JP2012029717A - Pad for cuff member, adhesion method of pad, and cuff member unit - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a pad for a cuff member which freely performs positioning of a living body insertion body and the pad for the cuff member and can be easily mounted on a living body insertion body, and to provide a method for mounting the pad and a cuff member unit provided with the pad and the cuff member.SOLUTION: In the pad for the cuff member which is superimposed on the front face of the cuff member and is made of a synthetic resin, and on which an opening for inserting the living body insertion is arranged, a cut reaching the opening from the circumferential edge of the pad is provided, and the living body insertion body can be inserted/extracted by push-opening the cut.

Description

  The present invention relates to a pad made of a synthetic resin that is disposed on the outer surface of a living body and is superimposed on the front surface of a cuff member through which the living body insert is inserted, and relates to a pad for a cuff member that can be easily attached to the living body insert. The present invention also relates to a method for bonding the pad, and a cuff member unit including the pad and the cuff member.

  A cuff member having a hole through which a living body piercing body (hereinafter simply referred to as a piercing body) is inserted is made of a sponge-like synthetic resin and has a pad disposed on the front side (outer side). JP-A-2007-98116 and JP-A-2008-295480. 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. 6 shows the cuff member shown in 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 (insertion 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, thermal fusion, ultrasonic fusion, and the like as methods for fixing the pad and cuff member to the biopsy body. It is difficult to perform at the operation site. Therefore, in the pad and cuff member of Patent Documents 1 and 2, it is necessary to fix the pad and cuff member to the living body puncture body in advance before the operation, but in this case, the pad and the cuff member are fixed. The living body insert is placed in accordance with the position of the patient, and the position of the patient outlet is determined. Therefore, the incision site becomes wide (many), and the invasion to the patient is great.

  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, and a method of bonding the pad. The purpose is to provide. Moreover, an object of this invention is to provide a cuff member unit provided with this pad and a cuff member.

  The pad of the present invention (Claim 1) is a pad made of synthetic resin that is superimposed on the front surface of the cuff member, and is a cuff member pad provided with an opening for inserting a insertion body. A cut is provided from the part to the opening, and the living body insertion body can be inserted into and removed from the opening by pushing the cut.

  The pad according to claim 2 is characterized in that, in claim 1, one cut adjacent area along the cut and the other cut adjacent area overlap each other.

  The pad of claim 3 is characterized in that, in claim 2, the thickness of the cut adjacent region is smaller than the thickness other than the cut adjacent region.

  The pad adhering method of the present invention (Claim 4) is a method of adhering the notch adjacent regions of the pad according to claim 2 or 3, in order to adhere the synthetic resin of the pad to one notch adjacent region. After adhering the solvent, the adjacent regions of the cut are overlapped with each other.

  According to a fifth aspect of the present invention, there is provided the pad bonding method according to the fourth aspect, wherein the solvent is attached to the notch adjacent region disposed on the side far from the cuff member among the notch adjacent regions. It is.

  The pad bonding method according to claim 6 is the method according to claim 4 or 5, wherein the solvent is tetrahydrofuran, cyclohexanone, chloroform, DMF (N, N-dimethylformamide), or NMP (N-methyl-2-pyrrolidone). It is a feature.

  A cuff member unit according to the present invention (Claim 7) is a cuff member unit including the pad according to any one of Claims 1 to 3 and a cuff member overlapped with the pad. The member is provided with a insertion body insertion hole.

  The cuff member unit according to claim 8 is the cuff member unit according to claim 7, wherein a slit reaching the outer peripheral edge of the cuff member from the insertion body insertion hole is provided in the cuff member, and the living body insertion body is inserted by opening the slit. It is characterized in that it can be taken in and out of the body insertion hole.

  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 this invention, a pad can be arrange | positioned according to the position of the exit part of the biopsy body in a patient's body surface.

  In the pad adhering method of the present invention, after adhering the solvent to the notch adjacent region, the notch adjacent regions can be firmly bonded by overlapping the notch adjacent regions, and the adhesive surface Easy alignment.

