40 at the position farthest from the patient's body when the balloon 40 is expanded. With this configuration, since the gas remaining in the balloon 40 is accumulated in the maximum expansion part 72, the discharge part 70 can discharge the gas in the balloon 40 from the maximum expansion part 72 to the outside of the balloon 40.

<Second embodiment>
Next, a second embodiment of the present invention will be described with reference to FIGS. 5 to 9. In the following explanation, redundant explanation of contents that have already been explained will be omitted. Further, contents not particularly mentioned in the following description can be the same as those in the first embodiment.

A hemostatic device 10A according to the second embodiment differs from the first embodiment in that it includes a support plate 90.

As shown in FIGS. 5 and 6, the hemostasis device 10A includes a balloon 40, a belt 21, and a discharge section 70A, similarly to the first embodiment.

The hemostasis device 10A further includes a support plate 90, as shown in FIGS. 5 to 9. The support plate 90 is made of a harder material than the balloon 40, and has one surface of the balloon 40 located on the side that contacts the body (the "inner surface") and another surface located on the opposite side (the "outer surface" side). ). Belt 21 is connected to support plate 90. Balloon 40 is connected to support plate 90 on the other side (the "outside" side). The support plate 90 has a window 91 that exposes a portion of the other surface (the "outer surface") of the balloon 40. The discharge section 70A is arranged at a position overlapping the window section 91 in the surface direction of the balloon 40.

The support plate 90 is harder than the balloon 40, is disposed on the outer surface of the balloon 40, and is connected to the outer surface of the balloon 40. A belt 21 is connected to this support plate 90. Therefore, the balloon 40 can be pressed against the outer periphery of the wrist W without creating a gap. Therefore, an air layer is less likely to be formed between the balloon 40 and the outer periphery of the wrist W, and attenuation of the ultrasonic waves emitted from the ultrasonic probe 80 is less likely to occur when generating an ultrasonic image. Further, the support plate 90 has a window 91 that exposes a portion of the outer surface of the balloon 40. Therefore, in the balloon 40, there is no other member covering the outer surface at the position of the window portion 91 of the support plate 90. Therefore, the ultrasonic probe 80 can be directly pressed against the outer surface of the balloon 40, and the ultrasonic waves emitted from the ultrasonic probe 80 are less likely to be attenuated. The discharge section 70A is arranged at a position overlapping the window section 91, and the outer surface side is not covered by the support plate 90. Therefore, the gas within the balloon 40 is discharged to the outside of the balloon 40 through the discharge portion 70A without remaining within the balloon 40. Therefore, with the above configuration, ultrasonic waves are less likely to be attenuated due to the presence of air or the presence of boundaries with other members. Therefore, the occlusion state of the blood vessel located at the puncture site P can be confirmed more accurately based on the obtained ultrasound image. Furthermore, the gas discharged through the discharge section 70A does not accumulate between the outer surface of the balloon 40 and the inner surface of the support plate 90.

As shown in FIGS. 5, 8, and 9, the support plate 90 includes a first support plate 93 connected to one longitudinal end of the balloon 40 (left end in FIG. 5), and a first support plate 93 connected to one longitudinal end of the balloon 40 (the left end in FIG. 5). A second support plate 94 is connected to the other end in the direction (the right end in FIG. 5). Unless the first support plate 93 and the second support plate 94 are explained separately, the first support plate 93 and the second support plate 94 will be collectively referred to as the support plate 90.

As shown in FIGS. 5 to 9, the first support plate 93 and the second support plate 94 are arranged apart from each other along the longitudinal direction. The space between the first support plate 93 and the second support plate 94 can be configured as a window portion 91. The form of the window portion 91 of the support plate 90 is not limited to this case. Modifications of the form of the window portion 91 will be described later (see Modification 3 in FIG. 14 and Modification 4 in FIG. 15).

As shown in FIG. 8, the support plate 90 has a plate shape in which at least a portion thereof is curved toward the inner surface (mounting surface side). The support plate 90 is made of a harder material than the balloon 40, and is configured to maintain a substantially constant shape.

The first support plate 93 has a first curved portion 93a curved toward the inner circumference at the right end in FIG. The second support plate 94 has a long shape in the longitudinal direction. A central portion 94a of the second support plate 94 in the longitudinal direction has a flat plate shape with almost no curve. The second support plate 94 has a second curved portion 94b curved toward the inner circumferential side at the left end in FIG. Note that the support plate 90 may not have a non-curved portion such as the central portion 94a, that is, may be curved over its entire length.

