JP2012105722A - Pad for cuff member, bonding method of pad protrusion, and cuff member unit - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a pad for a cuff member and a bonding method of a pad protrusion in which alignment of a living body implant body and a pad for a cuff member can be freely performed, and the pad can be easily mounted to the living body implant body without imposing burden on a patient; and to provide a cuff member unit including the pad and cuff member.SOLUTION: The pad for a cuff member, formed by having a synthetic resin put on a cuff member, has a rear surface and a front surface opposite thereto, and has a through hole to insert a living body implant body prepared from the rear surface to the front surface, wherein a break is prepared which attains from an outer peripheral edge section of the pad to the through hole, the break is pushed to be open and a living body implant body can be taken in and out to the through hole. In the front surface, a first protrusion is prepared in one break adjoining area which meets the break, and a second protrusion is prepared in the other break adjoining area.

Description

  The present invention relates to a pad made of a synthetic resin that is arranged on the outer surface of a living body and is superimposed on the front surface of a cuff member through which a living body insertion body such as a drive line is inserted, and is easily attached to the living body insertion body About. The present invention also relates to a method for adhering the ridges of the pad, and a cuff member unit including the pad and the cuff member.

  As a cuff member having a hole through which a living body insertion body such as a drive line is inserted, those made of sponge-like synthetic resin and having a pad disposed on the front side (outer side) are disclosed in JP2007-98116A and JP2008. -295480. FIG. 3 of Japanese Patent Application Laid-Open No. 2007-98116 describes a cuff member having a flange portion and a cylindrical portion obliquely intersecting the flange portion.

  FIG. 5 shows the cuff member of FIG. 3 of JP-A-2007-98116. The cuff member 12 includes a flange portion 13 and a cylindrical portion 14 erected from one surface of the flange portion 13. In the center of the flange portion 13, a circular opening having a diameter of about 5 to 100 mm is provided coaxially with the cylindrical portion 14. Between the inner peripheral edge and the outer peripheral edge of the flange portion 13, a protruding line 13 t is provided so as to go around. The pad 15 is overlapped with the inner region of the ridge 13t so as to be fitted and bonded with an adhesive. An opening is also provided in the center of the pad 15.

  A tube (biologically inserted body) 16 is inserted through the cylindrical portion 14. The pad 15 and the tube 16 are bonded with an adhesive 17. The flange portion 3 is superimposed on the outer surface of the living body, and the tube 16 is inserted into the living tissue.

JP2007-98116 JP 2008-295480 A

  Patent Documents 1 and 2 disclose adhesives, heat fusion, ultrasonic fusion, and the like as methods for fixing the pad and the cuff member to the biopsy body. In addition, there is a possibility of giving pain and irritation to the patient, and the adhesive force tends to decrease due to body fluid or physiological saline. When fixing by heat fusion or ultrasonic fusion, it is necessary to heat or irradiate ultrasonic waves so as to be sandwiched from both sides of the pad, and it is necessary to insert a tool into the living body. It is difficult to perform at the surgical site where the patient is placed. Therefore, it is necessary to fix the pad and the cuff member of Patent Documents 1 and 2 to the biopsy body in advance before the operation. In this case, according to the position where the pad and the cuff member are fixed. Since it is necessary to place a living body insertion body, it is difficult to align the pad and the cuff member, and the invasion to the patient is large, such as a wide incision range. In particular, when implanting an artificial heart having a magnetically levitated ultra-compact axial flow pump or centrifugal pump, the diameter of the drive line itself is about 6 mm, but the diameter of the pad and cuff member to be fixed to this is 30 mm. Therefore, it is necessary to make the diameter of the subcutaneous tunnel about 30 mm, which increases the burden on the patient. For these reasons, it is desired to improve the pad and the cuff member.

  The present invention provides a cuff member pad that can freely align the living body insert and the cuff member pad and can easily attach the pad to the living body insert without placing a burden on the patient. And it aims at providing the adhesion method of the protruding item | line of this pad. Moreover, an object of this invention is to provide a cuff member unit provided with this pad and a cuff member.

  A pad for a cuff member according to the present invention (Claim 1) is a pad made of a synthetic resin to be overlaid on a cuff member, and has a rear surface and a front surface opposite to the rear surface. In the cuff member pad provided with a through hole for inserting the insertion body, a cut is provided from the outer peripheral edge of the pad to the through hole, and the living body insertion body penetrates through the opening. A pad that can be inserted into and removed from a hole, and the front surface is provided with a first ridge in an area adjacent to one incision along the incision, and a second ridge in an area adjacent to the other incision. It is characterized by being.