It is a perspective view of the pad concerning an embodiment. 2 (a) is a plan view of the pad according to the embodiment, FIG. 2 (b) is a cross-sectional view taken along line BB of FIG. 2 (a), and FIG. 2 (c) is FIG. 2 (b). It is a CC sectional view taken on the line of FIG. FIG. 3 is a plan view of a pad according to another embodiment, and FIG. 3 (b) is a cross-sectional view taken along line BB of FIG. 3 (a). 4 (a) is a front view of the cuff member, FIG. 4 (b) is a right side view, FIG. 4 (c) is a plan view, and FIG. 4 (d) is a DD line of FIG. It is sectional drawing. FIG. 5 is a cross-sectional view of the cuff member unit according to the embodiment. It is sectional drawing of the conventional cuff member unit.

[Cuff member pad and pad bonding method]
The first embodiment will be described below with reference to FIGS.
FIG. 1 (a) is a perspective view of a pad for a cuff member according to an embodiment, and FIG. 1 (b) is a perspective view showing a method for mounting the pad on a living body insertion body. 2 (a) is a plan view of the pad, FIG. 2 (b) is a cross-sectional view taken along line BB of FIG. 2 (a), and FIG. 2 (c) is FIG. 2 (b). It is CC sectional view taken on the line.

  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 (c) 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 high portion 1a is a convexly curved surface, and the low portion 1b is a concavely curved surface. 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 circular opening 2 having a diameter of about 5 to 100 mm is provided so as to penetrate in the thickness direction of the step surface. The low part 1b has a substantially arc-shaped cross section perpendicular to the axis of the opening 2. In this embodiment, the drive line 4 is used as a living body piercing body, but it may be a sending / removing blood vessel or the like.

  The pad 1 has a cut 3 at a low portion 1b, and a drive line 4 as a living body insertion body can be attached to the opening 2 by pushing the cut 3 open. In this embodiment, the cut adjacent area is provided in the low place 1b, and the cut adjacent areas 3a and 3b overlap each other.

  The thicknesses of the cut adjacent regions 3a and 3b are preferably smaller than the thicknesses of the pads other than the cut adjacent regions, respectively. In particular, the thickness when the cut adjacent regions 3a and 3b are overlapped is different from that of the cut adjacent regions. The thickness is preferably adjusted to be the same as the thickness of the pad. The thicknesses of the cut adjacent regions 3a and 3b are each preferably about 0.3 to 1.0 mm, particularly preferably about 0.3 to 0.5 mm. If the thickness of the incision adjacent region is small, the applied solvent is likely to pass through the pad, so that the cuff member that is in close contact with the rear surface of the pad dissolves or adversely affects the living body.

  In order to attach the pad 1 to the drive line 4, the notch 3 is pushed open as shown in FIG. 1 (b), the drive line 4 is guided into the opening 2, and then the force that has been pushed open is released. The cut 3 is closed by the elastic force of the material 1. Next, the position of the pad 1 is adjusted by sliding the opening 2 along the drive line 4 so that the cut 3 is slightly opened as necessary. Thereafter, the notch adjacent region 3b is lifted, a solvent is adhered to the surface where the notch adjacent regions 3a and 3b are in contact, and the notch adjacent regions 3a and 3b are overlapped again to perform bonding. Thus, when apply | coating and adhering a solvent to a notch adjacent area | region, a solvent does not adhere easily to the cuff member provided under the pad. Moreover, since adhesion | attachment can be performed by superimposing an adjacent area | region along the incision 3, the position of an adhesion surface can be easily performed even during surgery.

  As the solvent to be attached to the adjacent region of the cut line, tetrahydrofuran, cyclohexanone, chloroform, DMF (N, N-dimethylformamide), NMP (N-methyl-2-pyrrolidone) and a polyurethane solution of 5 to 20% by weight of these solvents are preferable. . These solvents are liable to infiltrate into the inside of a pad made of the material described later, so that liquid dripping hardly occurs. Further, since it is highly volatile, the solvent infiltrated inside diffuses quickly to the outside of the pad, and the adjacent regions of the cut can be firmly bonded in a short time and hardly remain in the living body. In addition, although it is also possible to use a general adhesive for the adhesion of the area adjacent to the cut line, if the adhesive is used, the bonding surface of the pad becomes hard and the flexibility of the cuff member unit is impaired. Adhesion is preferably performed using the solvent.