The constituent materials of the support plate 90 include, for example, acrylic resin, polyvinyl chloride (especially hard polyvinyl chloride), polyethylene, polypropylene, polyolefin such as polybutadiene, polystyrene, poly-(4-methylpentene-1), polycarbonate, and ABS. Resins, polyesters such as polymethyl methacrylate (PMMA), polyacetals, polyacrylates, polyacrylonitrile, polyvinylidene fluoride, ionomers, acrylonitrile-butadiene-styrene copolymers, polyethylene terephthalate (PET), polybutylene terephthalate (PBT), butadiene - Examples include styrene copolymers, aromatic or aliphatic polyamides, and fluororesins such as polytetrafluoroethylene.

Similarly to the first embodiment, the discharge section 70A is configured to include at least a portion of one surface of the balloon 40 located on the side that contacts the body (the "inner surface") and the other surface located on the opposite side (the "outer surface"). It is composed of a porous member 71 that constitutes. The porous member 71 is made of a member that allows passage of gas (for example, air) and restricts passage of liquid.

As shown in FIGS. 6A and 6B, in the second embodiment, the discharge section 70A is arranged at a position overlapping the window section 91. Therefore, a part of the first sheet 47 is made of the porous member 71. The other parts of the first sheet 47 are made of, for example, polyvinyl chloride, like the second sheet 48. The balloon 40 is connected to the support plate 90 at the end where the joint section 49 is formed and at the region where the discharge section 70A is not present. Therefore, as shown in FIGS. 5, 8, and 9, the outer surface of the discharge portion 70A is not covered by the support plate 90. A region 92 in FIG. 9 indicates a connection location between the balloon 40 and the support plate 90.

As shown in FIG. 9, the area of the discharge section 70A is larger than the contact area of the ultrasonic probe 80. Therefore, when the ultrasonic probe 80 is pressed against the balloon 40, the ultrasonic probe 80 does not cover the entire area of the discharge section 70A. A portion of the discharge section 70A remains exposed to the outside. Therefore, even when the ultrasonic probe 80 is pressed against the balloon 40, the gas inside the balloon 40 is discharged to the outside of the balloon 40 through the discharge portion 70A.

As shown in FIGS. 5, 8, and 9, the belt 21 includes a first belt 23 connected to the longitudinal end of the first support plate 93 (the left end in FIG. 5), and a second support plate 93. The second belt 24 is connected to the longitudinal end of the plate 94 (the right end in FIG. 5). Unless the first belt 23 and the second belt 24 are separately described, the first belt 23 and the second belt 24 will be collectively referred to as the belt 21.

The belt 21 is made of a flexible band-shaped member. The belt 21 is connected to the balloon 40 and wrapped around the outer circumference of the wrist W, as shown in FIGS. 5 to 9. The inner surface of the end of the belt 21 is joined to the end of the support plate 90 by a method such as fusion (thermal fusion, high frequency fusion, ultrasonic fusion, etc.) or adhesive (adhesion using adhesive or solvent). .

The balloon 40 is arranged so as to overlap the first support plate 93 and the second support plate 94. Therefore, as shown in FIG. 8, when the balloon 40 is expanded, the support plate 90 suppresses expansion of the balloon 40 in the direction away from the body surface of the wrist W, and the compressive force of the balloon 40 is transferred to the wrist W side. Concentrate on. Therefore, the puncture site P can be suitably compressed.

(effect)
As described above, the hemostatic device 10A of the second embodiment includes the balloon 40, the belt 21, and the discharge part 70A, similarly to the hemostatic device 10 of the first embodiment. The hemostasis device 10A further includes a support plate 90. The support plate 90 is made of a harder material than the balloon 40, and has one surface of the balloon 40 located on the side that contacts the body (the "inner surface") and another surface located on the opposite side (the "outer surface" side). ). Belt 21 is connected to support plate 90. Balloon 40 is connected to support plate 90 on the other side (the "outside" side). The support plate 90 has a window 91 that exposes a portion of the other surface (the "outer surface") of the balloon 40. The discharge section 70A is arranged at a position overlapping the window section 91 in the surface direction of the balloon 40.

According to the hemostasis device 10A configured as described above, when the balloon 40 is fixed to a part of the patient's body by the support plate 90 and the belt 21 and a liquid is injected into the inner cavity 40a of the balloon 40, the expanded balloon 40 Apply pressure to the puncture site P. As the liquid is injected into the lumen 40a of the balloon 40, the gas inside the balloon 40 is discharged to the outside of the balloon 40 by the discharge section 70A facing the window 91 of the support plate 90. Therefore, when liquid is injected into the balloon 40, gas can be prevented from remaining inside the balloon 40. Since no gas remains in the balloon 40, for example, even if ultrasonic waves are irradiated from the ultrasonic probe 80 toward the puncture site P in order to confirm an ultrasonic image, the propagating ultrasonic waves are unlikely to be attenuated. Therefore, the ultrasonic image can be suitably confirmed, and the occlusion state of the blood vessel located at the puncture site P can be accurately confirmed based on the obtained ultrasonic image.