  The pad for a cuff member according to claim 2 is characterized in that, in claim 1, the first and second ridges extend along the cut from the outer peripheral edge of the pad to the through hole. It is what.

  The bonding method for pad ridges according to the present invention (Claim 3) is a method for bonding the pad ridges according to Claim 1 or 2, wherein the synthetic resin is a thermoplastic synthetic resin. The protrusions are heated by sandwiching the stripes, or the protrusions are fused by applying ultrasonic vibration.

  A cuff member unit according to the present invention (Claim 4) is a cuff member unit having the pad according to Claim 1 or 2 and a cuff member overlapped with the pad. A through-hole for inserting a inserted body is provided.

  The cuff member unit according to claim 5 is the cuff member unit according to claim 4, wherein the cuff member is provided with a slit reaching the outer peripheral edge of the cuff member from the through hole, and the living body insertion body can be inserted into and removed from the through hole by opening the slit. It is characterized by becoming.

  In the cuff member pad of the present invention, the pad can be mounted at a desired position of the biopsy body by pushing open the cut of the pad. If the cut is opened slightly, the pad can be smoothly slid along the living body insert. Therefore, according to the present invention, since the pad can be arranged in accordance with the position of the exit portion of the biopsy body on the body surface of the patient, the invasion to the patient can be reduced.

  According to the bonding method of the pad ridges of the present invention, the ridges are extremely separated from each other by heating between the first ridges and the second ridges provided on the pad or by applying ultrasonic vibration. It can be easily fused.

FIG. 1 (a) is a perspective view of a pad according to the embodiment, and FIG. 1 (b) is a perspective view showing a mounting method of the pad to a drive line. 2 (a) is a plan view of the pad according to the embodiment, FIG. 2 (b) is a side view, FIG. 2 (c) is a rear view, and FIG. 2 (d) is FIG. 2 (a). It is the DD sectional view taken on the line. 3 (a) is a front view of the cuff member, FIG. 3 (b) is a side view, FIG. 3 (c) is a plan view, and FIG. 3 (d) is a cross-sectional view taken along line DD of FIG. FIG. FIG. 4 is a sectional view of the cuff member unit according to the embodiment. It is sectional drawing of the conventional cuff member unit.

[Adhesion method for cuff member pads and pad ridges]
Hereinafter, an embodiment of the present invention will be described with reference to FIGS.
FIG. 1 (a) is a perspective view of a pad according to the embodiment, FIG. 1 (b) is a perspective view showing a method of mounting the pad on the drive line, and FIG. 2 (a) is a view of the pad. FIG. 2 (b) is a side view, FIG. 2 (c) is a rear view, and FIG. 2 (d) is a sectional view taken along the line DD of FIG. 2 (a).

  The pad 1 is made of synthetic resin having a substantially circular or substantially elliptical shape in plan view, and the lower surface side of FIG. 2 (d) is the rear surface 1R, and is superimposed on the cuff member. Moreover, the upper surface side is the front surface 1F.

  The front surface 1F is provided with a high place 1a having a relatively high height, a low place 1b having a relatively low height, and a step surface 1c between the two. The height 1a is a curved surface that is convexly curved. The heights “high” and “low” represent a state in which the low portion 1b side of the rear surface 1R of the pad 1 is superimposed on the horizontal plane.

  In the center of the step surface 1c, a cylindrical through hole 2 having a diameter of about 5 to 100 mm is provided so as to penetrate in the thickness direction of the step surface. In this embodiment, the drive line 5 is used as a living body piercing body, but it may be a blood vessel or the like.

  This pad 1 has a notch 3 at a height 1a and first and second ridges 4a and 4b provided in an adjacent region of the notch 3, and the living body is formed by pushing the notch 3 open. A drive line 5 as a insertion body can be mounted in the through hole 2. The cut 3 can be formed by a laser cutter or the like.