  The solvent may be attached to either of the cut adjacent areas 3a and 3b, but it is preferable that the solvent is attached to 3b which is the cut adjacent area disposed on the side far from the cuff member. When the solvent is attached to the cut adjacent region 3b, the problem that the solvent adheres to the cuff member that is in close contact with the lower side of the pad and the cuff member is deteriorated hardly occurs. As a method of attaching the solvent to the adjacent region of the cut, it is preferable to attach the solvent with a cotton swab or a brush soaked with the solvent. After adhering the solvent to the cut adjacent area, the cut adjacent areas may be immediately overlapped and bonded, or after drying for about 1 to 20 minutes, the cut adjacent areas may be overlapped and bonded. . When bonding is performed after drying, the influence on the patient due to volatilization of the solvent can be suppressed as much as possible.

  The amount of the solvent attached to the notch adjacent regions 3a and 3b is preferably about 0.5 to 10% by weight, particularly about 3 to 6% by weight of the pad. When the amount of solvent to be applied is small, the incision adjacent regions cannot be firmly bonded to each other, and when the amount of solvent is large, the cuff member is dissolved by the solvent or the solvent is removed from the tissue of the surgical site. May irritate.

  In this embodiment, the cut 3 and the cut adjacent areas 3a and 3b are provided in the low place 1b. However, as shown in FIG. 3, the cut 3 and the cut adjacent areas 3a and 3b may be provided in the high place 1a. Good. According to the form of FIG. 3, since the areas of the cut adjacent areas 3a and 3b are large, it becomes possible to bond the cut adjacent areas more firmly.

  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. Of these, polyurethane resins are particularly preferred, and segmented polyurethane resins are particularly preferred. 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 inserted body, and thus stable adhesion can be expected.

[Cuff member unit]
The cuff member unit of the present invention has the above-described pad and cuff member. As shown in FIGS. 4 and 5, the cuff member that is in close contact with the pad 1 is made of a porous synthetic resin having a shape that follows the front surface 1 </ b> F of the pad 1. The cuff member 5 is in close contact with the stepped surface 1c, the high portion 5a that is convexly curved with the same radius of curvature as the high portion 1a, the low portion 5b that is in close contact with the low portion 1b, and the step surface 1c. It has a step surface 5c and a biopsy body insertion hole (hereinafter sometimes referred to as "insertion hole") 6 provided in the step surface 5c. The insertion hole 6 has the same diameter as the opening 2 and is provided so as to be coaxial with the opening 2.

  The pad 1 is superimposed on the front surface 5F of the cuff member 5 and bonded to form the cuff member unit 8. Adhesive may be used to bond the pad 1 and the front surface 5F, but when the pad 1 and the cuff member 5 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 5 is the same size as the pad 1 or is slightly larger than the pad 1, and the entire periphery of the cuff member 5 is the entire pad 1 when the pad 1 is overlapped with the front surface 5F of the cuff member 5. A predetermined length (preferably 0 to 50 mm, particularly 1 to 10 mm) extends outward from the periphery.

  As shown in FIG. 4, the cuff member 5 used in the present embodiment has a slit 7, and the drive line 4 as a living body insertion body can be attached to the insertion hole 6 by pushing the slit 7 open. It is said that. In this embodiment, the slit 7 is provided in the low place 5b, but may be provided in the high place 5a. In order to attach the cuff member 5 provided with the slit 7 to the drive line 4 in this manner, the slit 7 is pushed open, the drive line 4 is guided into the insertion hole 6, and then the force that has been pushed open is released. The slit 7 is closed by the elastic force of the material of the cuff member 5. Next, if necessary, the cuff member 5 is slid along the drive line 4 so that the slit 7 is slightly opened, and the position of the cuff member 5 is adjusted.

  The thickness of the cuff member 5 is preferably about 10 to 100%, particularly about 10 to 50% of the diameter of the insertion hole 6 at the intersection 5g between the step surface 5c and the low portion 5b. The thickness of the cuff member 5 in the portion 5h where the ceiling surface of the insertion hole 6 and the rear surface of the cuff member 5 intersect is preferably about 10 to 100%, particularly about 10 to 50% of the diameter of the insertion hole 6.

  As the porous material constituting the cuff member 5, a porous synthetic resin having continuous pores is suitable.

The porous material constituting the cuff member 5 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.