The support plate 90 is harder than the balloon 40, is disposed on the outer surface of the balloon 40, and is connected to the outer surface of the balloon 40. A belt 21 is connected to this support plate 90. Further, the support plate 90 has a window 91 that exposes a portion of the outer surface of the balloon 40. The discharge section 70A is arranged at a position overlapping the window section 91, and the outer surface side is not covered by the support plate 90. Therefore, ultrasonic waves are less likely to be attenuated due to the presence of air or the presence of boundaries with other members. Therefore, the occlusion state of the blood vessel located at the puncture site P can be confirmed more accurately based on the obtained ultrasound image. Furthermore, the gas discharged through the discharge section 70A does not accumulate between the outer surface of the balloon 40 and the inner surface of the support plate 90.

At least a portion of the other portions of the balloon 40 other than the portion made of the porous member 71 is made of a material with lower elasticity than the porous member 71. With this configuration, in the balloon 40, the elongation of the discharge portion 70A made of the porous member 71 is suppressed by other parts. Therefore, deterioration in the function of the porous member 71 due to elongation can be suppressed. Further, the support plate 90 is connected to the balloon 40 at another portion that has lower elasticity than the porous member 71. Therefore, stretching between the balloon 40 and the support plate 90 can be prevented.

Next, a modification of the second embodiment will be described. In the following explanation, redundant explanation of contents that have already been explained will be omitted. Further, contents not particularly mentioned in the following description can be the same as those in the second embodiment.

<Modification 1>
FIGS. 10 and 11 are plan views of the balloon 40 and the support plate 90 according to Modification 1 of the second embodiment, viewed from the outside. 10 shows a state in which the long axis of the ultrasound probe 80 is pressed against the balloon 40 along the longitudinal direction of the support plate 90, and FIG. The state in which the balloon 40 is pressed against the balloon 40 is shown.

As shown in FIGS. 10 and 11, the window portion 91 has a rectangular shape with a long side 91a located along the longitudinal direction of the support plate 90 and a short side 91b located along the width direction of the support plate 90. has. The porous member 71 constituting the discharge portion 70B includes a center portion 73a disposed at the center position in the plane direction of the window portion 91, a first protrusion portion 73b protruding from the center portion 73a along the long side 91a, and a center portion 73b. It has a second protruding part 73c that protrudes from the part 73a along the short side 91b.

The discharge portion 70B has a substantially cross shape. In the discharge part 70B, the area along the long side 91a of the window part 91 is larger than the contact area of the ultrasound probe 80. In the discharge section 70B, the area of the window section 91 along the short side 91b is larger than the contact area of the ultrasound probe 80. Therefore, when the long axis of the ultrasound probe 80 is pressed against the balloon 40 along the longitudinal direction of the support plate 90 (the state shown in FIG. 10), and when the long axis of the ultrasound probe 80 is pressed against the balloon 40 along the longitudinal direction of the support plate 90, In any case when the ultrasonic probe 80 is pressed against the balloon 40 along the length (the state shown in FIG. 11), the ultrasonic probe 80 does not cover the entire area of the discharge part 70B. A portion of the discharge section 70B remains exposed to the outside. When the ultrasound probe 80 is pressed against the balloon 40, the orientation of the ultrasound probe 80 is not restricted, and the long axis or short axis of the ultrasound probe 80 can be easily aligned with the blood vessel. Therefore, the ultrasonic probe 80 is easy to use. Moreover, even when the ultrasonic probe 80 is pressed against the balloon 40, the gas inside the balloon 40 can be discharged to the outside of the balloon 40 through the discharge part 70B.

<Modification 2>
FIGS. 12 and 13 are plan views of a balloon 40 and a support plate 90 according to a second modification of the second embodiment, viewed from the outside. 12 shows a state in which the long axis of the ultrasound probe 80 is pressed against the balloon 40 along the longitudinal direction of the support plate 90, and FIG. The state in which the balloon 40 is pressed against the balloon 40 is shown.

As shown in FIGS. 12 and 13, the window portion 91 has a rectangular shape with a long side 91a located along the longitudinal direction of the support plate 90 and a short side 91b located along the width direction of the support plate 90. has. The porous member 71 constituting the discharge section 70C has a rectangular shape and is arranged at the four corners of the window section 91. In the balloon 40, the parts other than the discharge part 70C are made of, for example, polyvinyl chloride, like the second sheet 48.