  The heights of the first ridges 4a and the second ridges 4b provided in the adjacent region of the cut are preferably about 2 to 15 mm, particularly about 5 to 10 mm. If the height of the ridges 4a and 4b is less than the lower limit value, it is difficult to fuse the ridges with each other, and if the height exceeds the upper limit value, the patient rubs or gets caught on clothes. It is not preferable because there is a risk of being lost. However, it is possible to cut out a part of the upper side of the fused ridges within a range where the area of the fused surface is not extremely reduced (in a range where the adhesive strength is not lowered) and to suppress the height. The range means the final height. The thickness of the ridges is preferably about 0.5 to 3 mm, particularly about 1 to 2 mm. If the thickness of the ridge is less than the lower limit value, the fused portion tends to be weak and cannot be firmly fused. Further, if the thickness exceeds the upper limit value, it may be difficult to sandwich the ridges 4a and 4b, and there is a risk that heat and ultrasonic waves are not applied uniformly and in a short time, resulting in poor fusion. .

  As will be described later, the pad 1 is bonded to a cuff member 6 to form a cuff member unit 9, and is attached to a drive line. When the cuff member unit 9 is attached to the drive line 5, as shown in FIG. 1 (b), after the cut line 3 is pushed open and the drive line 5 is introduced into the through hole 2, the first protrusion 4a and the first protrusion 4a Fusing is performed by heat or ultrasonic waves with the two ridges 4b interposed therebetween.

  The ridges 4a and 4b are preferably fused together by heating or ultrasonic vibration. In the case of fusing by heat, it is preferable to heat and fuse at about 180 to 210 ° C. for about 1 to 10 seconds using a thermocompression bonding body such as an insulator, roll, plug, or ball. In the case of fusing by heating or ultrasonic vibration, it is preferable to use a tool or device having a shape that can sandwich the entire length of the ridges 4a and 4b at a time. With such a tool or device, a single operation can be used. By fusing, the fusion work time can be shortened.

  The pad 1 is preferably exemplified by polyurethane resin, polyamide resin, polyolefin resin, polyester resin, fluororesin, and derivatives thereof. These may be used alone or in combination of two or more. As the pad 1, a polyurethane resin is particularly preferable, and a segmented polyurethane resin is particularly preferable. The hardness of the pad is preferably about 50 to 150 (JIS Shore A hardness). The thickness of the pad 1 is preferably about 0.6 to 10 mm, particularly about 0.6 to 2.0 mm. Thus, by making the pad 1 thinner and more flexible, it is possible to absorb the swinging stress of the living body inserted body, and thus stable adhesion can be expected.

[Cuff member unit]
The cuff member unit of this invention has a cuff member and the above-mentioned pad. As shown in FIGS. 3 and 4, the cuff member in close contact with the pad 1 is made of a porous synthetic resin shaped like the front surface 1F of the pad 1. The cuff member 6 is in close contact with the stepped surface 1c, the high portion 6a that is convexly curved with the same curvature radius as the high portion 1a, the low portion 6b that is in close contact with the low portion 1b, and the step surface 1c. It has a step surface 6c and a through-hole 7 for inserting a biopsy body provided in the step surface 6c. The through hole 7 has the same diameter as the through hole 2 provided in the pad, and is provided so as to be coaxial with the through hole 2.

  As shown in FIG. 3, the cuff member 6 used in the present embodiment has a slit 8 in a positional relationship overlapping with the cut line 3 and pushes open the slit 8 so as to drive as a living body insertion body. 5 can be attached to the through-hole 7.

  The pad 1 is superimposed on the front surface 6F of the cuff member 6 and bonded to form a cuff member unit 9. Adhesive may be used to bond the pad 1 and the front surface 6F. However, when the pad 1 and the cuff member 6 are made of polyurethane resin, a solvent such as DMF, NMP, or THF, or these It can also be carried out with a 5 to 20% by weight polyurethane solution of the above solvent. The cuff member 6 is the same size as the pad 1 or slightly larger than the pad 1, and when the pad 1 is overlapped with the front surface 6 </ b> F of the cuff member 6, the entire periphery of the cuff member 6 is the entire pad 1. A predetermined length (preferably 0 to 50 mm, particularly 1 to 10 mm) extends outward from the periphery.

  The slit 8 can be formed by a cutting blade or a laser cutter. The cuff member unit 9 may be manufactured by bonding the cuff member 6 provided with the slit 8 and the pad 1 having the cut 3, and the pad 1 and the cuff member 6 before providing the slit 8 are bonded. Thereafter, the slit 8 may be formed by moving the cutting blade along the cut 3 of the pad 1. After bonding the pad 1 before providing the cut 3 and the cuff member 6 before providing the slit 8, the cut 3 and the slit 8 may be formed simultaneously by a laser cutter or the like. According to the latter two methods, the cut 3 and the slit 8 can be easily and accurately matched.

  The manufactured cuff member unit 9 is cleaned and then gas sterilized to obtain a cuff member unit product.