<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 resins described above are polyether-based, polyester-based, polyether-polyester-based, polycarbonate-based (also referred to as “polycarbonate-based”), depending on the soft segment structure and the structure of the soft segment / hard segment joint. 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.

EXAMPLES Hereinafter, the present invention will be described more specifically with reference to examples. However, the present invention is not limited to the following examples unless it exceeds the gist.
[Example 1]
A pad shown in FIG. 1 was prepared using a sheet made of a thermoplastic polyurethane elastomer (“Milactolan E980” manufactured by Milactran). The weight of this pad was 0.74 ± 0.02 g. When special grade tetrahydrofuran (Kanto Chemical Co., Ltd.) was applied to the cut adjacent region 3b of the pad with a cotton swab, the surface immediately became dry. When the coated surface was touched with a finger, the presence of the liquid could not be confirmed. Further, no change such as dissolution was observed on the coated surface. The weight of the pad after applying tetrahydrofuran and air-drying for 1 minute was 0.77 ± 0.04 g. From this result, the adhesion amount of the solvent was calculated to be 4% of the weight of the pad.

  After air drying, the cut adjacent areas 3a and 3b were overlapped and sandwiched for 1 minute. As a result, the cut adjacent areas 3a and 3b were firmly bonded, and it was difficult to peel off the bonded surface. In addition, although there was an irritating odor of tetrahydrofuran from the solvent-coated surface before adhesion, no irritation to the skin was felt.

[Comparative Example 1]
The pad was bonded in the same manner as in Example 1 except that the amount of the solvent adhered was adjusted to 1% or less of the weight of the pad. In Comparative Example 1, the adjacent area of the cut could not be firmly bonded and could be easily peeled off. Fluffing occurred in the area adjacent to the cut after peeling.

[Comparative Example 2]
The pad was bonded in the same manner as in Example 1 except that the solvent application amount was adjusted to be 10% or more of the pad weight. In Comparative Example 2, it was possible to firmly bond the cut adjacent regions 3a and 3b, but an irritating odor and unpleasant sensation due to tetrahydrofuran were confirmed. When this pad was stacked on the cuff member, the surface of the cuff member was dissolved.

  From the results of Examples and Comparative Examples, it can be seen that if the amount of the solvent is small, the bonding cannot be performed, and if the amount of the solvent is large, the cuff member is adversely affected. Moreover, if the amount of the solvent is large, the patient is stimulated, which is not preferable.

DESCRIPTION OF SYMBOLS 1 Pad 1a High place 1b Low place 1c Step surface 1F Front surface 1R Rear surface 2 Opening 3 Cut 3a, 3b Cut adjacent area 4 Bioinsert 5 Cuff member 5a Height 5b Low place 5c Step surface 5F Front surface 5R Rear surface 6 Body insertion hole 7 Slit

Claims (8)

In a pad made of synthetic resin that is superimposed on the front surface of the cuff member, and provided with an opening for insertion of the insertion body,
A cut is provided from the peripheral edge of the pad to the opening;
A pad, wherein the biopsy body can be inserted into and removed from the opening by pushing the cut.   The pad according to claim 1, wherein one cut adjacent area along the cut overlaps with the other cut adjacent area.   3. The pad according to claim 2, wherein a thickness of the cut adjacent region is smaller than a thickness other than the cut adjacent region.   It is a method of adhering the notch adjacent regions of the pad according to claim 2 or 3, and after adhering a solvent for adhering the synthetic resin of the pad to one notch adjacent region, the notch adjacent regions are overlapped. A method for bonding pads, characterized by combining them.   The pad adhering method according to claim 4, wherein the solvent is attached to a cut adjacent region disposed on a side far from the cuff member among the cut adjacent regions.   6. The pad bonding method according to claim 4, wherein the solvent is tetrahydrofuran, cyclohexanone, chloroform, DMF (N, N-dimethylformamide), or NMP (N-methyl-2-pyrrolidone).   A cuff member unit comprising the pad according to any one of claims 1 to 3 and a cuff member overlapped with the pad, wherein the cuff member is provided with an insertion body insertion hole. A cuff member unit.   In Claim 7, the said cuff member is provided with the slit which reaches the outer periphery of the cuff member from the said insertion body insertion hole, and it becomes possible to push in and open the slit, and the biological insertion body can be inserted into and removed from the insertion body insertion hole. A cuff member unit.

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