The portion other than the discharge portion 70C has a substantially cross shape. In a portion other than the discharge portion 70C, the area along the long side 91a of the window portion 91 is larger than the contact area of the ultrasound probe 80. In a part other than the discharge part 70C. The area of the window portion 91 along the short side 91b is larger than the contact area of the ultrasound probe 80. Therefore, when the long axis of the ultrasound probe 80 is pressed against the balloon 40 along the longitudinal direction of the support plate 90 (the state shown in FIG. 12), and when the long axis of the ultrasound probe 80 is pressed against the balloon 40 along the longitudinal direction of the support plate 90, In either case when the discharge portion 70C is pressed against the balloon 40 along the length (the state shown in FIG. 13), the discharge portion 70C remains exposed to the outside surface. When the ultrasound probe 80 is pressed against the balloon 40, the orientation of the ultrasound probe 80 is not restricted, and the long axis or short axis of the ultrasound probe 80 can be easily aligned with the blood vessel. Therefore, the ultrasonic probe 80 is easy to use. Moreover, even when the ultrasonic probe 80 is pressed against the balloon 40, the gas inside the balloon 40 can be discharged to the outside of the balloon 40 through the discharge section 70C.

<Modification 3>
FIG. 14 shows a plan view of the balloon 40 and the support plate 90 according to the third modification of the second embodiment, viewed from the outside.

As shown in FIG. 14, the support plate 90 of Modification 3 has a pair of girders 95 extending in the longitudinal direction connecting the first support plate 93 and the second support plate 94. As shown in FIG. The beam portion 95 is located in the width direction of the window portion 91. The window portion 91 is formed by opening a part of the support plate 90.

With this configuration, the pair of beam parts 95 of the support plate 90 can press the ends of the balloon 40 in the width direction. Therefore, it is possible to suppress the position of the balloon 40 from shifting in the width direction.

<Modification 4>
FIG. 15 shows a plan view of a balloon 40 and a support plate 90 according to a fourth modification of the second embodiment, viewed from the outside.

As shown in FIG. 15, the support plate 90 of Modification 4 includes a third support plate 96 and a fourth support plate 97 that extend in the longitudinal direction. The third support plate 96 and the fourth support plate 97 are spaced apart from each other along the width direction. The space between the third support plate 96 and the fourth support plate 97 can be configured as a window portion 91.

The balloon 40 is connected to the inner surface of the third support plate 96 at one end in the width direction (the upper end in FIG. 15), and is connected to the inner surface of the third support plate 96 at the other end in the width direction (the lower end in FIG. 15). Connected to the inner surface.

The third support plate 96 and the fourth support plate 97 are connected to the inner surface of the first belt 23 at one end in the longitudinal direction (the right end in FIG. 15), and are connected to the inner surface of the first belt 23 at the other end in the longitudinal direction (the left end in FIG. 15). At this point, it is connected to the inner surface of the second belt 24 .

Even with such a configuration, the support plate 90 (the third support plate 96 and the fourth support plate 97) is arranged on the outer surface side of the balloon 40 and connected to the outer surface of the balloon 40. A belt 21 is connected to this support plate 90. Therefore, the balloon 40 can be pressed against the outer periphery of the wrist W without creating a gap.

<Modification 5>
A fifth modification of the second embodiment is shown in FIGS. 16 and 17. FIG. 16 is a cross-sectional view for explaining the configuration of the balloon 40 of the hemostasis device 10A according to modification 5, and shows a cross-sectional view of the state when liquid is injected into the balloon 40. FIG. 17 is a cross-sectional view showing a hemostasis device 10A according to modification 5, and shows a cross-section of a main part in which part A in FIG. 16 is enlarged. FIG. 18 shows a plan view of the balloon 40 and support plate 90 of a hemostasis device 10A according to modification 5, viewed from the outside.

As shown in FIGS. 16 and 17, Modification 5 further includes a discharge section 70D as described below in addition to a discharge section 70A in which a portion of the first sheet 47 of the balloon 40 is formed of a porous member 71.

The discharge part 70D includes a tube 74 that communicates between the lumen 40a and the outside of the balloon 40, and a restriction part 75 configured to allow gas to be discharged through the tube 74 and to restrict liquid discharge. have

The restriction portion 75 is constructed by filling the tube 74 with the porous member 71 described above.

A bag-shaped air pocket 76 communicating with the tube 74 is arranged on the outer surface of the balloon 40 . Air pocket 76 is constructed from the same material as balloon 40 and is in a deflated state before use of hemostasis device 10A. Note that when the restricting portion 75 is made of the porous member 71, the air pocket 76 is not an essential component.