  In order to attach the cuff member unit 9 to the drive line 5, the cut line 3 and the slit 8 are pushed open, the drive line 5 is guided into the through holes 2, 7, and then the force that has been pushed open is released. The slit 3 and the slit 8 are closed by the elastic force of the material of the cuff member 6. Next, if necessary, the cuff member unit 9 is slid along the drive line 5 so that the cut 3 and the slit 8 are slightly opened, and the position of the cuff member unit 9 is adjusted. Thereafter, the protrusions 4a and 4b of the pad 1 are fused together by heating, ultrasonic vibration or the like as described above.

  The thickness of the cuff member 6 is preferably about 10 to 100%, particularly about 10 to 50%, of the diameter of the through hole 7 at the intersection 6g between the step surface 6c and the low portion 6b. The thickness of the cuff member 6 in the portion 6h where the ceiling surface of the through hole 7 and the rear surface of the cuff member 6 intersect is preferably about 10 to 100%, particularly about 10 to 50% of the diameter of the through hole 7.

  As the porous material constituting the cuff member 6, a porous synthetic resin having continuous pores is suitable.

The porous material constituting the cuff member 6 is preferably made of a thermoplastic resin or a thermosetting resin, and has an average pore diameter of about 50 to 1,000 μm, particularly about 100 to 650 μm, and has an apparent appearance in a dry state. It has a porous three-dimensional network structure with a density of 0.01 to 0.5 g / cm ^3, particularly 0.01 to 0.1 g / cm ³ .

  The average pore diameter and the apparent density are measured as follows.

<Measurement of average pore diameter>
Using a photograph of the plane (cut surface) of the sample cut with a double-blade razor taken with an electron microscope (SM200, manufactured by Topcon), each hole on the same plane is surrounded by a three-dimensional network structure. The image processing is performed (the image processing apparatus uses LUZEX AP manufactured by Nireco Corp., and the image capturing CCD camera uses LE N50 manufactured by Sony Corporation), and the area of each figure is measured. This is defined as a perfect circle area, and the diameter of the corresponding circle is determined as the hole diameter. However, the fine holes drilled in the skeleton portion of the porous body due to the effect of phase separation during the formation of the porous body are ignored, and only the communication holes on the same plane are measured.

<Porosity>
The porosity is preferably 50 to 80%, particularly preferably about 60 to 75%. In addition, the porosity in this specification can be calculated as follows. That is, a cut surface of a porous three-dimensional network material is photographed, and in the photograph, the resin part is white and the void (air part) is black, and the area of the white part and the area of the black part are calculated by an image processing method. . A calculated apparent density is obtained from the total area of the measurement visual field obtained by the image processing, the total area of the gap portion, and the specific gravity of the polyurethane resin according to JIS K7311. This apparent density is almost the same as the actual measurement value in the case of a general porous material, but is about 10 times or more larger than the actual measurement value in the case of the porous three-dimensional network material used in the present invention. This difference is caused by assuming that the skeleton portion of the porous three-dimensional network material is a solid structure made of polyurethane resin. Therefore, the skeleton group of the porous three-dimensional network material is calculated by substituting the calculated apparent density A and the actually measured apparent density B into the calculation formula (AB) / A × 100 (%). It becomes possible to obtain the porosity of the material itself. When the calculated apparent density is 0.91 g / cm ³ and the measured apparent density is 0.077 g / cm ³ , the skeleton substrate of the porous three-dimensional network material used in the present invention has a porosity of Calculated to be 91.5% porous.

<Measurement of apparent density>
A value obtained by cutting a porous structure into a rectangular parallelepiped of about 10 mm × 10 mm × 3 mm with a double-blade razor and obtaining a volume from the dimensions obtained by measurement with a projector (Nikon, V-12), and dividing the weight by the volume. The apparent density is obtained from

  Examples of the thermoplastic resin constituting such a porous three-dimensional network structure include polyurethane resins, polyamide resins, polyolefin resins, polyester resins, fluororesins, and derivatives thereof. These may be used alone or in combination of two or more. Of these, polyurethane resins are particularly preferred, and segmented polyurethane resins are particularly preferred.