As shown in FIG. 18, the discharge part 70D allows the tube 74 to be placed in the maximum expansion part 72 at a position where it does not get in the way when the ultrasound probe 80 is moved.

As the liquid is injected into the lumen 40 a of the balloon 40 , the gas inside the balloon 40 is discharged to the outside of the balloon 40 by passing through the porous member 71 of the discharge section 70 . Furthermore, the gas in the balloon 40 is discharged into the air pocket 76 by passing through the restriction part 75 of the discharge part 70D. Furthermore, the liquid within the balloon 40 is restricted from passing through the porous member 71. Therefore, the pressure force applied to the puncture site P by the balloon 40 does not decrease, and gas can be prevented from remaining in the balloon 40. Therefore, the occlusion state of the blood vessel located at the puncture site P can be confirmed more accurately based on the obtained ultrasound image without reducing the hemostasis function.

Note that it is possible to arrange only the above-mentioned discharge part 70D in the balloon 40 without disposing the discharge part 70A formed of the porous member 71 in the balloon 40. In this case, the first sheet 47 is made of, for example, polyvinyl chloride, like the second sheet 48. Then, the tube 74 and the restriction portion 75 are arranged on the first sheet 47.

Although the hemostasis device according to the present invention has been described above through the embodiments and modified examples, the present invention is not limited to each configuration described, and can be modified as appropriate based on the description of the claims. It is.

For example, each part constituting the hemostatic device can be replaced with any part that can perform the same function. Moreover, arbitrary components may be added.

Further, the present invention is not limited to a hemostasis device worn on the wrist, but can also be applied to a hemostasis device worn on the leg or the like.

10, 10A Hemostasis device 21 Belt (band body)
23 First belt 24 Second belt 30 Velcro fastener 40 Balloon 40a Inner cavity 47 First sheet 48 Second sheet 49 Joint portion 51 Air bubble 52 Gas 60 Injection portion 70, 70A, 70B, 70C, 70D Discharge portion 71 Porous member 72 Maximum expansion part 73a Center part 73b First protrusion 73c Second protrusion 74 Tube 75 Restriction part 76 Air pocket 80 Ultrasonic probe 90 Support plate 91 Window 91a Long side 91b Short side 93 First support plate 94 Second support plate 95 Girder 96 Third support plate 97 Fourth support plate P Puncture site R Radial artery W Wrist

Claims (8)

an inflatable and deflated balloon having a lumen into which a liquid is injected and configured to compress a puncture site formed in a patient;
a band for fixing the balloon to a part of the patient's body;
A hemostatic device, the hemostatic device comprising: a discharge section disposed on the balloon and discharging gas within the balloon to the outside of the balloon as the liquid is injected into the lumen. The band is made of a material with lower elasticity than the balloon, and is connected to the balloon at a position that does not overlap with at least a part of the area in the plane of the balloon,
The hemostatic device according to claim 1, wherein the discharge part is arranged in a region of the balloon where the band does not overlap. further comprising a support plate made of a harder material than the balloon and disposed on the other side of the balloon opposite to the one side that contacts the body;
The band body is connected to the support plate,
The balloon is connected to the support plate on the other side,
The support plate has a window portion that exposes a part of the other surface of the balloon,
The hemostasis device according to claim 1, wherein the discharge section is arranged at a position overlapping the window section in a surface direction of the balloon. The window portion has a rectangular shape with a long side located along the longitudinal direction of the support plate and a short side located along the width direction of the support plate,
The discharge portion includes a center portion disposed at a center position in a plane direction of the window portion, a first protrusion portion protruding from the center portion along the long side, and a first protrusion portion extending from the center portion along the short side. The hemostatic device according to claim 3, further comprising a second protruding portion. The discharge part is made of a porous member that constitutes at least part of one surface of the balloon that is located on the side that contacts the body and the other surface that is located on the opposite side,
The hemostatic device according to any one of claims 1 to 4, wherein the porous member is configured of a member that allows passage of the gas and restricts passage of the liquid. The hemostatic device according to claim 5, wherein at least a portion of the balloon other than the portion made of the porous member is made of a material with lower elasticity than the porous member. The discharge part includes a tube that communicates the inner cavity with the outside of the balloon, and a restriction part configured to allow discharge of the gas through the tube and to restrict discharge of the liquid. The hemostatic device according to claim 1, comprising: Claims 1 to 7, wherein the discharge part is configured to discharge the gas from a maximum expansion part of the balloon disposed at a position farthest from the patient's body when the balloon is expanded. The hemostatic device according to any one of the above.