The segmented polyurethane resin is synthesized from three components of a polyol, a diisocyanate and a chain extender, and has an elastomeric property due to a block polymer structure having a so-called hard segment portion and soft segment portion in the molecule. Therefore, the elastic properties obtained when this segmented polyurethane resin is used are that the subcutaneous tissue and cuff member when the patient, catheter or cannula move, or when the skin around the puncture site moves during disinfection work, etc. The effect of attenuating the stress generated at the interface with can be expected.
The segmented polyurethane resin has a polyether-based, polyester-based, polyether-polyester-based, or polycarbonate-based (also referred to as a polycarbonate ester type) depending on the soft segment structure or the structure of the soft segment / hard segment bonded portion. In the present invention, it is preferable to use a polycarbonate-based polyurethane resin. The reason for this is that polyurethane resin is a material that is generally susceptible to hydrolysis, and when implanted in a living body, it is naturally hydrolyzed by the action of body fluid (water) and body temperature, decomposed by the action of enzymes, and from immune cells. This is because the material is weakened by decomposition due to the action of released active oxygen. Therefore, it is preferable to use a polycarbonate-based polyurethane resin when it is stably present in the living body for a long time. This polycarbonate-based polyurethane resin is a resin that has the property of protecting nearby urethane bonds from decomposition by the strong crystal cohesive force of the polycarbonate segment, and is extremely superior in hydrolysis resistance compared to other polyurethane resins. is there.

  Below, an example of the manufacturing method of the porous three-dimensional network structure which consists of a thermoplastic polyurethane resin which comprises a cuff member is demonstrated.

  In order to produce a porous three-dimensional network structure made of a thermoplastic polyurethane resin, first, a polyurethane resin, a water-soluble polymer compound described later as a pore-forming agent, and an organic solvent that is a good solvent for the polyurethane resin are used. Mix to produce polymer dope. Specifically, after a polyurethane resin is mixed with an organic solvent to form a uniform solution, a water-soluble polymer compound is mixed and dispersed in this solution. Examples of the organic solvent include N, N-dimethylformamide, N-methyl-2-pyrrolidinone, and tetrahydrofuran, but are not limited thereto as long as the thermoplastic polyurethane resin can be dissolved. It is also possible to melt the polyurethane resin by the action of heat without reducing the amount of the organic solvent or using it, and to mix the pore forming agent therewith.

  Examples of the water-soluble polymer compound as the pore-forming agent include polyethylene glycol, polypropylene glycol, polyvinyl alcohol, polyvinyl pyrrolidone, alginic acid, carboxymethyl cellulose, hydroxypropyl cellulose, methyl cellulose, and ethyl cellulose, but are homogeneously dispersed with the thermoplastic resin. If it forms a polymer dope, this does not apply. Depending on the type of thermoplastic resin, it is also possible to use not only water-soluble polymer compounds but also lipophilic compounds such as phthalates and paraffins and inorganic salts such as lithium chloride and calcium carbonate. It is also possible to promote the generation of secondary particles during solidification, that is, the formation of a skeleton of the porous body, using a crystal nucleating agent for a polymer.

  Next, a polymer dope produced from a thermoplastic polyurethane resin, an organic solvent and a water-soluble polymer compound is immersed in a coagulation bath containing a poor solvent for the thermoplastic polyurethane resin, and the organic solvent and the coagulation bath are immersed in the coagulation bath. The water-soluble polymer compound is extracted and removed. In this way, a porous three-dimensional network material made of polyurethane resin can be obtained by removing part or all of the organic solvent and the water-soluble polymer compound. Examples of the poor solvent used here include water, lower alcohols, and low-carbon ketones. After the polyurethane resin is solidified, the porous three-dimensional network material is washed with water or the like to remove the organic solvent and pore-forming agent remaining in the porous three-dimensional network material.

In the porous three-dimensional network material, it is preferable that fine pores are also formed in the skeletal base material itself constituting the network structure. In particular, the porous three-dimensional network material has an average pore diameter of 100 to 650 μm and forms a continuous three-dimensional network structure with an apparent density in a dry state of 0.10 g / cm ³ or less. In addition, the skeleton base material itself constituting the network structure is a porous body having a porosity of 70% or more, and the surface layer of the skeleton base material is a dense layer interspersed with fine pores. Is preferred. This micropore makes the surface of the skeletal base material not a smooth surface but a complex uneven surface, so it is also effective in retaining collagen, cell growth factors, etc., and as a result increases cell engraftment Is possible. However, the fine pores of the skeleton substrate itself are not included in the concept of calculating the average pore diameter of the porous three-dimensional network structure referred to in the present invention.

  As described above, the skeleton base material itself that forms the network structure of the porous three-dimensional network material is porous with a high porosity, and the surface layer of the skeleton base material is a dense layer interspersed with fine pores. In addition, the following effects are exhibited by the fact that the pores inside the skeleton base material communicate with the outside through the fine pores in the surface layer. That is, since the skeleton base material of the porous three-dimensional network material is porous, the skeleton base material is infiltrated with an extracellular matrix such as collagen, albumin, oxygen, waste products, water, electrolyte, etc. These diffusions and exchanges are performed between the base material and the living tissue. Thereby, oxygen and nutrients can be replenished to the whole porous three-dimensional network material through this skeleton base material. Note that infiltration of cells into the skeletal base material is blocked by the dense layer on the surface of the skeletal base material, so that no cell component is present inside the skeletal base material. As a result, the inside of the skeleton base material is prevented from being clogged, and a capillary-like function for supplying oxygen and nutrients to the entire porous three-dimensional network material through the skeleton base material is maintained. As a result, functions useful as a bio-implanting material such as good tissue infiltration, engraftment, maturation, and angiogenesis are expressed.

In order to obtain the porosity of the skeleton base material of the porous three-dimensional network material made of polyurethane, first, the average pore diameter is measured as described above. That is, the cut surface of the porous three-dimensional network material is photographed, and in the photograph, the resin portion is white and the void (air portion) is black. . A calculated apparent density is obtained from the total area of the visual field of measurement obtained by the image processing, the total area of the gap portion, and the specific gravity of the polyurethane resin according to JIS K7311. This apparent density is generally about 10 times or more larger than the actually measured value. This error is caused by assuming that the skeleton portion of the porous three-dimensional network material is a solid structure made of polyurethane resin. Therefore, the skeleton group of the porous three-dimensional network material is calculated by substituting the calculated apparent density A and the actually measured apparent density B into the calculation formula (AB) / A × 100 (%). It becomes possible to obtain the porosity of the material itself. When the calculated apparent density is 0.91 g / cm ³ and the actually measured apparent density is 0.077 g / cm ³ , the skeleton substrate of the porous three-dimensional network material has a porosity of 91.5%. Calculated to be porous.

  In this porous 3D network material made of polyurethane, there are micropores on the surface of the skeletal base material, but this is not the size that cells can infiltrate, but it only forms irregularities that help cell engraftment It is the thing to do. That is, as described above, the surface of the skeletal base becomes a complex uneven surface due to the micropores, so that the cell engraftment is high. However, although these micropores are not sized to allow cells to infiltrate, nutrients, oxygen, water, etc. are sized to infiltrate. Oxygen, water, etc. are diffused and exchanged. That is, oxygen and nutrients can be replenished to the entire porous three-dimensional network material through this skeleton substrate.

  Each of the above embodiments shows an example of the present invention, and the present invention is not limited to the above configuration.

DESCRIPTION OF SYMBOLS 1 Pad 1a High place 1b Low place 1c Step surface 1F Front surface 1R Rear surface 2 Through-hole 3 Cut 4a 1st convex 4b 2nd convex 5 Drive line
6 cuff member 6a high place 6b low place 6c step surface 7 through hole 8 slit 9 cuff member unit

Claims (5)

A pad made of synthetic resin to be superimposed on a cuff member, having a rear surface and a front surface opposite to the rear surface, and having a through hole for inserting a biomedical body from the rear surface to the front surface In member pads,
A cut is provided from the outer peripheral edge of the pad to the through hole,
A pad in which the biopsy body can be inserted into and removed from the through hole by pushing the cut,
A pad for a cuff member, wherein the front surface is provided with a first protruding line in one cut adjacent area along the cut line and a second protruding line in the other cut adjacent area.   2. The cuff member pad according to claim 1, wherein the first and second ridges extend along the cut line from an outer peripheral edge portion of the pad to the through hole.   It is the method of joining the protruding item | line of the pad of Claim 1 or 2, Comprising: The said synthetic resin is a thermoplastic synthetic resin, and it heats | interposes this protruding item | line, or applies an ultrasonic vibration. A method for bonding pad ridges, wherein the ridges are fused with each other.   A cuff member unit comprising the pad according to claim 1 and a cuff member overlapped with the pad, wherein the cuff member is provided with a through hole for inserting a biopsy body. A cuff member unit.   5. The slit according to claim 4, wherein the cuff member is provided with a slit that reaches the outer peripheral edge of the cuff member from the through hole, and the living body insertion body can be inserted into and removed from the through hole by pushing open the slit and the slit of the pad. A cuff member unit.

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